Name: the assembly and application of 'shear rings': a novel endothelial model for orbital, unidirectional and periodic fluid flow and shear stress
Uploaded: 2016-10-31T14:00:00.000+00:00
Duration: 9 min 20 s
Description: Watch this Scientific Journal Video about The Assembly and Application of 'Shear Rings': A Novel Endothelial Model for Orbital, Unidirectional and Periodic Fluid Flow and Shear Stress at JoVE.com

The authors would like to acknowledge the assistance of Mr. Christopher Nguyen, Aaron Hunter and the Shreveport Jumpstart, SMART, and Biostart training programs as well as the Centenary College of Louisiana department of Biophysics, Shreveport, LA.

1. Construction of 150 mm Diameter Shear Rings (Figure 1)
NOTE: Shear rings may be constructed to create many different dimensions by varying the outer and inner Petri dish sizes, resulting in devices with different total surface areas, cell yields and developed ranges of shear forces. This report describes a 150 mm dish combined with an inner 100 mm dish for a total surface area of 98 cm2 (Figure 2).
<img alt="Figure 1" src="/files/ftp_upload/54632/54632fig1.jpg" /> 
Figure 1. Shear ring assembly. The top portion of the figure shows a partially assembled shear ring. Inject 0.5 ml of methylene chloride through the 3 mm hole with a transfer pipet if a tight seal has not completely formed between the inner and outer dishes. The shear ring is sealed shut by applying a 1 mm thick bead of silicon rubber adhesive around the inner edge of the shear ring top. The bottom portion of the figure shows the assembled shear ring. The blue represents the area of plated endothelial cells. The outer and inner red arrows indicate the orbital motion of the shear ring and media inside the shear ring when placed on an orbital shaker. <a href="https://cloudfront-jove-com.bdigitaluss.remotexs.co/files/ftp_upload/54632/54632fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" src="/files/ftp_upload/54632/54632fig2.jpg" /> 
Figure 2. Surface measurements for a 150 mm shear ring (not drawn to scale). Top panel shows centrifugal shifting of fluid towards outer ring in response to orbital rotation. <a href="https://cloudfront-jove-com.bdigitaluss.remotexs.co/files/ftp_upload/54632/54632fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<ol>
	<li>Create a shear ring construction template by generating a 150 mm outer edge profile in presentation software with a 100 mm internal diameter placed in the center of the 150 mm circle. Print the template on a sheet of A4 white paper.</li>
	<li>Pipet 10 ml of methylene chloride (dichloromethane) into a 150 mm glass Petri dish. It is critical that the dish is glass and not polystyrene (or other vinyl plastic), as methylene chloride solubilizes most plastics and is used here to join plastic components. 
	CAUTION: Use gloves for all construction with adequate hood ventilation. Methylene chloride is a contact irritant and is hepatotoxic.</li>
	<li>Align a 150 mm plastic Petri dish onto the outer shear ring template.</li>
	<li>Drill a 3 mm hole in the center of a 100 mm dish using a rotary tool. Remove any plastic shavings produced from the drilling.</li>
	<li>While holding with a gloved hand, invert and dip the top edge of the 100 mm Petri dish from the previous step into the pool of methylene chloride for approximately 3 sec.</li>
	<li>Transfer the &#34;wetted&#34; 100 mm dish edge-down onto the center of a 150 mm dish, carefully aligning the 100 mm dish onto the marked template. The methylene chloride will fuse the plastic, joining the 100 mm and 150 mm dishes. Gently rotate the 100 mm dish clockwise and counterclockwise a few times to ensure good adhesion to the 150 mm dish. 
	NOTE: Take great care to ensure proper alignment of the inner dish to the center of the outer dish. Eccentric alignment may result in variations of the shear stress at different locations in the shear ring. Take care to not allow methylene chloride to accidentally drip onto the outer track portion of the 150 mm Petri dish during the placement of the 100 mm dish. This will melt the plastic on the bottom surface where cells will be growing, creating an uneven surface that may cause flow disturbances.</li>
	<li>Once the methylene chloride has dried, flip the newly bound Petri dishes over and carefully inspect the points of contact to ensure that a tight seal has been formed between the two Petri dishes.</li>
	<li>If a tight seal has not completely formed, inject 0.5 ml of methylene chloride through the 3 mm hole with a transfer pipet. Pick up the dish and gently rotate it to allow the methylene chloride to reach the edge. 
	NOTE: If rotated too quickly, the methylene chloride can spill into the outer portion of the 150 mm dish, deforming the surface where cells will grow and ruining the shear ring. Leaking shear rings should be discarded.</li>
