- freely available
- re-usable
Processes 2014, 2(1), 71-88; doi:10.3390/pr2010071
Published: 10 January 2014
Abstract
: To mimic in vivo vibration of vocal fold cells, we studied the controllability and range of frequency, acceleration, duration, and shear stress in a new bioreactor attachment. The custom multiwell disc appliance fits into a commercially built rheometer, together termed a torsional rheometer bioreactor (TRB). Previous attachments to the TRB were capable of 50–100 Hz vibrations at relatively high strains but were limited to single-sample experiments. The TRB-multiwell disc system accommodates 20 samples in partially fluid-filled wells in an aseptic environment delivering three different acceleration conditions to different samples simultaneously. Frequency and amplitude used to calculate acceleration along with duration and shear stress were controllable and quantifiable using a combination of built-in rheometer sensors, manufacturer software, and smooth particle hydrodynamics (SPH) simulations. Computed shear stresses at the well bottom using SPH in two and three dimensions were verified with analytical approximations. Results demonstrate capabilities of the TRB-multiwell disc system that, when combined with computational modeling, provide quantifiable vibration parameters covering frequencies 0.01–250 Hz, accelerations of 0.02–300 m/s^{2}, and shear stresses of 0.01–1.4 Pa. It is well-suited for studying cell function underlying vocal fold lamina propria homeostasis, inflammation, and wound healing under differential vibration conditions.1. Introduction
When speaking or singing, the extracellular matrix (ECM) and cells of the vocal fold lamina propria experience forces from oscillation and collision [1,2]. The effect of these forces is described by three parameters: frequency, acceleration, and duration. Inertial forces result from repeated acceleration and deceleration, while shear forces result from fixed and free boundary conditions that prevent tissues from deforming uniformly. Under these forces, cells and extracellular matrix (ECM) modify, maintain, and repair the vocal fold lamina propria as part of normal laryngeal function. To excess, however, these force parameters are implicated in the etiology of vocal fatigue, nodules, polyps, or cysts [3,4]. Among school teachers, who are vocally very active, there is an increased propensity of females toward these disorders that is likely related to a higher fundamental frequency in their speech [5,6]. To better understand the underlying mechanisms in this benefit-cost dichotomy in vocal fold vibration, limited vibration regimens to ex vivo cell models have been used to study vibration-dependent cellular mechanisms [7,8,9,10]. While significant gene and protein changes have been identified, the roles of frequency, acceleration, duration, shear stress (FADS), and their interactions are largely unknown. The most likely reason is the challenges associated with delivering 10- to 100-fold biomimetic ranges for frequency and stress. Moreover, exploration of this FADS parameter space requires many experimental trials. A device with the potential to satisfy these requirements is a custom-modified torsional rheometer-bioreactor (TRB). The TRB is a commercial rheometer (Gemini model, Malvern Instruments, LTD) with appliances to support tissue and cell viability [11,12,13]. Initial feasibility of the rheometer to deliver shear stresses at low audio frequencies with parallel plate appliances was shown by adjusting sample thickness, plate radius, material viscoelasticity, and motor inertia [11]. Subsequently, a cup and plate system was designed for the TRB, whereby strains were delivered to three-dimensional cell-seeded scaffolds. Strains were 40% at 70 Hz, and non-destructive rheologic testing on the same engineered tissue was carried out [12]. A third configuration, a glass coverslip mounted to the cup or the moving parallel plate of the TRB, delivered shear stresses up to 2200 Pa at 100 Hz to a monolayer of cells. This delivery was under controlled temperature, humidity, and CO_{2} conditions using a custom incubator fitted to the commercial rheometer [13].
The above investigations demonstrate a high degree of versatility to configure the TRB for single sample experimentation but leave unanswered the challenge to process multiple samples simultaneously. A multiwell disc is evaluated in the current study. It accommodates up to 20 samples in a single experiment. The purposes of this study were to test the TRB’s ability to vibrate this multiwell disc at phonation frequencies with accelerations covering a 100-fold range and to computationally determine the range of shear stresses achievable within the partially fluid-filled wells.
2. Experimental Section
2.1. Maximizing Vibration Regimens
The multiwell disc is a commercially manufactured and sterilized 96-well cell-culture plate (BD Biosciences, San Jose, CA, USA) cut into a disc (Medical Instruments, The University of Iowa). The disc diameter is 57 mm, retaining eight usable wells at each of two outer radial positions and four wells at the innermost radial position (Figure 1). It is secured to a standard 45 mm diameter parallel plate (Malvern Instruments, Worcestershire, UK) using the following materials and assembly methods. A center hole in the multiwell disc is drilled that accepts a long center screw (20 mm length and 1.5 mm diameter). Two rubber liners 0.5 mm thick and 45 mm in diameter, with a hole in the middle for the screw to pass through, are used to prevent unwanted slippage and are placed on the bottom and top of the multiwell disc. An acrylic washer measuring 3 mm thick and 45 mm in diameter has a hole drilled through its center with a countersink so the screw head is embedded in the washer and will not make contact with the rheometer base. The acrylic washer and the rubber liners sandwiching the multiwell disc are then fastened to the parallel plate with the long screw threaded into predrilled screw threads at the center of the parallel plate.
