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Mechanical forces play an important role during brain development. In the early embryo, the anterior end of the neural tube enlarges and differentiates into the major brain subdivisions, including three expanding vesicles (forebrain, midbrain, and hindbrain) separated by two constrictions. Once the anterior neuropore and the spinal neurocoel occlude, the brain tube undergoes further regional growth and expansion in response to increasing cerebrospinal fluid pressure. Although this is known to be a response to mechanical loads, the mechanical properties of the developing brain remain largely unknown. In this work, we measured regional opening angles (due to residual stress) and stiffness of the embryonic chick brain during Hamburger-Hamilton stages 11–13 (approximately 42–51 hr incubation). Opening angles resulting from a radial cut on transverse brain slices were about 40°–110° (depending on region and stage) and served as an indicator of circumferential residual stress. In addition, using a custom-made microindentation device and finite-element models, we determined regional indentation stiffnesses and material properties. The results indicate that the modulus is relatively independent of position and stage of development, with the average shear modulus being about 220 Pa for stages 11–13 chick brains. Information on the regional material properties of the early embryonic brain will help illuminate the process of early brain morphogenesis.
Early development of the embryonic chick brain closely resembles that of the embryonic human brain [1,2,3,4]. In both cases the brain expands and differentiates at the anterior end of the neural tube into several major subdivisions, including three bulging vesicles or “hills” (prosencephalon or forebrain, mesencephalon or midbrain, and rhombencephalon or hindbrain) (Fig. 1d). The hills are separated by the forebrain-midbrain (FM) and midbrain-hindbrain (MH) constrictions or “valleys” (Fig. 1d). Once the brain cavity is sealed by occlusion of the anterior neuropore and the spinal neurocoel (by Hamburger-Hamilton  stage 12 for the chick brain), the brain tube undergoes further regional growth and expansion (Fig. 1). Proper vesicle expansion is a crucial step in normal brain development, as anomalies in this process are linked to severe neurological disorders, including hydrocephalus (abnormal vesicle enlargement caused by excessive accumulation of cerebrospinal fluid) and anencephaly (absence of most of the brain caused by a defect in neural tube closure).
While the morphological changes that occur during early brain development are well known, the mechanisms of vesicle formation and enlargement remain unclear. After the chick brain cavity is sealed (by stage 12), a cerebrospinal fluid pressure of about 2–3 mm H2O has been measured, and it increases gradually as brain development proceeds [6,7]. During the same period, rapid cavity expansion and tissue growth occur . It has been shown that the luminal pressure is necessary for early brain enlargement, as removal of normal pressure by intubation results in reduced growth and cavity size . The dependence of early brain growth on pressure is further demonstrated by immediate brain expansion that follows precocious occlusion of the spinal neurocoel before stage 11 . Therefore, mechanical forces play an important role in early brain development.
The early brain tube is composed of a single layer of neural stem cells called the neuroepithelium . The nuclei of these cells migrate radially within the cell body during the cell cycle forming a pseudo-stratified structure . The nuclei are located near the outside surface of the brain tube where DNA synthesis occurs. They move toward the lumen as the cell cycle proceeds and are close to the luminal side of the brain when mitosis occurs. During morphogenesis compressive stresses slow, whereas tensile stresses increase, cell proliferation (see review by Wozniak and Chen ). It has also been shown that sustained pressure promotes higher neuroepithelial proliferation [3,6]. Therefore, rapid proliferation of the neuroepithelium could result from tensile stresses in the early brain caused by increasing pressure. However, the stress distribution in the embryonic brain has not yet been determined. Mean wall stresses can be estimated using Laplace’s law, but detailed transmural distributions must be computed using a more complex model, which requires information on residual stresses (stresses in the tissue when all external loads are removed) and material properties. Such data for the early brain tube are not yet available.
In this work, we measured regional opening angles (residual stress) and stiffness of the embryonic chick brain during Hamburger-Hamilton stages 11–13 (approximately 42–51 hr incubation). Opening angles of 40°–110° (depending on region and stage) were measured following transmural cuts in thin brain slices. In addition, using a custom-made microindentation device, we probed the regional stiffness of the brain tube, and finite element models provided estimates for the modulus of the brain at different stages. Information on the regional material properties should help illuminate mechanical processes in early brain morphogenesis.
