Abstract
Tissue microstructure modeling of diffusion MRI signal is an active research area striving to bridge the gap between macroscopic MRI resolution and cellular-level tissue architecture. Such modeling in neuronal tissue relies on a number of assumptions about the microstructural features of axonal fiber bundles, such as the axonal shape (e.g., perfect cylinders) and the fiber orientation dispersion. However, these assumptions have not yet been validated by sufficiently high-resolution 3-dimensional histology. Here, we reconstructed sequential scanning electron microscopy images in mouse brain corpus callosum, and introduced a random-walker (RaW)-based algorithm to rapidly segment individual intra-axonal spaces and myelin sheaths of myelinated axons. Confirmed by a segmentation based on human annotations initiated with conventional machine-learning-based carving, our semi-automatic algorithm is reliable and less time-consuming. Based on the segmentation, we calculated MRI-relevant estimates of size-related parameters (inner axonal diameter, its distribution, along-axon variation, and myelin g-ratio), and orientation-related parameters (fiber orientation distribution and its rotational invariants; dispersion angle). The reported dispersion angle is consistent with previous 2-dimensional histology studies and diffusion MRI measurements, while the reported diameter exceeds those in other mouse brain studies. Furthermore, we calculated how these quantities would evolve in actual diffusion MRI experiments as a function of diffusion time, thereby providing a coarse-graining window on the microstructure, and showed that the orientation-related metrics have negligible diffusion time-dependence over clinical and pre-clinical diffusion time ranges. However, the MRI-measured inner axonal diameters, dominated by the widest cross sections, effectively decrease with diffusion time by ~ 17% due to the coarse-graining over axonal caliber variations. Furthermore, our 3d measurement showed that there is significant variation of the diameter along the axon. Hence, fiber orientation dispersion estimated from MRI should be relatively stable, while the “apparent” inner axonal diameters are sensitive to experimental settings, and cannot be modeled by perfectly cylindrical axons.
Similar content being viewed by others
References
Abdollahzadeh A, Belevich I, Jokitalo E, Tohka J, Sierra A (2017) 3D axonal morphometry of white matter. https://doi.org/10.1101/239228
Aboitiz F, Scheibel AB, Fisher RS, Zaidel E (1992) Fiber composition of the human corpus callosum. Brain Res 598:143–153
Achanta R, Shaji A, Smith K, Lucchi A, Fua P, Susstrunk S (2012) SLIC superpixels compared to state-of-the-art superpixel methods. IEEE Trans Pattern Anal Mach Intell 34:2274–2282. https://doi.org/10.1109/TPAMI.2012.120
Adams R, Bischof L (1994) Seeded region growing. IEEE Trans Pattern Anal 16:641–647
Alexander DC, Hubbard PL, Hall MG, Moore EA, Ptito M, Parker GJ, Dyrby TB (2010) Orientationally invariant indices of axon diameter and density from diffusion. MRI Neuroimage 52:1374–1389. https://doi.org/10.1016/j.neuroimage.2010.05.043
Arganda-Carreras I et al (2015) Crowdsourcing the creation of image segmentation algorithms for connectomics. Front Neuroanat 9:142. https://doi.org/10.3389/fnana.2015.00142
Anderson AW (2005) Measurement of fiber orientation distributions using high angular resolution diffusion imaging. Magn Reson Med 54(5):1194–1206