Three acceleration conditions occur for a given experiments. All are at the same frequency and occur simultaneously because of the radial well locations relative to the rotation axis.
Moment of inertia of the multiwell disc assembly is calculated using the equation for a cylinder rotating about a central axis (Equation (1))
Material density ρ (stainless steel, polycarbonate, acrylic, and rubber), radius R, and length ℓ of each concentric cylinder are included. The inertia for the complete assembly is 1.6 × 10^{−5} kg m^{2}.
TRB-multiwell system vibration is achieved by securing the multiwell assembly to a torsional rheometer (Malvern Instruments), then lowering it onto a three-dimensional recoil material (Figure 1). The recoil material supplies a necessary restoring force to the torque motor when operating in oscillation mode. Deformation of the vibrating recoil material transfers to the multiwell disc, resulting in linear displacement within the x–z plane if adhesion to the solid surfaces is secure.
The magnitude of displacement is limited by the effective resonance peak of the system as determined by the recoil material’s viscoelasticity [11]. Maximal complex strain per unit torque γ*/T* of the TRB-multiwell system is written in terms of the angular frequency ω, G'(ω) and G''(ω), the elastic and viscous moduli of the recoil material, respectively, and the common radius of the parallel plate and recoil material R
With the torque (maximum = 0.15 N m), inertia, and radius as fixed parameters, we manipulated the recoil material. Different viscoelastic properties allowed exploitation of the effective resonance of the TRB-multiwell system. Four recoil materials were tested in the present study.
2.2. Using SPH to Model Shear Stresses
Fluid shear stresses within the partially fluid-filled wells of the multiwell disc are not directly measurable. Rather, computational methods were used to quantify this vibration parameter. Smoothed Particle Hydrodynamics (SPH) is a computational technique for calculating the fluid dynamics using a Lagrangian framework. This approach has been validated against many benchmark cases, and is particularly well suited for free-surface flows, such as the TRB-multiwell system. SPH was initially proposed by Lucy [14] and separately by Gingold and Monaghan [15]. Although its first application was in astrophysics, SPH is currently used in the analysis of incompressible and multiphase flow, heat and mass transfer, elasticity, and fracture [16,17].
As opposed to mesh-based computational fluid dynamics (CFD) approaches, SPH is a mesh-free method based on interpolation theory. In this method, matter is divided into a set of interpolation points or particles. Material properties such as density and viscosity, as well as the field variables velocity, pressure, and stress, are assigned to the particles. Integral interpolation among these particles approximates the field variables,
If A(r′) is known only at a discrete set of N points r_{1}, r_{2},..., r_{N}, the interpolation of quantity A(r) can be approximated by a summation interpolant,
The final equation used in the present investigation is a cubic spline kernel that is frequently used in SPH simulations. The compact support of this kernel function is equal to 2h, meaning that the interactions vanish for r > 2h
2.3. Recoil Material Evaluation
Selection of recoil materials for empirical studies was based on predicted viscoelastic properties that could generate TRB-multiwell system accelerations of 10–1000 m/s^{2}. To predict properties at these accelerations, we calculated G' and G" with analytic expressions [11]. Rewriting complex strain γ* as acceleration, we assume the small angle approximation rθ = rd where r is radial distance from the center of rotation, θ is angular displacement, and d is sample thickness. Using the second derivative of sinusoidal motion e^{iωt} at angular frequency ω,
2.4. Shear Stress Modeling
Shear stresses within each well of the multiwell disc were computed during vibration conditions using the SPH model described above. The fluid within a well (radius = 3.25 mm, height = 12.1 mm), was modeled as a 2D particle array—60 × 129 for 100 μL or 30 × 129 for 50 μL of fluid—to oscillate with a given frequency and amplitude. Fluid density (1 g/cm^{3}) was fixed. Fluid viscosity of cell culture medium, measured in triplicate with the rheometer, was 2.26 ± 0.13 mPa s. We also tested the model using a viscosity three times that of cell culture medium. Computations were repeated for several simulation cycles of vibration to ensure a time-independent solution. Shear stresses were then calculated for particle arrays.