	<li>Seal off the hole in the 100 mm dish by applying a 3 mm bead of silicon rubber sealant.</li>
	<li>Using a rotary tool fitted with a flat cutting head, cut off the top 3 cm portion of a 15 ml conical polystyrene tissue culture tube, leaving at least 1 cm of the tube below the cap. Polish the edge of the cut tube until smooth and flat using the flat side of the cutting head. Remove any plastic shavings produced by grinding.</li>
	<li>Trace the cut off 15 ml conical tube onto the lid of the 150 mm dish with a marker, approximately 0.5 cm away from the edge of the dish. Drill a hole inside the drawn circle, leaving a margin approximately 1-2 mm from the edge of the circle.</li>
	<li>Place the cut off conical tube top over the drilled hole. Using a transfer pipet, apply approximately 250&#160;&#181;l of methylene chloride to the cut off edges of the conical tube to bind the conical tube to the 150 mm lid.</li>
	<li>Seal the 150 mm lid onto the 150 mm dish by applying a 1 mm thick bead of silicon rubber sealant around the inner edge of the top Petri dish.</li>
</ol>
2. Sterilization of Shear Rings
<ol>
	<li>Pipet approximately 10 ml of phosphate buffered saline into the newly formed shear ring through the 15 ml conical tube port. Swirl around to remove any debris inside the shear ring. Remove the phosphate buffered saline with a Pasteur pipet/vacuum aspirator.</li>
	<li>Repeat the previous step until debris is removed.</li>
	<li>To sterilize the shear ring, use a combination of a 70% ethanol rinse with UV irradiation.
	<ol>
		<li>Unscrew the vented cap, pipet approximately 10 ml of 70% ethanol through the access port, and screw the cap back on. Rotate and flip over the shear ring multiple times, ensuring that the inside of the shear ring is thoroughly washed.</li>
		<li>Under a fume hood, aspirate out excess 70% ethanol. With a spray bottle, thoroughly spray the cap and access port with 70% ethanol.</li>
		<li>Place the shear ring and cap under UV radiation within the tissue culture hood until completely dry.</li>
	</ol>
	</li>
	<li>Once dry, screw the cap back on and store sterilized shear rings at room temperature until used in cell culture plating.</li>
</ol>
3. Shear Stress Studies
<ol>
	<li>Plate endothelial cells in sterilized shear rings following the standard cell culture protocol typically using a 1:4 split ratio for transformed endothelial cell lines. 
	NOTE: Rat retinal microvascular endothelial cells were obtained commercially. Human brain endothelial cells (hCMEC/D3) cells were provided as a generous gift from Dr. Pierre-Oliver Couraud (Inserm, France) and were cultured in complete endothelial basal medium (EBM).</li>
	<li>Allow cultures to reach confluence prior to initiation of flow studies. Use 30 ml of tissue culture media (10% fetal calf serum, Dulbecco&#39;s modified Eagle&#39;s medium with 1% penicillin/streptomycin/amphotericin). Change cell culture medium every 3 days and maintain cells at 37 &#176;C with 7.5% CO2 and 92.5% room air.</li>
	<li>Place the orbital shaker in the incubator. 
	Note: Orbital shakers are typically heavy (&#62;10 kg). Place the orbital shaker on the bottom shelf of the incubator to minimize shelf stress and vibration.</li>
	<li>Place the experimental shear rings on the orbital shaker. Place static control group shear rings inside the same incubator.</li>
	<li>Estimate the maximum shear stress within the shear ring with the equation <img alt="Equation 1" src="/files/ftp_upload/54632/54632eq1.jpg" /> where <img alt="Equation 2" src="/files/ftp_upload/54632/54632eq2.jpg" /> is the radius of rotation for the orbital shaker (in cm), <img alt="Equation 3" src="/files/ftp_upload/54632/54632eq3.jpg" /> is the viscosity of the medium (in poise), <img alt="Equation 4" src="/files/ftp_upload/54632/54632eq4.jpg" /> is the density of the medium (in g/ml), and <img alt="Equation 5" src="/files/ftp_upload/54632/54632eq5.jpg" /> is the frequency of rotation (in rotation/sec)24.</li>
	<li>Initiate the rotation setting on the orbital shaker to the desired rpm (e.g., 90 rpm), leaving the shear rings on the shaker for the desired duration of shear stress application (e.g., 72 hr). 
	NOTE: Orbital shakers can produce heat, so the incubator temperature should be monitored initially to ensure 37 &#176;C is maintained throughout the duration of the experiment. Alternatively, shear rings can be transferred into environmental chambers (e.g., modular incubator chamber) and then placed within a rotating incubator.</li>
	<li>After cell layers have been exposed to shear for the desired length of time, remove shear rings from the incubator. Pull off the shear ring lid and retrieve cells and/or media for examining desired endpoint analyses (e.g., Western blotting, fluorescence activated cell sorting, etc.)25.</li>
</ol>