Assaf Y, Basser PJ (2005) Composite hindered and restricted model of diffusion (CHARMED) MR imaging of the human brain. Neuroimage 27:48–58. https://doi.org/10.1016/j.neuroimage.2005.03.042
Assaf Y, Blumenfeld-Katzir T, Yovel Y, Basser PJ (2008) AxCaliber: a method for measuring axon diameter distribution from diffusion MRI. Magn Reson Med 59:1347–1354. https://doi.org/10.1002/mrm.21577
Barazany D, Basser PJ, Assaf Y (2009) In vivo measurement of axon diameter distribution in the corpus callosum of rat brain. Brain 132:1210–1220. https://doi.org/10.1093/brain/awp042
Benjamini D, Komlosh ME, Holtzclaw LA, Nevo U, Basser PJ (2016) White matter microstructure from nonparametric axon diameter distribution mapping. Neuroimage 135:333–344. https://doi.org/10.1016/j.neuroimage.2016.04.052
Berthold CH, Nilsson I, Rydmark M (1983) Axon diameter and myelin sheath thickness in nerve fibres of the ventral spinal root of the seventh lumbar nerve of the adult and developing cat. J Anat 136:483–508
Bingham C (1974) Antipodally symmetric distribution on sphere. Ann Stat 2:1201–1225
Budde MD, Frank JA (2010) Neurite beading is sufficient to decrease the apparent diffusion coefficient after ischemic stroke. Proc Natl Acad Sci USA 107:14472–14477. https://doi.org/10.1073/pnas.1004841107
Burcaw LM, Fieremans E, Novikov DS (2015) Mesoscopic structure of neuronal tracts from time-dependent diffusion. Neuroimage 114:18–37. https://doi.org/10.1016/j.neuroimage.2015.03.061
Caminiti R, Ghaziri H, Galuske R, Hof PR, Innocenti GM (2009) Evolution amplified processing with temporally dispersed slow neuronal connectivity in primates. Proc Natl Acad Sci USA 106:19551–19556. https://doi.org/10.1073/pnas.0907655106
De Santis S, Jones DK, Roebroeck A (2016) Including diffusion time dependence in the extra-axonal space improves in vivo estimates of axonal diameter and density in human. white matter. Neuroimage 130:91–103. https://doi.org/10.1016/j.neuroimage.2016.01.047
Dell’Acqua F, Rizzo G, Scifo P, Clarke RA, Scotti G, Fazio F (2007) A model-based deconvolution approach to solve fiber crossing in diffusion-weighted MR imaging. IEEE Trans Biomed Eng 54:462–472. https://doi.org/10.1109/TBME.2006.888830
Dhital B, Reisert M, Kellner E, Kiselev VG (2019) Intra-axonal diffusivity in brain white matter. NeuroImage 189:543–550
Dorkenwald S, Schubert PJ, Killinger MF, Urban G, Mikula S, Svara F, Kornfeld J (2017) Automated synaptic connectivity inference for volume electron microscopy. Nat Methods 14:435–442. https://doi.org/10.1038/nmeth.4206
Duval T et al (2015) In vivo mapping of human spinal cord microstructure at 300 mT/m. Neuroimage 118:494–507. https://doi.org/10.1016/j.neuroimage.2015.06.038
Fieremans E, Burcaw LM, Lee HH, Lemberskiy G, Veraart J, Novikov DS (2016) In vivo observation and biophysical interpretation of time-dependent diffusion in human white matter. Neuroimage 129:414–427. https://doi.org/10.1016/j.neuroimage.2016.01.018
Frank LR (2002) Characterization of anisotropy in high angular resolution diffusion-weighted MRI. Magn Reson Med 47(6):1083–1099
Giacci MK, Bartlett CA, Huynh M, Kilburn MR, Dunlop SA, Fitzgerald M (2018) Three dimensional electron microscopy reveals changing axonal and myelin morphology along normal and partially injured optic nerves. Sci Rep 8:3979. https://doi.org/10.1038/s41598-018-22361-2
Grussu F, Schneider T, Yates RL, Zhang H, Wheeler-Kingshott C, DeLuca GC, Alexander DC (2016) A framework for optimal whole-sample histological quantification of neurite orientation dispersion in the human spinal cord. J Neurosci Methods 273:20–32. https://doi.org/10.1016/j.jneumeth.2016.08.002