To validate simulation results, we analytically determined a classical fluid-mechanics benchmark, the Stokes Second Problem. Stokes Second Problem describes oscillatory movement of a fluid that is bounded on the bottom by an infinitely long plane, freely bound on the top, and has no side walls. Oscillatory flow begins at time t at a particular frequency n (Figure 2). The velocity field u is governed by the equation
3. Results and Discussion
3.1. Viscoelastic Properties of Recoil Materials
To predict optimal properties of potential recoil materials, we calculated viscoelastic moduli for specific accelerations using Equations (10) and (11) with a nominal phase shift ϕ of 0.2. Elastic and viscous moduli should range from 30 to 2000 kPa and 0.5 to 300 kPa, respectively, and loss tangents (ratio of viscous to elastic moduli) should range from 0.02 to 0.2 to achieve 10–1000 m/s^{2} acceleration at 100–250 Hz (solid lines in Figure 3). Properties of the four tested recoil materials fell within these ranges. Their elastic and viscous moduli were 1.3–350 kPa and 1.1–140 kPa, respectively (symbols with dotted lines in Figure 3 top and middle). Direct measures were accurate up to 100 Hz and then extrapolated to 250 Hz using line fits (Table 1).
Table 1. Linear fit equations with highest R^{2} and corresponding coefficients used to extrapolate viscoelastic values of recoil materials to 250 Hz. |
Double-sided foam tape | Dimethyl silicon | Removable mounting squares | Hot melt pressure sensitive adhesive | |
---|---|---|---|---|
Elastic modulus | ||||
Freq range of data used in extrapolation (Hz) | 0.1–100 | 10–100 | 0.1–100 | 0.1–100 |
Line fit function | y = aln(x) + b | y = ae^{bx} | y = ax^{b} | y = ax + b |
a (Pa) | 34,669 | 279,045 | 30,709 | 6877 |
b (Pa) | 225,278 | 0.0016 | 0.078 | 0.1689 |
R^{2} | 0.9961 | 0.7644 | 0.9818 | 0.9952 |
Viscous modulus | ||||
Freq range of data used in extrapolation (Hz) | 0.1–100 | 32–100 | 0.1–100 | 0.1–100 |
Line fit function | y = aln(x) + b | y = ax + b | y = ax^{b} | y = ax + b |
a (Pa) | 4079.9 | −11.813 | 4187.9 | 112.83 |
b (Pa) | 54098 | 41086 | 0.1237 | 1899.6 |
R^{2} | 0.7611 | 0.0105 | 0.9607 | 0.9631 |
Loss tangent values were usually less than 0.2 across frequency. Exceptions to this dominance of elasticity over viscosity were for the dimethyl silicon polymer at frequencies less than 2.5 Hz and the hot melt pressure sensitive adhesive at frequencies greater than 100 Hz.
3.2. TRB-Multiwell Disc Accelerations
Accelerations of the TRB-multiwell disc system are shown in Figure 4. All four materials generated accelerations of 50 m/s^{2} or more at frequencies over 100 Hz. The greatest accelerations were obtained using the two stiffest recoil materials. Peak accelerations were 336 and 303 m/s^{2} at 151 Hz using the dimethyl silicon polymer (squares) and foam tape (triangles), respectively. Up to 250 Hz, the foam tape maintained slightly higher accelerations (285–170 m/s^{2}) compared to the dimethyl silicon polymer (285–115 m/s^{2}). At frequencies below 100 Hz, accelerations of the TRB-multiwell disc system were maximal when using the mounting squares (circles) as the recoil material. Accelerations of 100 m/s^{2} were achieved and sustained beginning at 28 Hz through 250 Hz. The hot melt pressure sensitive adhesive (diamonds) was the least effective at maximizing accelerations, both below and above 100 Hz, compared to the other three recoil materials. Peak accelerations were 100 m/s^{2} at 115 Hz and stayed above 78 m/s^{2} through 250 Hz.
Table 2 and Table 3 summarize approximate viscoelastic properties of recoil materials (to one significant figure) that produced target accelerations at frequencies 2–250 Hz. The values correspond to the four materials tested in the current study. The tables serve as references for future investigators interested in using other recoil materials for the TRB.
3.3. Stokes Second Equation Comparisons
A total of four different combinations of frequency and amplitude were determined analytically from Stokes second equation and compared to two-dimensional and three-dimensional SPH simulations. Shown in Table 4, 2D and 3D SPH stress values were comparable. 2D simulations required considerably less computation time than 3D simulations so they were used for the remainder of the conditions. Results from Stokes Second Problem were higher but within the same order of magnitude as those of the simulations. This result is consistent with a study by Khan and colleagues [19]. They compared analytic solutions of an oscillating fluid between two sidewalls to that without side walls. The reduced amplitude was attributed to increasing shear forces at the wall boundary, which causes the velocity to die out early as it approaches zero at the wall boundary.
