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ABSTRACT AIMS: To determine the short-term effects of simulated microgravity on mesenchymal stem cell behaviors—as a function of clinorotation speed—using time-lapse microscopy. BACKGROUND:

Ground-based microgravity simulation can reproduce the apparent effects of weightlessness in spaceflight using clinostats that continuously reorient the gravity vector on a specimen,

creating a time-averaged nullification of gravity. In this work, we investigated the effects of clinorotation speed on the morphology, cytoarchitecture, and migration behavior of human

mesenchymal stem cells (hMSCs). METHODS: We compared cell responses at clinorotation speeds of 0, 30, 60, and 75 rpm over 8 h in a recently developed lab-on-chip-based clinostat system.

Time-lapse light microscopy was used to visualize changes in cell morphology during and after cessation of clinorotation. Cytoarchitecture was assessed by actin and vinculin staining, and

chemotaxis was examined using time-lapse light microscopy of cells in NGF (100 ng/ml) gradients. RESULTS: Among clinorotated groups, cell area distributions indicated a greater inhibition of

cell spreading with higher angular frequency (_P_<0.005), though average cell area at 30 rpm after 8 h became statistically similar to control (_P_=0.794). Cells at 75 rpm clinorotation

remained viable and were able to re-spread after clinorotation. In chemotaxis chambers, clinorotation did not alter migration patterns in elongated cells, but most clinorotated cells

exhibited cell retraction, which strongly compromised motility. CONCLUSIONS: These results indicate that hMSCs respond to clinorotation by adopting more rounded, less-spread morphologies.

The angular frequency-dependence suggests that a cell’s ability to sense the changing gravity vector is governed by the rate of perturbation. For migration studies, cells cultured in

clinorotated chemotaxis chambers were generally less motile and exhibited retraction instead of migration. SIMILAR CONTENT BEING VIEWED BY OTHERS CELLULAR MECHANOTRANSDUCTION OF HUMAN

OSTEOBLASTS IN MICROGRAVITY Article Open access 21 March 2024 IMPAIRMENT OF 7F2 OSTEOBLAST FUNCTION BY SIMULATED PARTIAL GRAVITY IN A RANDOM POSITIONING MACHINE Article Open access 07 June

2022 SIMULATED LUNAR MICROGRAVITY TRANSIENTLY ARRESTS GROWTH AND INDUCES OSTEOCYTE-CHONDROCYTE LINEAGE DIFFERENTIATION IN HUMAN WHARTON’S JELLY STEM CELLS Article Open access 04 May 2024

INTRODUCTION Intricate multi-scale interactions among cells, tissues, and organs fundamentally govern human health, which has evolved on Earth under a constant gravitational load of 1 g (9.8

 m/s2). The biological mechanisms underlying the role of gravity in human health remain poorly understood, but their elucidation is necessary for enabling long-term manned space exploration.

Numerous studies, supported by the National Aeronautics and Space Administration and other space agencies, have shown deleterious effects of space travel on the human body, such as

accelerated bone loss,1,2 muscle tissue degeneration,3 and others.4 Importantly, these observations may have broader implications beyond spaceflight applications to provide a more detailed

understanding of diseases on Earth. In particular, the musculoskeletal system has historically been a focal point in space biology research, because of the strikingly adverse changes that

occur in astronauts.5 More recently, studies have begun to investigate mesenchymal stem cells for their roles in musculoskeletal lineage determination,6 bone repair,7 and tissue

maintenance.8 Although the most relevant environment for performing microgravity research is in space, competition to use space-based facilities, like the International Space Station, is

fierce and is further complicated by substantial time and resource investments.9 As a result, lower-cost and logistically simpler alternatives are attractive and include sounding rockets10

and parabolic flights,11 or in-lab devices such as random positioning machines12 and clinorotation devices (clinostats)13 to simulate microgravity. The selection of a specific technique

usually depends on accessibility, cost, experimental design, and research question. Clinostats are among the most accessible methods to simulate microgravity, and they allow researchers to

study living cells using standard laboratory tissue culture supplies.14 Clinorotation experiments have provided significant insight into the behavior of biological organisms in space. The