Jespersen SN, Kroenke CD, Ostergaard L, Ackerman JJ, Yablonskiy DA (2007) Modeling dendrite density from magnetic resonance diffusion measurements. Neuroimage 34:1473–1486. https://doi.org/10.1016/j.neuroimage.2006.10.037
Jespersen SN et al (2010) Neurite density from magnetic resonance diffusion measurements at ultrahigh field: comparison with light microscopy and electron microscopy. Neuroimage 49:205–216. https://doi.org/10.1016/j.neuroimage.2009.08.053
Jespersen SN, Olesen JL, Hansen B, Shemesh N (2017) Diffusion time dependence of microstructural parameters in fixed spinal cord. Neuroimage. https://doi.org/10.1016/j.neuroimage.2017.08.039
Jones DK (2010) Diffusion MRI: theory, methods, and application. Oxford University Press, Oxford
Kaynig V et al (2015) Large-scale automatic reconstruction of neuronal processes from electron microscopy images. Med Image Anal 22:77–88. https://doi.org/10.1016/j.media.2015.02.001
Kirschner DA, Hollingshead CJ (1980) Processing for electron microscopy alters membrane structure and packing in myelin. J Ultrastruct Res 73:211–232
Kleinnijenhuis M, Johnson E, Mollink J, Jbabdi S, Miller K (2017) A 3D electron microscopy segmentation pipeline for hyper-realistic diffusion simulations. In: ISMRM 25th annual meeting, Hawaii, USA Proceedings of the ISMRM annual meeting, vol 25, p 1090
Komlosh ME, Ozarslan E, Lizak MJ, Horkayne-Szakaly I, Freidlin RZ, Horkay F, Basser PJ (2013) Mapping average axon diameters in porcine spinal cord white matter and rat corpus callosum using d-PFG. MRI Neuroimage 78:210–216. https://doi.org/10.1016/j.neuroimage.2013.03.074
Lee H-H, Fieremans E, Novikov DS (2017) What dominates the time dependence of diffusion transverse to axons: intra- or extra-axonal water? NeuroImage. https://doi.org/10.1016/j.neuroimage.2017.12.038
Leergaard TB, White NS, de Crespigny A, Bolstad I, D’Arceuil H, Bjaalie JG, Dale AM (2010) Quantitative histological validation of diffusion MRI fiber orientation distributions in the rat brain. PLoS One 5:e8595. https://doi.org/10.1371/journal.pone.0008595
Liewald D, Miller R, Logothetis N, Wagner HJ, Schuz A (2014) Distribution of axon diameters in cortical white matter: an electron-microscopic study on three human brains and a macaque. Biol Cybern 108:541–557. https://doi.org/10.1007/s00422-014-0626-2
Little GJ, Heath JW (1994) Morphometric analysis of axons myelinated during adult life in the mouse superior cervical ganglion. J Anat 184(Pt 2):387–398
Maco B, Cantoni M, Holtmaat A, Kreshuk A, Hamprecht FA, Knott GW (2014) Semiautomated correlative 3D electron microscopy of in vivo-imaged axons and dendrites. Nat Protoc 9:1354–1366. https://doi.org/10.1038/nprot.2014.101
Marzan DE, West BL, Salzer JL (2018) Microglia are necessary for toxin-mediated demyelination and activation of microglia is sufficient to induce demyelination. https://doi.org/10.1101/501148
Mason JL, Langaman C, Morell P, Suzuki K, Matsushima GK (2001) Episodic demyelination and subsequent remyelination within the murine central nervous system: changes in axonal calibre. Neuropathol Appl Neurobiol 27:50–58
Mollink J et al (2017) Evaluating fibre orientation dispersion in white matter: comparison of diffusion MRI, histology and polarized light imaging. Neuroimage 157:561–574. https://doi.org/10.1016/j.neuroimage.2017.06.001
Neuman C (1974) Spin echo of spins diffusing in a bounded medium. J Chem Phys 60:4508–4511