Table 2. Approximate elastic moduli of recoil materials (in kPa) to achieve target accelerations at frequencies 2–250 Hz (e.g., to generate 100 m/s^{2} at 200 Hz, the recoil material’s elastic modulus is between 50 and 400 kPa). |
Acceleration (m/s^{2}) | 0.4 | 1 | 2 | 5 | 10 | 15 | 20 | 40 | 60 | 80 | 100 | 200 | 300 |
---|---|---|---|---|---|---|---|---|---|---|---|---|---|
Frequency (Hz) | Approximate Elastic Modulus of Recoil Materials (kPa) | ||||||||||||
2 | 30 | ||||||||||||
4 | 30 | ||||||||||||
6 | 30 | ||||||||||||
8 | 10–300 | 10–35 | 30 | ||||||||||
10 | 10–300 | 40 | |||||||||||
20 | 11–300 | 40 | |||||||||||
50 | 10–400 | 10–40 | 40 | ||||||||||
80 | 10–400 | 10–50 | 50 | ||||||||||
100 | 20–400 | 20–50 | |||||||||||
130 | 20–400 | 400 | |||||||||||
150 | 20–400 | 400 | |||||||||||
180 | 20–400 | 400 | |||||||||||
200 | 20–400 | 50–400 | 400 | ||||||||||
220 | 20–400 | 50–400 | 400 | ||||||||||
250 | 20–400 | 50–400 |
Table 3. Approximate viscous moduli of recoil materials (in kPa) to achieve target accelerations at frequencies 2–250 Hz (e.g., to generate 100 m/s^{2} at 200 Hz, the recoil material’s viscous modulus is between 8 and 80 kPa). |
Acceleration (m/s^{2}) | 0.4 | 1 | 2 | 5 | 10 | 15 | 20 | 40 | 60 | 80 | 100 | 200 | 300 |
---|---|---|---|---|---|---|---|---|---|---|---|---|---|
Frequency (Hz) | Approximate Viscous Modulus of Recoil Materials (kPa) | ||||||||||||
2 | 4 | ||||||||||||
4 | 5 | ||||||||||||
6 | 5 | ||||||||||||
8 | 3−70 | 3−5 | 5 | ||||||||||
10 | 4−60 | 5 | |||||||||||
20 | 5−60 | 6 | |||||||||||
50 | 7−70 | 7−8 | 7 | ||||||||||
80 | 8−70 | 8−10 | 8 | ||||||||||
100 | 8−70 | 8−10 | |||||||||||
130 | 8−70 | 70 | |||||||||||
150 | 8−70 | 40−70 | |||||||||||
180 | 8−70 | 40−70 | |||||||||||
200 | 8−80 | 80 | |||||||||||
220 | 8−80 | 80 | |||||||||||
250 | 8−80 | 80 |
Table 4. Comparison of 2D, 3D and Stokes Second Problem results. |
Frequency and amplitude conditions | 2D SPH | 3D SPH | Stokes 2nd problem |
---|---|---|---|
Shear stress (Pa) | |||
126 Hz; 0.46 mm | 0.3 | 0.5 | 1.6 |
126 Hz; 0.069 mm | 0.05 | 0.06 | 0.5 |
220 Hz; 0.063 mm | 0.07 | 0.1 | 0.2 |
220 Hz; 0.0094 mm | 0.01 | 0.03 | 0.08 |
3.4. Simulation of Shear Stress
Smooth particle hydrodynamics (SPH) results showed that shear stresses reached steady state after a single vibration cycle (Figure 5). Largest stresses were computed at the well bottom and stress magnitude diminished with vertical distance. In all, 17 different cases were simulated, varying frequency, amplitude of vibration, fluid viscosity, and fluid volume. As shown in Figure 6, an increase in acceleration (by increasing frequency or amplitude) increased shear stress proportionally. Alternatively, a three-fold viscosity increase quadrupled shear stress. Halving the fluid volume increased shear stress by 1.5–4.5 times, depending on the acceleration. In summary, resulting fluid shear stresses, shown in Figure 6, span a 100-fold range, from 0.01 to 1.35 Pa.
4. Conclusions
The multiwell disc appliance facilitates exploration of a frequency, acceleration, duration, shear (FADS) parameter space that has been rendered too time consuming and expensive with previously designed vibrating bioreactors. Our data demonstrate maximum accelerations of 9.2–334 m/s^{2} at 100–250 Hz by using different recoil materials with the TRB-multiwell system. These accelerations are much lower than predicted vocal fold accelerations using three-mass computer simulation or stroboscopy data (1000–4000 m/s^{2} at 100–400 Hz) [20,21] but they are the highest values generated by any bioreactor to date [7,8,10,22,23,24,25,26]. Stiff recoil materials provide accelerations in the order of 300 m/s^{2} above 100 Hz and more compliant materials provide 100 m/s^{2} at 28–100 Hz vibrations.
The large range of accelerations of the multiwell disc is made possible due to one main factor. The viscoelastic properties of the added recoil materials allow a mechanical resonance of the oscillating motor over a broad frequency range. The factory-designed torsional rheometers require the test sample stiffness to generate a recoil force for oscillatory motion. For low stiffness test materials, particularly when operating at higher frequencies, the motor shaft and plate spin instead of oscillate. Previously, we showed that the effective resonance of a rheometer-sample system shifts along the frequency axis depending on the sample radius, thickness, and the unknown elastic modulus [11]. Accurate viscoelastic measurements were achieved over a greater frequency range (up to and below the resonant peak produced by test sample stiffness) by increasing the sample radius or decreasing the sample thickness, or some combination of these variables. An increase in the sample radius or loss tangent reduces the resonant peak height and increases its width.