technique was originally developed to study gravitropism in plant development, and has revealed that gravity serves a key role in statocyte function, which is believed to be directly

involved in plant gravisensing and growth patterns.15 In animal and human cells, clinorotation has been used to recreate experiments that would otherwise be challenging to perform in space,

such as high-resolution microscopy16 and assessment of stem cell differentiation.17 Cellular changes in microgravity have been associated with disruptions in the cytoskeleton and,

consequently, changes in cell morphology and behavior.18,19 Although clinorotation is a standard ground-based tool, previously reported studies on the effects of simulated microgravity in

mesenchymal stem cells have yielded conflicting findings (Table 1). For instance, some researchers have shown that microgravity enhances proliferation,17 whereas others have demonstrated

inhibition.20 Chondrogenic differentiation has also been found to be either promoted21 or suppressed.22 Similar inconsistencies have also been highlighted in a recent review.23 Some of these

observed discrepancies could be due to differences in culture media formulation and cell source, but it is also possible that the choice of clinorotation parameters used for an experiment

may substantially influence cell behavior. A two-dimensional clinostat rotates a sample along the longitudinal axis to produce a time-averaged nullification of the gravity vector.

Theoretically speaking, to simulate microgravity effectively, the period of rotation should be shorter than some time constant that governs the rate processes involved in the cellular

gravisensing machinery that enable a cell to ‘perceive’ and respond to the changing trajectory of the gravity vector. For conventional clinostats, however, there are also practical

considerations that limit the angular frequency of rotation.24 Specifically, rotation speed must be adjusted to balance sedimentation forces, centrifugal and Coriolis effects, and Stokes’

drag. Because of these constraints, the parameters of angular rotation depend on the particular design and implementation of each experimental system. To minimize the effects of these

extrinsic stimuli, we recently developed a lab-on-chip clinorotation device (clinochip, Figure 1a) that confines adhered cells within a small region along the axis of rotation, limiting

residual accelerations to levels below 10−4g at different rotation speeds.25 Moreover, the clinochip is amenable to time-lapse microscopy, which enables us to characterize the kinetics of

cell spreading, changes in morphology, and migration with minimal disruption to the simulated microgravity environment. In this study, we used this device to investigate how angular

frequency affects human mesenchymal stem cell (hMSC) behavior. On the basis of the concept that there are specific rate processes that govern cellular gravisensing (Figure 1b), we

hypothesize that hMSCs would exhibit angular frequency-dependent responses. The results of this work demonstrate that hMSCs can in fact ‘detect’ differences in rotation speed in a manner

that causes heterogeneous population shifts toward more rounded morphologies and retraction of cell area. This could have significant implications on our basic understanding of stem cell

regulation as well as on strategies that are being used in stem cell-based applications. MATERIALS AND METHODS MATERIALS hMSCs were obtained from a commercial source (PT-2501, Lonza,

Walkersville, MD, USA), and confirmed to be mycoplasma-free. Clinochip fabrication required microscope slides (12-544-1, Fisher Scientific, Waltham, MA, USA) and 0.25- mm-thick

polydimethylsiloxane sheets (HT-6240, Rogers Corporation, Rogers, CT, USA). Fluorescence visualization was performed for actin using 5% (w/v) Texas red phalloidin (Life Technologies,

Gaithersburg, MD, USA) and for focal adhesions using 1 μg/ml fluorescein-conjugated anti-vinculin (MA1–34629, Life Technologies). Fibronectin (354008, BD Biosciences, San Jose, CA, USA) was

used to enable cell adhesion, and nerve growth factor (NGF; 7S-NGF, Life Technologies) was used for migration experiments. Calcein-AM and ethidium homodimer-1 (L-3224, Life Technologies)

were used to perform cell viability assays. EXPERIMENTAL SETUP In general, we used a single experimental system for all of our experiments, as detailed previously.25 In brief, the system

consists of a custom microscope-mounted gear system, driven by a computer-controlled stepper motor that rotates a small slide holder.25 This slide holder can accommodate various custom and

commercially available lab-on-chip devices. A non-rotating slide holder enables having a static (standard gravity) control condition performed concurrently. The entire system is enclosed in

an environmental chamber (Precision Plastics, Beltsville, MD, USA) and installed on an Olympus IX-81 epi-fluorescence microscope (Center Valley, PA, USA). CELL MORPHOLOGY PLATFORM A custom