Novikov DS, Jensen JH, Helpern JA, Fieremans E (2014) Revealing mesoscopic structural universality with diffusion. Proc Natl Acad Sci USA 111:5088–5093. https://doi.org/10.1073/pnas.1316944111
Novikov DS, Fieremans E, Jespersen SN, Kiselev VG (2018a) Quantifying brain microstructure with diffusion MRI: theory and parameter estimation. NMR Biomed. https://doi.org/10.1002/nbm.3998
Novikov DS, Kiselev VG, Jespersen SN (2018b) On modeling. Magn Reson Med 79:3172–3193. https://doi.org/10.1002/mrm.27101
Novikov DS, Veraart J, Jelescu IO, Fieremans E (2018c) Rotationally-invariant mapping of scalar and orientational metrics of neuronal microstructure with diffusion MRI. Neuroimage. https://doi.org/10.1016/j.neuroimage.2018.03.006
Perge JA, Koch K, Miller R, Sterling P, Balasubramanian V (2009) How the optic nerve allocates space, energy capacity, and information. J Neurosci 29(24):7917–7928
Politis A (2016) Microphone array processing for parametric spatial audio techniques. http://urn.fi/URN:ISBN:978-952-60-7037-7
Reisert M, Kellner E, Dhital B, Hennig J, Kiselev VG (2017) Disentangling micro from mesostructure by diffusion MRI: a Bayesian approach. Neuroimage 147:964–975. https://doi.org/10.1016/j.neuroimage.2016.09.058
Ronen I, Budde M, Ercan E, Annese J, Techawiboonwong A, Webb A (2014) Microstructural organization of axons in the human corpus callosum quantified by diffusion-weighted magnetic resonance spectroscopy of N-acetylaspartate and post-mortem histology. Brain Struct Funct 219:1773–1785. https://doi.org/10.1007/s00429-013-0600-0
Salo RA, Belevich I, Manninen E, Jokitalo E, Grohn O, Sierra A (2018) Quantification of anisotropy and orientation in 3D electron microscopy and diffusion tensor imaging in injured rat brain. Neuroimage 172:404–414. https://doi.org/10.1016/j.neuroimage.2018.01.087
Schilling K, Janve V, Gao Y, Stepniewska I, Landman BA, Anderson AW (2016) Comparison of 3D orientation distribution functions measured with confocal microscopy and diffusion. MRI Neuroimage 129:185–197. https://doi.org/10.1016/j.neuroimage.2016.01.022
Schilling KG, Janve V, Gao Y, Stepniewska I, Landman BA, Anderson AW (2018) Histological validation of diffusion MRI fiber orientation distributions. and dispersion. Neuroimage 165:200–221. https://doi.org/10.1016/j.neuroimage.2017.10.046
Schneider R, Weil W (2008) Stochastic and integral geometry. Springer, Berlin
Sepehrband F, Alexander DC, Clark KA, Kurniawan ND, Yang Z, Reutens DC (2016a) Parametric probability distribution functions for axon diameters of corpus callosum. Front Neuroanat 10:59. https://doi.org/10.3389/fnana.2016.00059
Sepehrband F, Alexander DC, Kurniawan ND, Reutens DC, Yang Z (2016b) Towards higher sensitivity and stability of axon diameter estimation with diffusion-weighted MRI. NMR Biomed 29:293–308. https://doi.org/10.1002/nbm.3462
Shepherd GM, Raastad M, Andersen P (2002) General and variable features of varicosity spacing along unmyelinated axons in the hippocampus and cerebellum. Proc Natl Acad Sci USA 99:6340–6345. https://doi.org/10.1073/pnas.052151299
Sommer C, Straehle C, Koethe U, Hamprecht FA (2011) Ilastik: interactive learning and segmentation toolkit. In: Biomedical imaging: from nano to macro, 2011 IEEE international symposium on IEEE, pp 230–233
Sotiropoulos SN, Behrens TE, Jbabdi S (2012) Ball and rackets: inferring fiber fanning from diffusion-weighted. MRI Neuroimage 60:1412–1425. https://doi.org/10.1016/j.neuroimage.2012.01.056
Stikov N, Perry LM, Mezer A, Rykhlevskaia E, Wandell BA, Pauly JM, Dougherty RF (2011) Bound pool fractions complement diffusion measures to describe white matter micro and macrostructure. Neuroimage 54:1112–1121. https://doi.org/10.1016/j.neuroimage.2010.08.068