By adding a recoil material with known stiffness, we showed here that a system resonance could be exploited to provide a greater frequency range over which desired accelerations could be achieved. The viscoelastic properties of four recoil materials were tested to provide a two order of magnitude range of accelerations.
Shear stress is the last component in FADS parameter space we took into account when simulating vocal fold vibration conditions in the TRB. The partially filled wells of the multiwell disc exposed cells to shear stress, but measuring the stresses directly was not possible. Rather, using smooth particle hydrodynamics (SPH), we computed shear stresses in two dimensions—values comparable to those in three-dimensional simulations but with less computational expense. The resulting shear stresses of 0.01–1 Pa were tunable by altering frequency, amplitude, viscosity, or fluid volume in the TRB-multiwell disc system.
Direct measures of shear stress within vibrating vocal fold tissue are not currently possible. Furthermore, until now, shear stresses within a bioreactor have not been a controllable parameter from which to systematically investigate vocal fold cell function or tissue remodeling. Target shear stresses of 100–1000 Pa in previous appliance designs were consistent with stresses reported in physical and computational models and with constitutive relationships of bulk vocal fold deformation [2,27,28,29]. Multiwell disc stresses, however, were 100-fold lower than this target, just as achievable accelerations were much less than what is estimated during vocal fold oscillation.
While this outcome might appear to be a significant limitation to the TRB-multiwell disc system, preliminary results from our lab show vocal fold fibroblast sensitivities to these ranges (see Appendix Materials). We tested effects of FADS when vocal fold fibroblast cells first established ECM connectivity, a time scale that corresponds to events in early wound healing and in cell migration [30,31,32,33,34]. In particular, cellular focal adhesions to ECM transduce kinetic to biochemical signaling and regulate cell motility, genetic messaging, and matrix remodeling [35,36,37,38], making cell adhesion a strong candidate for initial investigations into FADS-sensitive mechanobiology.
Future knowledge from studies using the TRB-multiwell disc system could extend beyond that of vocal fold cellular and tissue function. Skin and brain are two organ systems with known exposures to forces comparable to that of vocal fold tissue—forces transferred to embedded cells with comparable magnitudes due to similar viscoelastic properties of the tissues [39,40,41]. Persons operating heavy hand-held equipment can experience adverse effects such as Hand-Arm Vibration Syndrome if frequency, acceleration, and duration safety limits are exceeded [21,42,43]. Greater understanding of neuronal mechanobiology in the presence of tool-transmitted vibrations, at 28–100 Hz vibrations and 100 m/s^{2} accelerations, could be realized using the more compliant drivers with the TRB-multiwell disc system, as exemplified in Figure 4. In the brain, endogenous neural mechanobiology is not well understood, nor is there good understanding of the cellular-molecular responses to traumatic brain injury [44,45]. A finding that the neuropeptide galanin has protective functions against shear stress of cortical neurons was determined using a microfluidics device [46]. The stresses with that device are a subset of the quantitative FADS parameters possible with the TRB-multiwell disc system. Controls on the rheometer permit single or short duration pulsing to simulate blunt trauma forces, or duty ratio-to-continuous low frequency motion to simulate endogenous conditions on multiple samples simultaneously. Particularly for systems such as the brain and vocal fold, forces are complex and knowledge of their mechanobiology is limited. A device such as the TRB-multiwell disc system can provide an invaluable tool, quantifying forces to gain understanding of cell behavior directly related to FADS parameters.
Acknowledgments
This work was supported by NIH Grant No. DC010275 and No. DC008047 from the National Institute on Deafness and Other Communication Disorders. We wish to acknowledge Mehrdad Hosnieh Farahani for his help with simulation coding and Susan Thibeault for her gracious gift of the immortalized vocal fold fibroblast cells.
Conflicts of Interest
The authors declare no conflict of interest.
Appendix
1. Supplemental Experimental Section: Fibroblast Adhesion
1.1. Cell Culture and Adhesion Assay
An immortalized vocal fold fibroblast cell line was used for adhesion studies, originating from a 21 y.o. male (young adult cell line, hVFFCs) [47,48]. Cells were cultured in a 37 °C, 5% CO_{2} atmosphere in Dulbecco’s modified Eagle medium (DMEM), high glucose with glutamine, 10% heat-inactivated fetal bovine serum (FBS). The day prior to experimentation, cells were lifted using trypsin and replated into flasks, then removed the following day using an enzyme-free dissociation solution known to minimize the disturbance of cell surface proteins (Gibco, Carlsbad, CA, USA). Cells were then treated with Calcein AM (calcein acetoxymethyl ester) (Invitrogen Corporation, Carlsbad, CA, USA) to fluorescently tag adherent cells. Twenty wells in two the multiwell discs (one experimental and one control) were coated with 0.5 µg/mL fibronectin with 100 µL per well and stored overnight.