Fertile White Leghorn chicken eggs (Sunrise Farms, Catskill, NY) were incubated at 38°C for 42–52 hours to yield embryos at stages 11, 12, and 13 (Figs. 1a–c) of Hamburger and Hamilton . Embryos were extracted from the eggs using Whatman filter paper rings  and washed in phosphate-buffered saline (PBS) solution at room temperature. The differentiated brain regions along each embryonic neural tube can easily be identified under the microscope (Figs. 1d–f).
Thin slices (approximately 100 μm in thickness) were obtained by cutting the brain tube transversely with a pair of fine spring scissors (Fine Science Tools, Foster City, CA) (Fig. 2a). Dissections revealed that surrounding head mesenchyme can affect the opening angles of the brain slices (Figs. 2d–f). Hence, most of these tissues were removed from the brain slice using sharp glass micropipettes (Fig. 2b). The scissors were then used to make a radial (transmural) cut on the dorsal side of the brain slice (Fig. 2c) to release circumferential residual stress. The resulting approximate zero-stress state of the brain slice was characterized by the opening angle (θ) between two radii joining the midpoint to the two tips of the inner wall (see Fig. 2c). The opening angle was measured from an image acquired about 15 min after the radial cut. All the microdissection experiments were conducted in PBS at room temperature. Due to complications from the optic vesicles, sections from the forebrain region are not included.
All the samples in Figs. 1 and and22 were imaged with a video camera (COHU, Model 4915, San Diego, CA) mounted on a dissecting microscope (Leica Microsystems, Model MZ8, Bannockburn, IL). Images were acquired by a frame grabber (FlashBus MV, Integral Technologies, Indianapolis, IN) and imaging software (SigmaScan Pro V.5.0, Systat Software, San Jose, CA).
At each stage, 7–10 slices were obtained for each region, except the MH valley region at stage 13 (4 slices). To compare opening angles between regions at a certain stage or between stages at a certain region, one-way ANOVA tests were used followed by Tukey’s all-pair comparison. For all statistical analyses, 0.05 was chosen as the significance level.
Regional stiffness of the brain tube at each developmental stage was probed by a custom-made microindentation device, which had been previously designed for testing the embryonic chicken heart . Briefly, one end of a glass cantilever beam (about 66 μm in diameter) is attached to a piezoelectric stage (PZS-200, Burleigh Instruments, Fishers, NY) through a rigid glass pipette. The other (free) end is joined perpendicularly to a short glass cylindrical indenter tip (with a flat face about 20 μm in diameter). A manually-marked ink spot on the indenter tip was used to track its displacement (Fig. 3a). The beam stiffness was measured to be about 1 mdyn/μm (10 nN/μm).
After removing most of the surrounding tissues, the brain tube was isolated from the embryo by removing the part of the neural tube below the hindbrain region. Hence, all tests were conducted on brains with no internal pressure. The ventral side of the brain at a given region was held by suction on a glass pipette (about 100 μm in diameter) and positioned under the microscope with a micromanipulator. The indenter tip was positioned directly opposite the glass pipette to indent the dorsal side of the brain, perpendicular to the brain surface (Fig. 3a). The piezoelectric stage was controlled by an amplified 0.1-Hz sawtooth-like voltage signal. The beam and the indenter tip were then driven to approach or retract away from the brain tube at a speed of approximately 46 μm/s. The initial distance of the brain tube and the indenter tip was controlled such that the indenter tip either would not touch the brain tube when approaching (control) or would gently indent the brain tube at the specified region (Fig. 3b). All microindentation experiments were conducted at room temperature, with the sample brain, the cantilever beam and the indenter tip submerged in PBS. The dorsal side of the brain is ideal for indentation because there is little mesenchymal tissue on this side.
The displacements of the indenter tip during control and indentation were obtained from video micrographs by tracking the ink spot on the indenter tip, from which the beam deflection and tissue indentation depth were determined (Fig. 3c). The product of beam deflection and beam stiffness yields the indentation force (see Fig. 3c and  for more detail). Finally, the slope of a linear regression of the approximately straight force-indentation curve (up to 10 μm) yielded the stiffness of the brain at the indented region (Fig. 3d). At each stage, the stiffness in each region was obtained from 5–11 chick embryos. One-way ANOVA tests were used to compare the regional indentation stiffness at each stage.
Regional stiffness depends on both material properties and geometry. In addition to microindentation tests, finite element models are needed to estimate the material properties of the brain. Three types of models were created:
It is important to note that, although the indentation depth in the experiments is relatively small compared to the wall thickness, large strains can occur close to the indenter. Hence, all models in this paper include the nonlinearities associated with large deformations.