Stikov N et al (2015) In vivo histology of the myelin g-ratio with magnetic resonance imaging. Neuroimage 118:397–405. https://doi.org/10.1016/j.neuroimage.2015.05.023
Straehle CN, Kothe U, Knott G, Hamprecht FA (2011) Carving: scalable interactive segmentation of neural volume electron microscopy images. Med Image Comput Comput Assist Interv 14:653–660
Sturrock RR (1980) Myelination of the mouse corpus callosum. Neuropathol Appl Neurobiol 6:415–420
Sun D, Roth S, Black MJ (2010) Secrets of optical flow estimation and their principles. In: Computer vision and pattern recognition (CVPR), 2010 IEEE conference on IEEE, pp 2432–2439
Sun D, Roth S, Black MJ (2014) A quantitative analysis of current practices in optical flow estimation and the principles behind them. Int J Comput Vis 106:115–137
Tang-Schomer MD, Johnson VE, Baas PW, Stewart W, Smith DH (2012) Partial interruption of axonal transport due to microtubule breakage accounts for the formation of periodic varicosities after traumatic axonal injury. Exp Neurol 233:364–372. https://doi.org/10.1016/j.expneurol.2011.10.030
Tariq M, Schneider T, Alexander DC, Gandini Wheeler-Kingshott CA, Zhang H (2016) Bingham-NODDI: mapping anisotropic orientation dispersion of neurites using diffusion. MRI Neuroimage 133:207–223. https://doi.org/10.1016/j.neuroimage.2016.01.046
Tournier JD, Calamante F, Connelly A (2007) Robust determination of the fibre orientation distribution in diffusion MRI: non-negativity constrained super-resolved spherical deconvolution. Neuroimage 35:1459–1472. https://doi.org/10.1016/j.neuroimage.2007.02.016
Veraart J, Fieremans E, Novikov DS (2018a) On the scaling behavior of water diffusion in human brain white matter. Neuroimage. https://doi.org/10.1016/j.neuroimage.2018.09.075
Veraart J, Novikov DS, Fieremans E (2018b) TE dependent diffusion imaging (TEdDI) distinguishes between compartmental T-2 relaxation times. Neuroimage 182:360–369. https://doi.org/10.1016/j.neuroimage.2017.09.030
West KL, Kelm ND, Carson RP, Does MD (2015) Quantitative analysis of mouse corpus callosum from electron microscopy images. Data Brief 5:124–128. https://doi.org/10.1016/j.dib.2015.08.022
West KL, Kelm ND, Carson RP, Does MD (2016) A revised model for estimating g-ratio from MRI. Neuroimage 125:1155–1158. https://doi.org/10.1016/j.neuroimage.2015.08.017
Wilke SA et al (2013) Deconstructing complexity: serial block-face electron microscopic analysis of the hippocampal mossy fiber synapse. J Neurosci 33:507–522. https://doi.org/10.1523/JNEUROSCI.1600-12.2013
Womersley RS (2017) Efficient spherical designs with good geometric properties. Contemporary computational mathematics - A celebration of the 80th birthday of Ian Sloan. Springer, Cham, pp 1243–1285
Yang HJ, Vainshtein A, Maik-Rachline G, Peles E (2016) G protein-coupled receptor 37 is a negative regulator of oligodendrocyte differentiation and myelination. Nat Commun 7:10884. https://doi.org/10.1038/ncomms10884
Zaimi A, Wabartha M, Herman V, Antonsanti PL, Perone CS, Cohen-Adad J (2018) AxonDeepSeg: automatic axon and myelin segmentation from microscopy data using convolutional neural networks. Sci Rep 8:3816. https://doi.org/10.1038/s41598-018-22181-4
Zhang H, Schneider T, Wheeler-Kingshott CA, Alexander DC (2012) NODDI: practical in vivo neurite orientation dispersion and density imaging of the human brain. Neuroimage 61:1000–1016. https://doi.org/10.1016/j.neuroimage.2012.03.072