The day of the experiment, the fibronectin-coated wells were washed with PBS. 100 µL of Calcein AM-treated cells (10^{6} cells/mL) were placed in each coated well using complete cell culture medium. Experimental conditions commenced 30 min later. Upon completion of a prescribed vibration regimen, the experimental and control multiwell discs were removed from their TRB. Each well was washed 3 times with PBS so only adhered cells remained, inverted for 5 min to dry, and replenished with 200 µL of PBS. Optical density (i.e., fluorescent intensity) was measured for each disc (absorption wave length = 490 nm; emission wave length = 525 nm) along with serial dilution wells (prepared similarly to the discs but maintained in a standard incubator during testing) using a FLUOstar Omega microplate reader (BMG Labtech; Durham, NC, USA).
1.2. Vibration Regimens
Selection of vibration regimens mimicked human voice use. Frequencies were male and female fundamental frequencies (126 and 220 Hz respectively). ON/OFF vibration duty ratios were 0.55 (0.55 s ON and 0.45 s OFF), corresponding to voiced-unvoiced characteristics of spoken American English and recorded during daily voice use of public school teachers [49]. The test duration was also similar to teacher-student contact time (4.4–6.4 h). Accelerations covered a 10-fold range (9.8–111 m/s^{2}). To reduce the four vibration parameters (frequency, duration, acceleration, stress) down to two, we used a metric proposed by Titze et al. for vocal fold vibration: cumulative distance (i.e., vocal dose)
1.3. Adhesion Ratio Calculation
Adherence changes due to vibration regimens were reported as the adhesion ratio. Measured optical density, from each well containing cells, was divided by the mean optical density of the control wells (N = 20). All experiments were conducted with multiple samples; at the outermost and middle positions of the experimental multiwell disc N = 8, and at the innermost position of the experimental multiwell N = 4. Standard deviation for each mean adhesion ratio was calculated using propagation of errors, then dividing by the square root of N to obtain the standard error of the mean [50].
2. Supplementary Results
2.1. Adhesion Sensitivity to Vibration
Human vocal fold fibroblast cells were tested for their early adhesion abilities (within 7 h of initially plating cells on fibronectin) in the multiwell disc under a variety of vibration conditions. The adhesion ratio (experimental/control emitted optical density) diminished linearly with calculated shear stress and diminished exponentially as a function of cumulative distance (Figure A1). Adhesion ratios were consistently greater than 0.9 when cumulative distances were less than 160 m and shear stresses were less than 40 mPa.
References
- Titze, I.R. Mechanical stress in phonation. J. Voice 1994, 8, 99–105. [Google Scholar] [CrossRef]
- Tao, C.; Jiang, J.J. Mechanical stress during phonation in a self-oscillating finite-element vocal fold model. J. Biomech. 2007, 40, 2191–2198. [Google Scholar] [CrossRef]
- Solomon, N.P. Vocal fatigue and its relation to vocal hyperfunction. Int. J. Speech-Lang. Pathol. 2008, 10, 254–266. [Google Scholar] [CrossRef]
- Thibeault, S.L. Advances in our understanding of the Reinke space. Curr. Opin. Otolaryngol. Head Neck Surg. 2005, 13, 148–151. [Google Scholar]
- Hunter, E.J.; Tanner, K.; Smith, M.E. Gender differences affecting vocal health of women in vocally demanding careers. Logop. Phoniatr. Vocol. 2011, 36, 128–136. [Google Scholar] [CrossRef]
- Roy, N.; Merrill, R.M.; Thibeault, S.; Gray, S.D.; Smith, E.M. Voice disorders in teachers and the general population: effects on work performance, attendance, and future career choices. J. Speech Lang. Hear. Res. 2004, 47, 542–551. [Google Scholar] [CrossRef]
- Gaston, J.; Quinchia Rios, B.; Bartlett, R.; Berchtold, C.; Thibeault, S.L. The response of vocal fold fibroblasts and mesenchymal stromal cells to vibration. PLoS One 2012, 7, e30965. [Google Scholar]
- Titze, I.R.; Hitchcock, R.W.; Broadhead, K.; Webb, K.; Li, W.; Gray, S.D.; Tresco, P.A. Design and validation of a bioreactor for engineering vocal fold tissues under combined tensile and vibrational stresses. J. Biomech. 2004, 37, 1521–1529. [Google Scholar] [CrossRef]