‘clinochip’ device was used for visualizing cell spreading (that is, changes in cell morphology over time), and fabricated according to our previously described protocol.25 This clinochip

consists of three layers comprising polydimethylsiloxane sandwiched between two layers of glass. In brief, we used a high-resolution razor cutter (FC8000, Graphtec, Irvine, CA, USA) to trim

stock polydimethylsiloxane sheets. The sheet was cut to length and width dimensions of microscope slides and with a single 1-mm wide, 30-mm long channel at the center. A second microscope

slide was used as the third layer. Prior to assembly, two 1-mm diameter holes had been made in the top slide using a sandblaster (6500, Airbrasive, Piscataway, NJ, USA) to provide access to

the channels. The three layers were energetically bonded using a high-frequency corona treater (BD-20AC, Electrotechnic Products, Chicago, IL, USA). The clinochip was first sterilized for 20

 min in a UV chamber. To promote cell attachment, the channel was then treated with 100 μg/ml fibronectin for 1 h and washed with phosphate-buffered saline before use. Passage 3 (P3) and P4

hMSCs were seeded into clinochip channels and incubated at 37 °C for 10 min to allow for cell attachment, followed by commencement of clinorotation. CELL MIGRATION PLATFORM Cell migration

was analyzed using commercially available Ibidi Chemotaxis slides (μ-Slide Chemotaxis 2D, Ibidi, Munich, Germany). The slides fit perfectly in our clinorotation device and the 2×1 mm

dimensions of the chamber are suitable for simulated microgravity, as they constrain cells to a narrow region about the axis of rotation to minimize centrifugal effects. First, a 100 μg/ml

fibronectin solution was injected into the viewing chamber and incubated for 1 h, followed by three phosphate-buffered saline washes. Then, P3 and P4 hMSCs were plated and incubated at 37 °C

for 12 h of initial seeding time. Our pilot experiments showed that after 12 h the spreading areas of hMSCs reach a plateau so that cell spreading would not confound the cell migration

data. As a first step, we chose to study hMSC chemotaxis mediated by NGF, one of several growth factors identified in this active field of research.26 Mesenchymal stem cells have been shown

to express receptors to neurotrophic factors including NGF,27 and also secrete NGF during tissue repair.28 In these migration experiments, NGF was prepared as a 100 ng/ml solution and

injected into the top ports of the chamber. Following manufacturer’s instructions, the same volume was aspirated from the opposite port to create a chemical gradient. CLINOROTATION AND

TIME-LAPSE IMAGING Both morphology and chemotaxis platforms were rotated along the axis of the channels in which cells were cultured. Residual accelerations are one to two orders of

magnitude smaller than conventional clinostats, even at 75 rpm.25 Before the experiment, we made sure that the channels did not contain any bubbles, to minimize any other external effects

such as shear stress and dehydration. During imaging, we constrained our analyses to cells near the axis of rotation, away from the sides of the channel, to avoid potential edge effects. At

the appropriate times (10 min after seeding for morphology assays; 12 h after seeding for chemotaxis and migration assays to allow the cells to become fully spread), clinorotation was

initiated at 30, 60, or 75 rpm and maintained over the course of 8 h. Clinochips at 0 rpm (non-rotated) were used as a control (standard gravity). During each hour, rotation was paused for a

total of 60 s, and a set of bright-field images of the clinochip were acquired at ×200 magnification. At the end of the 8 h period, cells were fixed in 4% paraformaldehyde, and

fluorescently stained for actin and vinculin. Captured images were analyzed using ImageJ (National Institutes of Health). CELL VIABILITY AND RECOVERY AFTER CLINOROTATION Cell viability was

determined using calcein-AM (green) to indicate intracellular esterase activity for live cells and ethidium homodimer-1 (red) to indicate loss of plasma membrane integrity for dead cells.