To get a sense for the significance of residual stress in our stiffness measurements, we studied two limiting cases that can be simulated in two dimensions (2D) – a cylinder in plane strain and a sphere undergoing axisymmetric deformation. For these preliminary parametric studies, 2D models are highly desirable because they are significantly more efficient to build and run than comparable 3D models. The sphere is the simplest geometry that can capture the effects of residual stress on indentation in a 2D finite element model. The cylinder model was used to obtain the residual stress distribution in a brain slice that would produce an opening angle close to the experimental mean for the stage-12 midbrain. A similar residual stress distribution was then introduced in the sphere model, which was indented.
First, we created a nonlinear plane-strain (cylinder) model for a section of a stage-11 chick midbrain using the commercial finite element software COMSOL Multiphysics (V.3.3, COMSOL AB). Residual stress was introduced by specifying volumetric growth across the wall to achieve geometry and opening angles similar to those measured for the stage-12 midbrain (Fig. 4a, b). Due to symmetry, only half of the brain was analyzed, with appropriate symmetry conditions specified. Growth was simulated using the theory presented by Rodriguez et al. , which can be readily implemented in COMSOL (see details in Taber, 2008 ). Briefly, starting with the zero-stress configuration (the smaller outline in Fig. 4a), each material element grows according to a specified growth deformation gradient tensor Fg. Geometric compatibility among elements requires elastic deformation Fe that in turn causes residual stresses in the unloaded brain. Thus, the total deformation is described by F = Fe·Fg (Fg = I for no net growth with I being the identity tensor). The major deformation variable is F, Fg is specified, and the stresses depend on Fe = F·Fg−1. Here, axisymmetric growth was specified in the radial and circumferential directions, i.e., Fg = λgrerer+λgθeθeθ, where the λgi are growth stretch ratios relative to the undeformed cylindrical polar coordinates (r, θ), and ei are the corresponding local unit vectors . For representative material properties (see below), the following differential growth was found to produce proper brain geometry (radius and wall thickness) and opening angle (one of the two vertical boundaries was set free) in the cylinder model: λgr = 1.4 and λgθ = 1+0.5·(ro/r−1), where ro is the undeformed outer radius of the brain section (Fig. 4a, b).
To a first approximation, the neuroepithelium is assumed to be an isotropic, nearly incompressible, pseudoelastic material characterized by the modified neo-Hookean strain-energy density function
where μ and κ are the small-strain shear and bulk modulus respectively, I1 is the first invariant of the right Cauchy-Green deformation tensor (given by FeT·Fe), Je = det Fe is the elastic volume ratio, and p is a penalty variable introduced for nearly incompressible materials. The Cauchy stress tensor is given by the constitutive relation σ = Je−1 Fe·W/FeT, and stresses are normalized relative to the shear modulus (e.g., circumferential stress σθ*= σθ/μ in Fig. 4). For numerical stability, we took the bulk modulus (κ) to be three orders of magnitude larger than μ.
Local indentation cannot be simulated in a plane-strain model for a cylinder because deformation would be imposed along the entire length of the cylinder. Hence, using results from the cylindrical model, we next developed a spherical indentation model as a simple representation for a brain vesicle. Axisymmetric deformation is assumed, i.e., all variables depend only on the radial and meridional coordinates r and θ, respectively (ϕ is the circumferential coordinate). With the initial cross-sectional geometry taken to be the same as that of the cylinder model, the following growth was found to produce geometry and residual stress distributions in the sphere model similar to those in the cylinder model: λgr = 1.24 and λgθ = λgϕ = 1+0.3·(ro/r−1). Following growth, a small circular boundary (10-μm radius) on top of the sphere was specified to move downwards, mimicking the indentation, while an area (100 μm in diameter) on the opposite side was fixed to simulate the pipette support (Fig. 4c). Stiffness is defined as the slope of the linear regression fit to the force-displacement curve (Fig. 4e; regressions not shown).
In addition, the geometry after growth (close to the average size of the stage-12 midbrain) was used to establish another spherical indentation model that contained no residual stress (not shown). The indentation results from these two models were compared to examine how residual stress affects the indentation stiffness.