- Webb, K.; Li, W.; Hitchcock, R.W.; Smeal, R.M.; Gray, S.D.; Tresco, P.A. Comparison of human fibroblast ECM-related gene expression on elastic three-dimensional substrates relative to two-dimensional films of the same material. Biomaterials 2003, 24, 4681–4690. [Google Scholar]
- Wolchok, J.C.; Brokopp, C.; Underwood, C.J.; Tresco, P.A. The effect of bioreactor induced vibrational stimulation on extracellular matrix production from human derived fibroblasts. Biomaterials 2009, 30, 327–335. [Google Scholar] [CrossRef]
- Titze, I.R.; Klemuk, S.A.; Gray, S. Methodology for rheological testing of engineered biomaterials at low audio frequencies. J. Acoust. Soc. Am. 2004, 115, 392–401. [Google Scholar] [CrossRef]
- Klemuk, S.A.; Jaiswal, S.; Titze, I.R. Cell viability viscoelastic measurement in a rheometer used to stress and engineer tissues at low sonic frequencies. J. Acoust. Soc. Am. 2008, 124, 2330–2339. [Google Scholar] [CrossRef]
- Titze, I.R.; Klemuk, S.A.; Lu, X. Adhesion of a monolayer of fibroblast cells to fibronectin under sonic vibrations in a bioreactor. Ann. Otol. Rhinol. Laryngol. 2012, 121, 364–374. [Google Scholar]
- Lucy, L. A numerical approach to the testing of the fission hypothesis. Astron. J. 1977, 82, 1013–1024. [Google Scholar] [CrossRef]
- Gingold, R.; Monaghan, J. Smoothed particle hydrodynamics-theory and application to non-spherical stars. Mon. Notices R. Astron. Soc. 1977, 181, 375–389. [Google Scholar]
- Monaghan, J. Smoothed particle hydrodynamics. Rep. Prog. Phys. 2005, 68, 1703. [Google Scholar] [CrossRef]
- Liu, M.; Liu, G. Smoothed particle hydrodynamics (SPH): An overview and recent developments. Arch. Comput. Methods Eng. 2010, 17, 25–76. [Google Scholar] [CrossRef]
- Ferry, J.D. Viscoelastic Properties of Polymers; John Wiley & Sons: New York, NY, USA, 1980. [Google Scholar]
- Khan, M.; Iftikhar, F.; Anjum, A. Some unsteady flows of a jeffrey fluid between two side walls over a plane wall. Z. Fur Naturforschung Sect. A 2011, 66, 745–752. [Google Scholar]
- Horacek, J.; Laukkanen, A.M.; Sidlof, P.; Murphy, P.; Svec, J.G. Comparison of acceleration and impact stress as possible loading factors in phonation: A computer modeling study. Folia Phoniatr. Et Logop. 2009, 61, 137–145. [Google Scholar] [CrossRef]
- Titze, I.R.; Svec, J.G.; Popolo, P.S. Vocal dose measures: Quantifying accumulated vibration exposure in vocal fold tissues. J. Speech Lang. Hear. Res. 2003, 46, 919–932. [Google Scholar] [CrossRef]
- Van Dyke, W.S.; Sun, X.; Richard, A.B.; Nauman, E.A.; Akkus, O. Novel mechanical bioreactor for concomitant fluid shear stress and substrate strain. J. Biomech. 2012, 45, 1323–1327. [Google Scholar] [CrossRef]
- Wolchok, J.C.; Tresco, P.A. The isolation of cell derived extracellular matrix constructs using sacrificial open-cell foams. Biomaterials 2010, 31, 9595–9603. [Google Scholar] [CrossRef]
- Bacabac, R.G.; Smit, T.H.; van Loon, J.J.W.A.; Boulabi, B.Z.; Helder, M.; Klein-Nulend, J. Bone cell responses to high-frequency vibration stress: Does the nucleus oscillate within the cytoplasm? FASEB J. 2006, 20, 858–864. [Google Scholar] [CrossRef]
- Titze, I.R.; Broadhead, K.; Tresco, P.A.; Gray, S. Strain distribution in an elastic substrate vibrated in a bioreactor for vocal fold tissue engineering. J. Biomech. 2005, 38, 2406–2414. [Google Scholar] [CrossRef]
- Kutty, J.K.; Webb, K. Vibration stimulates vocal mucosa-like matrix expression by hydrogel-encapsulated fibroblasts. J. Tissue Eng. Regen. Med. 2010, 4, 62–72. [Google Scholar]
- Jiang, J.J.; Titze, I.R. Measurement of vocal fold intraglottal pressure and impact stress. J. Voice 1994, 8, 132–144. [Google Scholar] [CrossRef]
- Gunter, H.E. A mechanical model of vocal-fold collision with high spatial and temporal resolution. J. Acoust. Soc. Am. 2003, 113, 994–1000. [Google Scholar] [CrossRef]
- Chen, L.-J.; Mongeau, L. Verification of two minimally invasive methods for the estimation of the contact pressure in human vocal folds during phonation. J. Acoust. Soc. Am. 2011, 130, 1618–1627. [Google Scholar] [CrossRef]
