A Unidirectional Cell Switching Gate by Engineering Grating Length and Bending Angle

Zhou, Shihua; Gopalakrishnan, S.; Xu, Yuan; Yang, Jie; Lam, Y. W.; Pang, S. W.

doi:10.1371/journal.pone.0147801

Cited by 17 publications

(22 citation statements)

References 68 publications

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“…During cell migration, topographical guidance-induced direction changes could be observed, including a 180°direction reversal. 42,47 Multiple factors have been reported to affect cell migration direction; however, the actual mechanism remains unclear. In this study, the dynamic changes in cell traction force during directional reversals were analyzed.…”

Section: Characteristics Of Traction Force During Reversed Cell Migramentioning

confidence: 99%

Dynamic Tracking of Osteoblastic Cell Traction Force during Guided Migration

Hui

Pang

2017

Cel. Mol. Bioeng.

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Introduction-Continuous development of cell traction force can regulate cell migration on various extracellular matrixes in vivo. However, the topographical effect on traction force is still not fully understood. Methods-Micropost sensors with parallel guiding gratings were fabricated in polydimethylsiloxane to track the cell traction force during topographical guidance in real time. The force distributions along MC3T3-E1 mouse osteoblasts were captured every minute. The traction force in the leading, middle, and trailing regions was monitored during forward and reversed cell migration. Results-The traction force showed periodic changes during cell migration when the cell changed from elongated to contracted shape. For cell migration without guiding pattern, the leading region showed the largest traction force among the three regions, typically 5.8 ± 0.8 nanonewton (nN) when the cell contracted and 7.1 ± 0.5 nN when it elongated. During guided cell migration, a lower traction force was obtained. When a cell contracted, the trailing traction force was 4.1 ± 0.4 for nonguided migration and 2.2 ± 0.2 nN for guided migration. As a cell became elongated, the trailing traction force was 6.0 ± 0.5 nN during non-guided migration and 4.8 ± 0.3 nN under guidance. When a cell reversed its migration direction, the magnitudes of the traction force from the leading to the trailing regions also flipped. Conclusion-The cell traction force is continuously influenced by topographical guidance, which determines cell migration speed and direction. These results of cell traction force development on various topographies could lead to better cell migration control using topotaxis.

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Section: Characteristics Of Traction Force During Reversed Cell Migramentioning

confidence: 99%

Dynamic Tracking of Osteoblastic Cell Traction Force during Guided Migration

Hui

Pang

2017

Cel. Mol. Bioeng.

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“…The remaining positive photoresist was removed in acetone for 10 min. The Si stamp was coated with trichloro(1H, 1H, 2H, 2H-perfluorooctyl) silane (FOTS) (Sigma-Aldrich, 97%), which acted as an anti-sticking layer [32] (Fig 1C). A 60 μm thick 10:1 (weight ratio, w/w prepolymer to curing agent) PDMS (Sylgard 184, Dow Corning) was spin-coated at 1000 rpm for 60 s on the Si stamp and reversely imprinted onto another Si substrate at 130°C and pressure of 40 bar for 10 min.…”

Section: Methodsmentioning

confidence: 99%

Control of neural probe shank flexibility by fluidic pressure in embedded microchannel using PDMS/PI hybrid substrate

Rezaei

Pang

2019

PLoS ONE

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Implantable neural probes are widely used to record and stimulate neural activities. These probes should be stiff enough for insertion. However, it should also be flexible to minimize tissue damage after insertion. Therefore, having dynamic control of the neural probe shank flexibility will be useful. For the first time, we have successfully fabricated flexible neural probes with embedded microfluidic channels for dynamic control of neural probe stiffness by controlling fluidic pressure in the channels. The present hybrid neural probes consisted of polydimethylsiloxane (PDMS) and polyimide (PI) layers could provide the required stiffness for insertion and flexibility during operation. The PDMS channels were fabricated by reversal imprint using a silicon mold and bonded to a PI layer to form the embedded channels in the neural probe. The probe shape was patterned using an oxygen plasma generated by an inductively coupled plasma etching system. The critical buckling force of PDMS/PI neural probes could be tuned from 0.25–1.25 mN depending on the applied fluidic pressure in the microchannels and these probes were successfully inserted into a 0.6% agarose gel that mimicked the stiffness of the brain tissue. Polymer-based neural probes are typically more flexible than conventional metal wire-based probes, and they could potentially provide less tissue damage after implantation.

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“…It could be due to the bent gratings had less intersections with trench sidewalls compared to straight gratings that were perpendicular to trenches below. It had been shown that bent gratings had the effect of reversing cell migration direction [16,30]. When segment length of the bent grating became shorter, more cells migrated in the reversed direction so less cells could move towards…”

Section: Plos Onementioning

confidence: 99%

“…Migration of cells in circulating system has been considered as the key in understanding cancer metastasis and circulating tumor cells [9][10][11][12]. Migration behaviors of cancer cells in two-dimensional system in vitro have been studied including cell migration on micropatterns, under confinement, and cell separation [13][14][15][16][17]. However, there is still limited understanding of cancer cell invasion because the microenvironments used for the studies were quite different from the highly complicated extracellular matrix (ECM) in vivo.…”

Section: Introductionmentioning

confidence: 99%

Traversing behavior of tumor cells in three-dimensional platforms with different topography

2020

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Three-dimensional polydimethylsiloxane platforms were developed to mimic the extracellular matrix with blood vessels by having scaffolds with micropatterns, porous membrane and trenches. Precisely controlled physical dimensions, layouts, and topography as well as different surface chemical treatments were applied to study their influences on nasopharyngeal carcinoma cell (10-15 μm in diameter) migration in mimicked platforms over 15-hour of time-lapse imaging. By placing the pores at different distance from the edges of the trenches, pores with different trench sidewall exposures and effective sizes were generated. Pores right next to the trench sidewalls showed the highest cell traversing probability, most likely related to the larger surface contact area with cells along the sidewalls. Straight grating oriented perpendicular to trenches below the top layer increased cell traversing probability. Pore shape as well as pore size influenced the cell traversing probability and cells could not traverse through pores that were 6 μm or less in diameter, which is much smaller than the cell size. Trench depth of 15 μm could induce more cells to traverse through the porous membrane, while shallower trenches impeded cell traversing and longer time was needed for cells to traverse because 3 and 6 μm deep trenches were much smaller than cell size which required large cell deformation. Hydrophobic surface coating on the top layer and fibronectin in pores and trenches increased the cell traversing probability and reduced the pore size that cells could traverse from 8 to 6 μm, which indicated that cells could have larger deformation with certain surface coatings.

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A Unidirectional Cell Switching Gate by Engineering Grating Length and Bending Angle

Cited by 17 publications

References 68 publications

Dynamic Tracking of Osteoblastic Cell Traction Force during Guided Migration

Dynamic Tracking of Osteoblastic Cell Traction Force during Guided Migration

Control of neural probe shank flexibility by fluidic pressure in embedded microchannel using PDMS/PI hybrid substrate

Traversing behavior of tumor cells in three-dimensional platforms with different topography

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