Acknowledgements
We would like to thank the NYULH DART Microscopy Lab Alice Liang, Kristen Dancel-Manning and Chris Patzold for their expertise in electron microscopy work, Kirk Czymmek and Pal Pedersen from Carl Zeiss for their assistance of 3d EM data acquisition, and Marios Georgiadis for the discussion of the myelin structure change caused by tissue preparations. It is also a pleasure to thank Markus Kiderlen from Aarhus University and Valerij Kiselev from University Medical Center Freiburg for a discussion on the relation between 2-dimensional and 3-dimensional axonal dispersions; Markus Kiderlen has also kindly provided the reference on the relation between the Steiner compact and the cosine transform of the FOD discussed in Appendix C. Jelle Veraart is a Postdoctoral Fellow of the Research Foundation - Flanders (FWO; grant number 12S1615N). Research was supported by the National Institute of Neurological Disorders and Stroke of the NIH under award number R21 NS081230 (Fieremans, E., Novikov, D. S., and Kim, S. G.) and R01 NS088040 (Fieremans, E. and Novikov, D. S.), and was performed at the Center of Advanced Imaging Innovation and Research (CAI2R, http://www.cai2r.net), an NIBIB Biomedical Technology Resource Center (NIH P41 EB017183, Fieremans, E., Novikov, D. S., and Kim, S. G.).
Funding
This study was supported by the National Institute of Neurological Disorders and Stroke of the NIH under award number R21 NS081230 (Fieremans, E., Novikov, D. S., and Kim, S. G.) and R01 NS088040 (Fieremans, E. and Novikov, D. S.), and was performed at the Center of Advanced Imaging Innovation and Research (CAI2R, http://www.cai2r.net), an NIBIB Biomedical Technology Resource Center (NIH P41 EB017183, Fieremans, E., Novikov, D. S., and Kim, S. G.).
Author information
Authors and Affiliations
Corresponding author
Ethics declarations
Conflict of interest
The authors declare that they have no conflict of interest.
Ethical approval
All procedures performed in studies involving animals were in accordance with the ethical standards of New York University School of Medicine. All mice were treated in strict accordance with guidelines outlined in the National Institutes of Health Guide for the Care and Use of Laboratory Animals, and the experimental procedures were performed in accordance with the Institutional Animal Care and Use Committee at the New York University School of Medicine. This article does not contain any studies with human participants performed by any of the authors.
Informed consent
Not applicable.
Additional information
Publisher’s Note
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Appendices
Appendix A: The myelin thickness upper bound used for the segmentation could influence g-ratio estimations
The estimated g-ratio values could be influenced by the myelin thickness upper bound used for dilating the segmented IAS to further segment the myelin sheath (“Myelin sheath and g-ratio”, “Materials and methods”). In Fig. 7, six different upper bound values, varying from 0.1 to 0.6 µm, are used to segment the myelin sheath and calculate the mean g-ratio, ranging from 0.77 to 0.55, indicating that the upper bound has to be carefully chosen for an accurate g-ratio estimation. A small upper bound (e.g., Fig. 7, upper left) could lead to a underestimated myelin thickness and an overestimated g-ratio; in contrast, a large upper bound (e.g., Fig. 7, upper right) could lead to an overestimated myelin thickness and a underestimated g-ratio.