To estimate material properties from the microindentation experiments, nonlinear 3-D finite element models for the stage 11–13 chicken brain were created, using the finite element software ABAQUS (v.6.7, Abaqus, Inc.). For simplicity, because the above 2-D models show that residual stress has little effect on the measured stiffness (see Results), residual stresses are not included in these models. The models resemble the overall morphology of the chick brain at each stage, but the optic vesicles in the forebrain are not included (Fig. 5a–c). Due to symmetry, only one longitudinal half of the brain needs to be analyzed, with symmetry conditions specified accordingly. The indenter tip is simulated as a rigid cylinder, with frictionless contact specified between the surfaces on the indenter tip and the brain tube. A small circular area (100-μm diameter) of the brain tube on the opposite side of the indenter tip is fixed to simulate the pipette support (Fig. 5a). Other boundaries are free. The geometry is partitioned into 106 (order of magnitude) linear tetrahedral elements (Fig. 5), with the mesh being further refined near the indentation region (see close-up in Fig. 5e). The sufficiency of the mesh density was confirmed by solving the problem for increasing mesh densities. Similar procedures were adopted for all regions to be tested.
As a first approximation, we assume that all regions of the brain possess the same material properties. Again, the wall is assumed to be composed of an isotropic, nearly incompressible neo-Hookean material characterized by the shear modulus (μ) and bulk modulus (κ, three orders of magnitude larger than μ), respectively. The indentation stiffness was obtained by linearly fitting the initial force-indentation curve (up to 20-μm indentation).
At each stage, a value of the shear modulus was obtained for each region by matching the stiffness from the indentation model to the average stiffness for the same region from the experiments. These data were used to compute a mean shear modulus for each stage. For statistical comparison of shear moduli from different stages, one-way ANOVA test was used.
For better understanding of how local geometry (e.g., hills vs. valleys) of the brain tube affects the indentation results, we created several 3-D models in ABAQUS that possess the same cross sectional geometry (as the average stage-12 midbrain region) at the indentation site but different overall longitudinal curvatures (Fig. 6). These geometrical variations include longitudinally convex (part of a sphere), straight (cylinder), and concave curvatures relative to the indenter position (Fig. 6a–c, respectively). For comparison, an additional model of a smaller straight cylinder (not shown) was also created that possesses the same cross sectional geometry as the average stage-12 MH valley (the same wall thickness but only half the inner diameter of the midbrain section). Due to symmetry, only a quarter of the geometry was analyzed, with symmetry conditions specified accordingly. All other procedures for material, mesh, and indentation contact are similar to those discussed above for the 3-D brain models.
When a radial cut was made, the brain slice sprang open immediately (Fig. 2c). Overall, the average opening angles of the stage 11–13 chick brain sections (n = 7–10 for most regions at each stage) varied from 40° to 110° (Fig. 7a). At stage 11, opening angles were significantly different between midbrain hill (M) and midbrain-hindbrain valley (MH) (p < 0.005) and between forebrain-midbrain (FM) and MH valleys (p < 0.05). At stage 12, the only significant difference in opening angles was between midbrain hill and MH valley (p < 0.005). At stage 13, there was no significant difference in opening angles between regions (p > 0.1). From stage 11 to 13, only opening angles at the FM valley region changed significantly (p < 0.05).
Despite mixed statistical results, at each developmental stage the average opening angles in the hill regions tended to be larger than those in the narrower valley regions (Fig. 7a). For each region (except the FM valley) during development, the average opening angle seemed to increase first from stage 11 to 12, and then decrease to a smaller magnitude at stage 13.
The peak indentation depth in the experiments was about 10 μm, or about 15% of the wall thickness. The stiffness of the early chick brain from the microindentation tests ranged from ~0.4 to 1 mdyn/μm (n = 5–10 for each region at each stage) (Fig. 7b). At each developmental stage (11–13), variations of the indentation stiffness among different regions were not statistically significant, although there appears to be a general trend of increasing average stiffness for most regions as the brain develops (Fig. 7b).
Because the shape and size of the brain changes dramatically from stage 11 to 13 (Fig. 1), indentation stiffness alone cannot be used as an indicator for changes in material properties during development. Hence, given the geometry, the 3-D indentation model (Fig. 5) was used to estimate the shear modulus (μ) of the brain at each stage. As described in the Methods section, the value of μ for each region was determined by matching the stiffness from the indentation model to the average measured stiffness for the same region. These data then provided an average modulus for each stage. The average values of μ for stage 11–13 chick brains were about 201, 192, and 276 Pa, respectively (Fig. 7c). There was no significant change of wall shear modulus from stage 11 to 13 (p > 0.5). The overall average value of the shear modulus during the studied stages is about 220 Pa.