Calcein (final concentration 4 μM) and ethidium homodimer (final concentration 2 μM) were added to cell culture media that was used to plate hMSCs in fibronectin-treated clinochips. After 10

 min of attachment, clinochips were either rotated at 75 rpm or maintained at standard gravity conditions (non-rotated control) and fluorescence micrographs were taken at 1, 4, and 8 h

during clinorotation. In addition to the live/dead assays, we acquired light micrographs of cell morphology in standard gravity following exposure to (a) 1 or 4 h of 30 rpm clinorotation,

(b) 1 or 4 h of 60 rpm clinorotation, or (c) 1, 4, or 8 h of 75 rpm clinorotation. After termination of the clinorotation treatment, images were acquired in standard gravity every 30 min for

4 h, and then analyzed for cell area and shape factor using ImageJ (National Institutes of Health). STATISTICAL ANALYSES Because no prior publications have quantified cell areas during

clinorotation, we relied on pilot data for descriptive statistics to make sample size calculations. Assuming a critical significance level of _α_=0.05, statistical power of 0.9 (_β_=0.1),

and a detectable difference equal to the population s.d., we performed a power analysis to calculate an estimated sample size of _n_=23, using the method of Sokal and Rohlf.29 To ensure

adequate statistical power for cell area measurements, we chose to include at least _n_=30 for each sample group (Table 2), acquired over several experimental replicates. All data are

expressed as mean±s.e.m. Variance did not markedly differ between groups (less than fourfold). Average cell areas among different clinorotation speeds were first log transformed to improve

normality. Differences between clinorotation groups were then statistically analyzed using the Welch’s _t_-test for samples with unequal variance and unequal sample size, with Tukey _post

hoc_ tests for multiple pairwise comparisons. Using Welch's _t_-test for samples with unequal variance and sample size, we analyzed differences in cell velocity and directionality

between 0 (_n_=15) and 75 rpm (_n_=6) only for cells that were actively migrating. Similarly, we used Welch's _t_-test with Tukey post hoc test for multiple pairwise comparisons to

analyze differences in cell area between 30 and 75 rpm (at 0, 1, 2, 3, and 4 h) only for cells that were actively retracting (_n_=28). RESULTS SIMULATED MICROGRAVITY AFFECTS CELL SPREADING

Simulated microgravity had a profound effect on both the extent and kinetics of cell spreading (Figure 2). After the initial 10-min cell attachment and before rotation commenced, all of the

groups possessed similar cell areas of ~500 μm2. We found that hMSCs in the non-rotated 0 rpm condition (i.e., standard gravity) markedly increased spreading areas within 1 h after plating,

reaching an average of 2000 μm2. Their spreading area increased gradually with time, until they reached an average of 3000 μm2 by 8 h. For clinorotated groups, cell spreading was impeded

almost immediately. At 1 h, cells in the 30 rpm group were significantly smaller than control with an average cell area slightly above 1000 μm2; cells at 60 and 75 rpm were both

significantly different from 0 and 30 rpm, remaining rounded and small. The effects of clinorotation continued to affect cell spreading over the course of the entire 8 h experiment in a

rotation speed-dependent manner. By 8 h, we measured a statistically similar but smaller average area of 2750 μm2 for cells at 30 rpm. In contrast, the 60 rpm group had an average area of

2192 μm2, and the 75 rpm group had the lowest cell area of 1500 μm2, both statistically smaller than 0 and 30 rpm. From a kinetics perspective, the time required for cell spreading areas to

reach 2000 μm2 was within 1 h for non-rotating controls, within 4 h for 30 rpm, and within 8 h for 60 rpm. Our experiments did not run long enough to determine whether or not cells would

reach this mark for the 75 rpm condition, but based on the observed trends, it appears that cell spreading no longer increases after 7 h. These results indicate that cell spreading is

markedly affected by angular frequency and that these effects can be observed as soon as 1 h after clinorotation starts. Finer temporal resolutions and longer durations in future experiments

may provide more detailed insight on the time constant of important cellular processes associated with cellular gravisensing. One notable observation we made was that cells within each

clinorotation speed were not uniformly spread. As individual cells did not accurately represent the population characteristics, we plotted the group-wise distributions of cell morphologies