Appendix B: Axonal diameter estimates per various definitions
In this section, distributions of axonal diameters are shown based on different definitions, such as equivalent circle diameter (Fig. 8a), short and long axis length of the fitted ellipse (Fig. 8b, c), and inscribed circle diameter (Fig. 8d). To compare with a previous study (Sepehrband et al. 2016a), we fitted the axonal diameter histogram to Gamma distribution and generalized extreme value (GEV) distribution in Fig. 8, which shows that GEV distribution fits better to the experimental diameter distribution (of all four definitions) than Gamma distribution does, consistent with the conclusion in (Sepehrband et al. 2016a). Also, GEV distribution has a longer tail than Gamma distribution does for thick axons in diameters > 3–5 µm, manifested by semi-logarithmic plots of diameter distributions in the bottom row of Fig. 8.
Appendix C: Relations between 2d and 3d dispersion angles
The purpose of this Appendix is to relate the 2d dispersion angle \({\theta _{2d}}\) derived from 2d histology (using, e.g., structure tensor) to the 3d dispersion angle \({\theta _{3d}}\) (defined, e.g., as \({\theta _{{\text{eff}}}}\) or \({\theta _{{p_2}}}\) in the main text). It is quite obvious that, generally, \({\theta _{2d}} \leq {\theta _{3d}}\), since the projection onto a plane removes part of the orientational variance (in the direction transverse to that plane). Here we address this relation quantitatively, and also estimate the 2d dispersion angle in terms of the 3-dimensional FOD’s SH coefficients and rotational invariants.
Aligning the z-axis with the main direction of a fiber bundle, the \(i\)-th fiber segment is defined by the polar and azimuthal angles \(\left( {{\theta _i},{\phi _i}} \right)\). Its 2d projection angle \(\theta _{i}^{'}=\theta _{i}^{'}({\theta _i},{\phi _i})\) within a plane (e.g., x–z plane in Fig. 9a) parallel to the main direction (z-axis), can be determined as
We now define the 2d dispersion angle. One can average the above \(\theta _{i}^{'}\) over the FOD,
such that
or, alternatively, adopt the above Taylor approximation as a definition, since it is actually more natural to average \(\cos ^{2} \theta _{i}^{'}\) rather than the angle itself, as \(\cos ^{2} \theta _{i}^{'}\) corresponds to the structure tensor component.
The FOD average will be performed in two steps. First, we average \({\cos ^2}\theta _{i}^{'}\) over the azimuthal angle \({\phi _i}\). This can be explicitly done if the FOD is axially symmetric. We also note that random histological sampling performed on a sufficiently large scale effectively performs such azimuthal averaging. The azimuthal averaging can be performed exactly for any fixed \({\theta _i}\):
Hence, we explicitly see that the azimuthal 2d dispersion variance is given by the first power of \(\cos {\theta _i}\), which is greater than the 3d variance \({\cos ^2}{\theta _i}\), corresponding to a narrower 2d dispersion, \({\theta _{2d}} \leq {\theta _{3d}}\), cf. Equation (6) of the main text.
At the second step, we average Eq. (7) over the remaining polar angle \({\theta _i}\) to obtain \({\cos ^2}{\theta _{2d}}=\left\langle {|\cos {\theta _i}|} \right\rangle\). We can already see that for narrow FODs, Taylor-expanding up to \(\left\langle {\theta _{i}^{2}} \right\rangle \simeq \theta _{{3d}}^{2}\), we find \({\theta _{2d}} \simeq {\theta _{3d}}/\sqrt 2\), which is just a statement that the variance of the axial radius \(\langle{x^2}+{y^2}\rangle=2\langle{x^2}\rangle\) is given by twice the variance of its x- or y-coordinate. Note, however, that this approximation ceases to be correct for the higher orders of \(\theta\), essentially because of the non-trivial denominator \(\sqrt {{x^2}+{z^2}}\) in the definition of \(\cos \theta _{i}^{'}\), as opposed to \(\sqrt {{x^2}+{y^2}+{z^2}} =1\).