Next, we used the brain models for each stage (Fig. 5a–c), along with the average modulus for the same stage (Fig. 7c), to compute an indentation stiffness for each region. In general, the trends in the measured and computed stiffnesses agree reasonably well (Fig. 7b). These results suggest that the modulus is approximately independent of age and position during the studied stages.
Residual stress can greatly affect mechanical properties of soft tissue as determined from microindentation tests . The significance of these effects depends on the magnitude of the stress and the structure of the tissue. We used computational models to examine how residual stress affects embryonic brain mechanics. First, differential volumetric growth was specified in an unloaded cylinder to create residual stress with circumferential compression near the inner layers and tension near the outer surface (Fig. 4a). Simulating a radial cut released the residual stress (Fig. 4b), yielding a zero-stress arc characterized by an opening angle (116°) close to the average experimental value (108° for the stage-12 midbrain region). Next, growth was specified in a spherical model for a brain vesicle (Fig. 4c, d), yielding residual stresses similar to those in the cylinder model. The indentation stiffness for the sphere with residual stress was only about 3% higher than that given by indenting a stress free sphere of the same material and geometry (not shown) (Fig. 4e). These results indicate that residual stress has a relatively small effect on the stiffness probed by the microindentation tests. For simplicity, therefore, residual stress was not included in our 3-D models.
As expected, the stiffness of a cylinder with a given wall thickness increases as the radius decreases (see Fig. 6e for straight tube). Surprisingly, however, but consistent with our experimental measurements, the 3-D model predicts that hills and valleys have roughly the same indentation stiffness (Fig. 7b), despite having considerably different radii (for the same modulus and wall thickness). To investigate this phenomenon, we created several different models that possess different longitudinal curvature (Fig. 6a–c). Unless noted otherwise, the radius and the wall thickness at the indentation site are the same for all models as those for a stage-12 midbrain section. To simplify comparison, all the stiffness values are normalized by the indentation stiffness of the stage-12 midbrain, as provided by the realistic 3-D model shown in Fig. 5d. The results indicate that the stiffness of the convex cylinder (0.90) is higher than that of the straight (0.67) and concave cylinders (0.57) (Fig. 6d, e).
For the brain tube, these results suggest that, in a valley, stiffening due to a smaller radius (relative to a hill) is effectively cancelled by the softening effect of the concave curvature. These combined effects produce a brain tube of nearly uniform indentation stiffness (Fig. 7b).
During early development, the embryonic chick brain undergoes rapid growth and expansion in response to increasing luminal pressure, and the major subdivisions along the brain tube become more and more prominent (Fig. 1). To understand the mechanisms that drive morphogenesis of the brain tube, the mechanical response to the increasing cavity pressure must be determined. This requires knowledge of the mechanical properties of embryonic brain tissue, which have not been previously explored.
In this study, we found that considerable residual stress exists in the early chick brain, which can be characterized by the opening angle (Fig. 2). Although the variations are not statistically significant, the average opening angles at each stage seem to exhibit a pattern, i.e., larger opening angles in the hill regions and smaller ones in the valley regions (Fig. 7a). This spatial pattern might indicate differential growth between hill and valley regions. Moreover, our data indicate that the temporal change of the average opening angle for each region (except the FM valley) is similar to the change in the opening angle of blood vessels during pressure increase , whereby the angle first increases and then decreases. From these results, we speculate that the inner side of the neuroepithelium first grows in response to higher circumferential stress near the lumen from stage 11–12, giving higher residual compression near the inner radius and thus larger opening angles. By stage 13, the outer layers grow relatively faster, causing opening angles to decrease. However, unlike multi-layered blood vessels, the early brain is composed of only a single neuroepithelial cell layer. Therefore, the adaptation mechanisms of the early brain to increasing pressure may be different. This behavior warrants further study.
Surprisingly, at each stage the measured stiffness was approximately the same at all locations, despite considerable differences in geometry (Fig. 7b). Investigating this behavior with idealized models, we found that indentation stiffness is higher for convex curvature and smaller radius, but lower for concave curvature and larger radius (Fig. 6e). Hence, geometric effects in the hills (convex curvature and larger radius) and the valleys (concave curvature and smaller radius) essentially cancel out, giving nearly uniform indentation stiffness. Our measurements and calculations also suggest that the shear modulus is approximately uniform and independent of developmental stage (Fig. 7b, c).