at various time points (Supplementary Figure 1). The 0 rpm control group adopts a broad distribution of cell areas within the first hour, followed by the 30 and 60 rpm groups. By 8 h, it is

clear that the 0, 30, and 60 rpm cell populations encompassed comparable ranges of cell areas. The 75 rpm group, however, exhibited a much more narrow distribution. Likewise, when staining

for filamentous actin we found that cells also spanned a range of cell shapes within each group (Supplementary Figure 2). There were no discernable differences in actin organization between

cells of similar morphology (elongated or rounded), even when comparing across different clinorotation conditions. This suggests that the observed population differences with angular

frequency is caused by disparate effects on individual cells, perhaps by triggering/overcoming some intrinsic signal within cells to reduce cell adhesion, suppress actin stress fiber

formation, and consequently induce cell rounding. It is unclear whether simulated microgravity directly affects actin stress fiber assembly to result in cell rounding, or whether cell

rounding induced by simulated microgravity is what inhibits stress fiber formation. To quantify these differences in cell shape as a function of clinorotation speed, we computed circularity

(circularity=4_π_*area/perimeter2), as it accommodates more abstract shapes than an aspect ratio calculation. We assigned circularity values above 0.6 to cells that were considered rounded

(Figure 3, black), values between 0.3 and 0.6 to semi-elongated cells (Figure 3, hatch) and values below 0.3 to elongated cells (Figure 3, gray). As expected from the previous area

measurements, Figure 3 clearly shows that increasing clinorotation speed results in a larger percentage of rounded cells in its population. The number of elongated cells was significantly

reduced with increasing clinorotation speed, and no elongated cells were found at 75 rpm. Plotting cell circularity against cell area for each clinorotation speed at different time points,

we clearly see a temporal increase in area associated with cell elongation in 0 rpm control cells (Supplementary Figure 3). This trend becomes disrupted with exposure to 30 and 60 rpm

clinorotation, as cells tended to exhibit a broad range of circularity and area. However, only at 75 rpm the does cell population maintain high circularity and smaller areas across time

points (1, 4, and 8 h). Overall, our morphology analysis demonstrates that the cell population at 75 rpm possesses a more consistent morphology (average area, cell distribution, circularity

versus area over time) over time. CELL VIABILITY AND RECOVERY AFTER CLINOROTATION To determine whether there was any loss of viability or if rounded cells were undergoing apoptosis, we

exposed cells to 75 rpm and used a live/dead assay after 1, 4, and 8 h of clinorotation (Figure 4b). We found no difference in cell viability or changes in cell number when compared with

control; in fact, the majority of cells were alive (>90%). Under light microscopy, we observed no evidence of apoptosis (i.e., membrane blebbing) for the cells that were not viable. This

also indicates that our clinochip system can be used effectively without loss of cells due to lifting or cell death for at least 8 h. We investigated whether clinorotation effects on cell

morphology are reversible by performing time-lapse microscopy after exposure to 1, 4, and 8 h of 75 rpm clinorotation. Following cessation of clinorotation, all cells increased their areas

and round cells became more elongated, similar to most of the cells in standard gravity controls (Figure 4a). Similar experiments were also repeated for 30 and 60 rpm after 1 and 4 h of

clinorotation (Supplementary Figure 4). SIMULATED MICROGRAVITY INHIBITS CELL MIGRATION BY INDUCING CELL ROUNDING For cell migration experiments, cells were seeded in Ibidi chemotaxis chips

with a chemical gradient of 100 ng/ml NGF to promote cell migration. Under clinorotation, only a few cells migrated, whereas most cells did not (see Table 2 for cell numbers). Cells that

were actively migrating at 75 rpm had a similar velocity (_P_=0.391) and directionality (_P_=0.822) when compared with control cells (Figure 5). Cells that were not migrating under simulated

microgravity exhibited morphological retraction (Figure 5). In other words, cell areas changed from fully spread morphologies to more rounded ones. This phenomenon is in agreement with our

observations in cell-spreading experiments, even when the initial conditions were different (10 min for spreading assays versus 12 h for chemotaxis and migration assays). We found that

during clinorotation cells retracted their area, but did so independently of rotation speed (‘0 h’ _P_=0.539, ‘1 h’ _P_=0.288, ‘2 h’ _P_=0.963, ‘3 h’ _P_=0.848, ‘4 h’ _P_=0.689, between 30

and 75 rpm). After 4 h of clinorotation during chemotaxis, cells at 30 and 75 rpm reached an average area of 2500 μm2, which is a value similar to the spreading experiments for 30 rpm at 8 h