To estimate the 2d dispersion angle based on FOD’s SH coefficients \({p_{lm}}\) in Eq. (2), we average the right-hand side of Eq. (7), where only the \(m\) = 0 SH contribute due to the axial symmetry. Using Eq. (2) and \({Y_{l0}}\left( \theta \right)=\sqrt {\frac{{2l+1}}{{4\pi }}} {P_l}\left( {\cos \theta } \right)\), where \({P_l}\left( {\cos \theta } \right)\) are the Legendre polynomials, we obtain
where the integral
can be evaluated using the generating function of Legendre polynomials \(\frac{1}{{\sqrt {1 - 2tz+{t^2}} }}=\mathop \sum \nolimits_{l} {P_l}\left( z \right){t^l}\), such that \(\mathop \int \nolimits_{0}^{1} \frac{z}{{\sqrt {1 - 2tz+{t^2}} }}~{{\rm d}}z=~\mathop \int \nolimits_{{ - \infty }}^{\infty } \frac{{{{\rm d}}\lambda }}{{\sqrt \pi }}~\mathop \int \nolimits_{0}^{1} z{{\rm d}}z~{{{\rm e}}^{ - {\lambda ^2}(1 - 2tz+{t^2})}}\) and the subsequent integral is reduced to a few Euler’s Gamma functions.
Finally, we use the definition in Eq. (3) to express \({p_{l0}}\) via the rotational invariants \({p_l}\), when the other \(m\) ≠ 0 FOD harmonics are either zero (axial symmetry) or negligible. As a result, we find
It is important to note that the 2d dispersion angle \({\theta _{2d}}\) appears to depend on the SH and rotational invariants \({p_l}\) with all \(l\), in contrast to the 3d dispersion angle \({\cos ^2}{\theta _{3d}}=(2{p_2}+1)/3\) in Eqs. (4a, 4b), which only involves the irreducible representation of the SO(3) group of rotations with the weight \(l\) = 2. It is quite obvious that the 3d definition of the dispersion angle is more natural (after all, the FOD is a 3-dimensional object), and mathematically, it is a better quantity, since it only depends on the \(l\) = 2 invariant, and does not mix the irreducible representations of SO(3). The above equation gives the precise way to compare 2d and 3d FOD estimates.
Figure 9b shows that the predicted 2d dispersion angle based on rotational invariants and Eq. (9) is close to the value calculated by projecting fiber segments on 2d planes, with only 3% error due to a lack of perfect axial symmetry of our FOD.
We note that Eq. (7) derived above has an interesting geometric meaning. Its right-hand side, averaged over the FOD, provides the cosine transform of the FOD [cf. Eq.(8) above], with respect to the z-axis. We now recall that the cosine transform of the FOD, multiplied by the length-to-volume ratio of all fiber segments, equals to the number density of intersections of the fibers by the x–y plane. This statement is intuitively obvious (fiber length projected onto the z-axis contributes to the intersection); it is rigorously discussed for the point processes, e.g., in Eq. (4.40) of the book (Schneider and Weil 2008). This statement is valid in any basis, and serves as a foundation for constructing the Steiner compact, which is an equivalent FOD representation. In other words, the FOD, whose direct estimation relies on calculating the gradients to determine the local directions, through the cosine transform is related to a simpler, counting problem, of calculating the numbers of intersections by all possible planes. Going back from the Steiner compact to the FOD by inverting the cosine transform is essentially rederived above, cf. the right-hand side of Eq. (9). Remarkably, we can see that the left-hand side of Eq. (7) relates the Steiner compact to the structure tensor calculation in the x–z plane. This means that the angular-averaged 2d structure tensor calculation (in any plane parallel to z) can also be performed as a counting problem, by counting the density of fiber intersections by the plane orthogonal to z.
Rights and permissions
About this article
Cite this article
Lee, HH., Yaros, K., Veraart, J. et al. Along-axon diameter variation and axonal orientation dispersion revealed with 3D electron microscopy: implications for quantifying brain white matter microstructure with histology and diffusion MRI. Brain Struct Funct 224, 1469–1488 (2019). https://doi.org/10.1007/s00429-019-01844-6
Received:
Accepted:
Published:
Issue Date:
DOI: https://doi.org/10.1007/s00429-019-01844-6