It is important to note that these results were obtained for relatively small indentations; future work should determine nonlinear material properties of the brain from large-indentation tests. Nevertheless, it is interesting to consider the possibility that these characteristics result from some optimization principle in brain development. Even before the brain tube seals and cerebrospinal fluid pressure begins to rise, the brain tube contains relatively small but distinct vesicles (hills) separated by constrictions (valleys). Genetic and chemical activity may produce this initial pattern. Then, as the lumen pressure increases, Laplace’s law gives the average circumferential stress σθ = pr/h, where p is the pressure, r is the radius, and h is the wall thickness. Hence, for uniform h, the different radii dictate that the average stress in the hills is larger than in the valleys. If growth rate increases with stress , then the hills would grow faster than the valleys, leading to further relative expansion of the vesicles driven by positive feedback. Therefore, the geometric and mechanical characteristics of the brain tube may be optimized to facilitate brain vesicle expansion and differentiation in response to increasing cavity pressure.
A previous study has determined the nonlinear material properties of the stage-12 chick heart during cardiac looping . The average shear moduli of the chick myocardium and cardiac jelly at stage 12 are approximately 26 and 6 Pa, respectively . Thus, the shear modulus of the early chick brain is an order of magnitude greater than that of the heart. On the other hand, shear moduli for the embryonic chick brain are surprisingly similar to those (100–1000 Pa) measured for animals in various species and ages [19,20,21,22], despite dramatic differences in components and structure between embryonic and fully developed brains . The primary steps of the brain development include generation and differentiation of neurons from neural stem cells and their subsequent migration and maturation . Mature brains are composed of gray matter containing neuronal cell bodies and white matter containing interconnected axonal fibers. In general, mechanics of the mature brain is important in modeling and understanding of traumatic brain injury and neurosurgery . For example, during neurosurgical procedures, the human brain behaves like a compressible viscoelastic solid . All of these results, however, might be affected by various conditions during testing .
Residual stress was not included in our 3-D models. A previous study has shown that residual stress can greatly affect the stiffness and material properties determined from microindentation tests of soft tissue . For the brain tube, however, our models show that normal levels of residual stress have little effect on overall indentation stiffness.
The spatial distribution of residual stresses in the early brain, as manifested by opening angles, might provide an optimal mechanical environment for dividing neural stem cells. From a mechanics point of view, residual stresses can help make stress distributions relatively uniform across the wall of a pressurized tube, e.g., blood vessels . The wall of the early brain tube is composed of a single layer of pseudo-stratified neural stem cells or neuroepithelium . The nuclei of these cells migrate radially within the cell body during the cell cycle . The opening angle results show that circumferential residual stresses exist throughout the brain tube at all stages (Fig. 7a). With these residual stresses, the unloaded (stage 11) or initially-pressurized brain (stage 12) would be under tensile stresses in the outer layers and compressive stresses in the inner layers of the wall (Fig. 4a). Therefore, the nuclei are under tension when they are located near the outside of the brain tube where DNA synthesis occurs. The nuclei move towards the lumen as the cell cycle proceeds, and would be under compression near the luminal side of the brain when mitosis occurs. However, as tensile forces are usually generated during mitosis to separate the chromosomes , it is likely that overall compression in the inner layers of the early brain could hinder, if not control, the neural dividing process. During morphogenesis, compressive stresses generally reduce, whereas tensile stresses increase, proliferation rates (see review in ). As luminal pressure increases later during development [6,7], the inner layers of the brain tube would also be under tension, which could facilitate faster division of neural stem cells.
The above speculation is consistent with the following findings: (1) early brain enlargement requires luminal pressure ; (2) the brain cavity expands faster than the tissue grows at the beginning (stage 11–12) of brain enlargement (proliferation slowed by compression), but soon (after stage 13) the reverse is true (proliferation facilitated by tension) ; (3) sustained hyperpressure promotes higher mitotic activity .
Much work is needed to learn the role of mechanics in regulating proliferation of neural stem cells. Information provided in this study on the residual stress and material properties of the early brain will help illuminate the mechanical environment of such cells and the process of early brain morphogenesis.
We thank Krikor Dikranian for helpful discussions and suggestions. This work was supported by the National Science Foundation (grant DMS-0540701) and the National Institutes of Health (grant R01 GM075200).