(_P_=0.962 between 30 rpm, _P_=0.975 between 75 rpm). However, we did not conduct experiments long enough to determine steady state–retracted cell areas. Our results indicate that the

cellular response to simulated microgravity is more dominant than chemotactic signals, suggesting the role of migration of hMSCs to tissue repair sites might be suppressed in microgravity.

We base this conclusion on our observations of response to NGF at a concentration of 100 ng/ml. However, these results were obtained with only one concentration of NGF and it is possible

that different concentrations or other chemotactic molecules can elicit a stronger chemotactic response. For example stromal-derived factor-1, which is known to be a strong homing signal for

hMSCs.30 Nevertheless, because the response of adhered cells to clinorotation is retraction of cellular processes, we believe that the behavior will be similar, unless the chemotactic agent

can also enhance cell adhesion. DISCUSSION Understanding how angular frequency, or rotation speed, of clinorotation affects cell behavior is a critical aspect of microgravity simulation

experiments, so that the role of the changing gravity vector in cellular regulation can be appropriately considered. In this work we show that hMSCs can behave differently depending on

clinorotation speed. In particular, although average cell area increased more slowly at 30 rpm compared with non-rotated controls, it continues along an upward trajectory at 8 h and seems to

be converging with control values. For higher rotational speeds, cell area increases even more slowly, and appears to reach a plateau by 8 h at 75 rpm. This suggests that changes in cell

morphology may approach a limit at an angular frequency that is close to 75 rpm, and almost certainly must exceed 30 rpm. Although these results are relevant to our clinochip configuration,

results may vary for other clinostat devices, particularly for those that support cells in suspension. Our results are consistent with other research showing that rotation speed affects

animal cells, plants, and bacteria (_Escherichia coli_). For example, a study on osteoblastic ROS 17/2.8 cells reported that rotations at 10 and 40 rpm did not exhibit reproducible,

detectable changes from stationary control cells.31 Only a speed of 50 rpm showed reproducible changes in actin cytoskeleton and cell surface integrin β1 and apoptosis. The same effect has

been observed with E. coli,32 which exhibited differential response as a function of clinorotation speeds from 10 to 50 rpm. Interestingly, the difference between 40 and 50 rpm is only

0.1674 of a cycle per second, indicating that cells can be highly sensitive to small changes in angular frequency. Although a precise gravisensing mechanism has yet to be determined, it must

be one that can detect subtle alterations to external forces in a short period of time. Our data indicate that it is linked to pathways that are involved in cell spreading and cytoskeletal

organization, two phenomena that have been observed for different cell types. Potential candidates could be one or more molecules already known to play important roles in cellular

mechanoregulation, such as the Rho family of GTPases,33 ion mechanosensitive channels,34 intracellular calcium,35 nuclear deformations,36 focal adhesions, or other cell surface receptors.37

Although mechanosensitive pathways seem the most direct apparatus for gravisensing, others have also suggested the importance of external environmental factors including fluid shear, fluid

and nutrient exchange, oxygen content, buoyancy, and changes in the extracellular matrix.38 Thus, clinostats used to probe candidate gravisensing receptors should minimize external

environmental variables that arise from clinostat operation. In the context of a proposed framework for cellular gravisensing, the current results are consistent with our working

hypothetical model (Figure 1b). Standard gravity would constitute a constant gravitational stimulus and be detectable to all cells. With intermediate timescales of gravitational

nullification, the probability for a single cycle of rotational perturbation to evade gravisensing in each cell would assume a broad distribution. As any putative biochemical gravisensing

reaction(s) would be stochastic, the probability for gravisensory evasion in each cell would decrease with both lower angular frequency and exposure to longer duration perturbations. We did

in fact observe such trends, as a result of the time lapse, single-cell measurement capabilities of the clinochip system. For our clinochips, we do not expect that centripetal forces have a