- Gupton, S.L.; Waterman-Storer, C.M. Spatiotemporal feedback between actomyosin and focal-adhesion systems optimizes rapid cell migration. Cell 2006, 125, 1361–1374. [Google Scholar] [CrossRef]
- Lim, X.; Tateya, L.; Tateya, T.; Munoz-Del-Rio, A.; Bless, D.M. Immediate inflammatory response and scar formation in wounded vocal folds. Ann. Otol. Rhinol. Laryngol. 2006, 115, 921–929. [Google Scholar]
- Ling, C.; Raasch, J.L.; Welham, N.V. E-Cadherin and transglutaminase-1 epithelial barrier restoration precedes type IV collagen basement membrane reconstruction following vocal fold mucosal injury. Cells Tissues Organs 2011, 193, 158–169. [Google Scholar] [CrossRef]
- Welham, N.V.; Lim, X.; Tateya, I.; Bless, D.M. Inflammatory factor profiles one hour following vocal fold injury. Ann. Otol. Rhinol. Laryngol. 2008, 117, 145–152. [Google Scholar]
- Zaidel-Bar, R.; Cohen, M.; Addadi, L.; Geiger, B. Hierarchical assembly of cell-matrix adhesion complexes. Biochem. Soc. Trans. 2004, 32, 416–420. [Google Scholar] [CrossRef]
- Burridge, K.; Chrzanowska-Wodnicka, M. Focal adhesions, contractility, and signaling. Annu. Rev. Cell Dev. Biol. 1996, 12, 463–519. [Google Scholar] [CrossRef]
- Matthews, B.D.; Overby, D.R.; Mannix, R.; Ingber, D.E. Cellular adaptation to mechanical stress: Role of integrins, Rho, cytoskeletal tension and mechanosensitive ion channels. J. Cell Biol. 2006, 119, 508–518. [Google Scholar]
- Schwartz, M.A. Integrins and Extracellular Matrix in Mechanotransduction. Cold Spring Harb. Perspect. Biol. 2010, 2. [Google Scholar] [CrossRef]
- Jamney, P.A.; McCulloch, C.A. Cell mechanics: Integrating cell responses to mechanical stimuli. Annu. Rev. Biomed. Eng. 2007, 9, 1–34. [Google Scholar]
- Arbogast, K.B.; Margulies, S.S. Material characterization of the brainstem from oscillatory shear tests. J. Biomech. 1998, 31, 801–807. [Google Scholar] [CrossRef]
- Holt, B.; Tripathi, A.; Morgan, J. Viscoelastic response of human skin to low magnitude physiologically relevant shear. J. Biomech. 2008, 41, 2689–2695. [Google Scholar] [CrossRef]
- Chan, R.W. Measurements of vocal fold tissue viscoelasticity: Approaching the male phonatory frequency range. J. Acoust. Soc. Am. 2004, 115, 3161–3170. [Google Scholar] [CrossRef]
- McLeod, R.W.; Griffin, M.J. Effects of whole-body vibration waveform and display collimation on the performance of a complex manual control task. Aviat. Space Environ. Med. 1990, 61, 211–219. [Google Scholar]
- Dahlin, L.B.; Necking, L.E.; Lundstrom, R.; Lundborg, G. Vibration exposure and conditioning lesion effect in nerves: An experimental study in rats. J. Hand Surg. 1992, 17, 858–861. [Google Scholar] [CrossRef]
- Tyler, W.J. The mechanobiology of brain function. Nat. Rev. Neurosci. 2012, 13, 867–878. [Google Scholar] [CrossRef]
- LaPlaca, M.C.; Prado, G.R. Neural mechanobiology and neuronal vulnerability to traumatic loading. J. Biomech. 2010, 43, 71–78. [Google Scholar] [CrossRef]
- Liu, M.; Song, W.; Li, P.; Huang, Y.; Gong, X.; Zhou, G.; Jia, X.; Zheng, L.; Fan, Y. Galanin protects against nerve injury after shear stress in primary cultured rat cortical neurons. PLoS One 2013, 8, e63473. [Google Scholar]
- Chen, X.; Thibeault, S.L. Characteristics of age-related changes in cultured human vocal fold fibroblasts. Laryngoscope 2008, 118, 1700–1704. [Google Scholar] [CrossRef]
- Chen, X.; Thibeault, S.L. Novel isolation and biochemical characterization of immortalized fibroblasts for tissue engineering vocal fold lamina propria. Tissue Eng. C 2009, 15, 201–212. [Google Scholar] [CrossRef]
- Titze, I.R.; Hunter, E.; Svec, J.G. Voicing and silence periods in daily and weekly vocalizations of teachers. J. Acoust. Soc. Am. 2007, 121, 469–478. [Google Scholar] [CrossRef]
- Bevington, P.R.; Robinson, K.D. Data Reduction and Error Analysis for the Physical Sciences; Tubb, S.J., Morriss, J.M., Eds.; McGraw-Hill, Inc.: New York, NY, USA, 1992; pp. 1–328. [Google Scholar]
© 2014 by the authors; licensee MDPI, Basel, Switzerland. This article is an open access article distributed under the terms and conditions of the Creative Commons Attribution license (http://creativecommons.org/licenses/by/3.0/).