role with our observed angular frequency-dependence, as residual accelerations were calculated to be on the micro-scale regime. In addition, because the capillary number (indicative of

viscous forces) is orders of magnitude smaller than surface tension, fluid shear forces are deemed negligible. There is also no enhanced nutrient transport that accompanies clinorotation in

our system. Without these confounding factors, it seems reasonable to conclude that the cell morphology differences we observed were predominantly due to changes in the angular frequency of

clinorotation. We believe the rounding and retracted cell area of hMSCs in simulated microgravity inhibit migration in the presence of a chemical gradient. Interestingly, the kinetics of

cell area changes during retraction were different from those during spreading, and were also angular frequency independent, suggesting that distinct gravisensing mechanisms may regulate

different processes. Similarly, other cell processes, and even cell fate, could be affected.39 In the same way that microgravity may produce these cellular alterations, other mechanical

stimuli and substrate characteristics can also modulate cell function.40 Stem cell morphology has a strong correlation with cellular phenotype and differentiation potential.41,42 It has been

demonstrated in prior work that spread cells have a higher tendency to undergo osteogenesis and that cells with rounded morphologies are more susceptible to adipogenesis.42 Because of the

short-term nature of this current study, it is not possible to establish whether hMSCs in our system would behave according to these trends. However, our data would suggest that cells at 30 

rpm clinorotation would be more amenable to osteogenic differentiation, whereas cells at 75 rpm would tend toward adipogenic or chondrogenic lineages. This may help explain the conflicting

reports on mesenchymal stem cells differentiation during clinorotation that we and others23 have observed. Future longer-term studies with the clinochip are required to explore hMSC

differentiation potential. Specifically, as we have shown that the population distribution of cell morphologies can be controlled by the angular frequency of rotation, we may be able to

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references ACKNOWLEDGEMENTS FUNDING This work was supported by National Aeronautics and Space Administration Space Biology Program, Grant NNX13AM06G. AUTHOR INFORMATION AUTHORS AND

AFFILIATIONS * Fischell Department of Bioengineering, University of Maryland, College Park, MD, USA Carlos Luna & Adam H Hsieh * NASA Goddard Space Flight Center, Greenbelt, MD, USA

Alvin G Yew * Department of Orthopaedics, University of Maryland, Baltimore, MD, USA Adam H Hsieh Authors * Carlos Luna View author publications You can also search for this author inPubMed 

Google Scholar * Alvin G Yew View author publications You can also search for this author inPubMed Google Scholar * Adam H Hsieh View author publications You can also search for this author

inPubMed Google Scholar CONTRIBUTIONS CL, AY, AH conceived the project and analyzed the data, CL performed the experiments, AY developed the lab-on-chip clinostat, and all authors

contributed to writing of the manuscript. CORRESPONDING AUTHOR Correspondence to Adam H Hsieh. ETHICS DECLARATIONS COMPETING INTERESTS The authors declare no conflict of interest. ADDITIONAL

INFORMATION Supplementary Information accompanies the paper on the _npj Microgravity_ (http://www.nature.com/npmgrav) SUPPLEMENTARY INFORMATION SUPPLEMENTARY FIGURE LEGENDS (DOC 26 KB)

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under a Creative Commons Attribution-NonCommercial-NoDerivatives 4.0 International License. The images or other third party material in this article are included in the article’s Creative

Commons license, unless indicated otherwise in the credit line; if the material is not included under the Creative Commons license, users will need to obtain permission from the license

holder to reproduce the material. To view a copy of this license, visit http://creativecommons.org/licenses/by-nc-nd/4.0/ Reprints and permissions ABOUT THIS ARTICLE CITE THIS ARTICLE Luna,

C., Yew, A. & Hsieh, A. Effects of angular frequency during clinorotation on mesenchymal stem cell morphology and migration. _npj Microgravity_ 1, 15007 (2015).

https://doi.org/10.1038/npjmgrav.2015.7 Download citation * Received: 12 March 2015 * Revised: 15 May 2015 * Accepted: 12 June 2015 * Published: 30 July 2015 * DOI:

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