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J. Winny Yun has a research grant from the Annette Funicello foundation. J. Steven Alexander has research support from the Department of Neurology, LSUHSC-S.

The construction of the shear ring system for exposing endothelial cells to shear is a simple approach to performing shear stress studies. Nevertheless, there are a few steps that are critical for obtaining superior shear rings and better results. A complete seal should be made between the inner and outer ring to prevent media from leaking which could create inconsistent shear stress among samples. If a complete seal is not made, a minimal amount of methylene chloride should be added to the edge between the inner and outer dish with a transfer pipet through the hole in the inner ring. Gently rotating the ring should allow for the methylene chloride to form a complete seal. Also, plastic shavings inadvertently produced from cutting may be present on the shear ring track, so rinsing out the shear ring after construction should remove any debris that could adversely affect cell growth and give inconsistent shear stress application.
The shear rings described in the article are relatively large in size, leading to a high volume of output per sample. However, smaller versions could be constructed using smaller Petri dishes (e.g., 100 mm Petri dish with a 60 mm insert). Constructing multiple smaller shear rings could allow for higher numbers of study replicates while still maintaining relatively large fluid volumes and surface areas per sample when compared to other methods.
A few issues have been noted when using shear rings. First, some orbital shakers produce excess amounts of heat, and some incubators fail to control this increase in temperature. This can be avoided by the appropriate selection of rotators and the use of non-water jacketed incubators, which exchange heat much more readily. Culture contamination is another potential concern when using shear rings, particularly following assembly in an open-air environment. Shear rings must be thoroughly sterilized before use.
Here we have described a simple method to expose large numbers of endothelial cells to fluid shear stress. Other methods of producing unidirectional and periodic shear are available but are also far more costly, complex, and time-consuming when considering the surface areas and numbers of exposed cells per experiment. One such method involves connecting a peristaltic pump to a parallel plate flow chamber, which can difficult to set up and relatively costly. While the shear ring is simple to construct and use, the application of shear stress is less precise. Orbital flow can generate complex flow currents, which may model some, but not all, physical states of flow found in normal vascular physiology. The intrinsic inability to precisely control flow in the shear ring can be seen as one current limitation to the model. Furthermore, the mathematical formula described in the protocol above may be used as a tool to estimate maximal fluid shear stress in the shear ring. However, additional and more sophisticated experimental and computational studies are needed to definitively characterize flow patterns in the shear ring. As the characterization of flow patterns and fluid shear stress is better understood in the shear ring, one should be able to better adjust experimental parameters (optimal size of shear ring, rpm of the orbital shaker, volume of media in the shear ring, etc.) to generate the desired periodic, unidirectional shear stress.

Fluid shear stress has been shown to modulate endothelial gene programs1-5 through activation of cis-regulatory elements6, histone acetyltransferase activity7 and shear stress response elements (SSRE)8. Shear stress influences endothelial contributions towards coagulation by modulating tissue factor9 and tissue plasminogen activator (tPA)10 expression. Shear stress also influences control of angiogenesis11 and vessel remodeling by regulating PDGF-B synthesis and responsiveness8. The endothelial derived vasoactive mediators adrenomedullin, endothelin-1, urotensin II and relaxin are also regulated by shear12. Transcription of endothelial nitric oxide synthase production and nitric oxide production are both shear dependent10. Shear also controls endothelial ICAM-1 expression13. Flow-induced shear stress can therefore powerfully influence a large variety of endothelial responses. Importantly, vascular pulsations now also appear to play important roles in the pathophysiology of both normal vascular aging and forms of vascular dementia14 and may even contribute to other neurodegenerative diseases, such as multiple sclerosis15.
Venous and arterial endothelial cells are inherently exposed to diverse hemodynamic flow patterns in vivo, and many different endothelial cell phenotypes can be exhibited16. Depending on the magnitude and periodicity of flow, effects on endothelial cells may include inflammatory cell activation and apoptosis, which may reflect changes in gene or protein expression17,18. Studies on endothelial cell responses to shear phenomena therefore remain complicated by the difficulties in producing in vitro models that adequately produce such shear patterns.
Many different experimental protocols have been developed to apply fluid shear stress to endothelial cell monolayers. One of the most commonly used systems is the parallel plate flow chamber, which creates uniform laminar flow within the chamber19-21. A peristaltic pump is typically connected to create periodic flow, which can recapitulate flow characteristics typically found in many locations in vivo22. Another common set-up uses the &#39;cone and plate&#39; model, where fluid shear stress is determined by the rotational speed of the cone23. Both systems, and other arrangements similar to them, can be tedious to set up and require components that can be relatively expensive and inaccessible to many laboratories.
Another major limitation of these current models is the relatively low number of replicate studies that can be simultaneously performed, each with a relatively low surface area. This increases the time and complexity of such approaches. Therefore, an ideal model that induces unidirectional and periodic shear might be one where a high number of study replicates can be easily set up, each with a relatively large surface area. Furthermore, the aforementioned models require a fairly sophisticated setup, which may be cost-prohibitive for many users. A model that can produce fluid shear disturbances using basic laboratory materials might have several advantages.
A simple and highly economical method of applying unidirectional, periodic shear stress involves the placement of circular dishes on an orbital shaker24. This protocol is very simple and can be scaled up to achieve high numbers of study replicates, each with a relatively large surface area, as needed. However, cells located in the center of the dish are exposed to different flow patterns than cells along the periphery, yielding mixed cellular phenotypic responses in the same dish.
In this current report, we describe the construction and use of &#39;shear rings&#39;, our model for creating unidirectional and periodic shear stress. The design for the shear ring effectively limits &#39;mixed&#39; cellular shear-induced phenotypes by restricting the flow pathway within a circular culture dish to the periphery through the placement of an inner ring. The construction and operation of the shear ring is simple and economical and can be easily scaled to accommodate a wide range of orbital shakers using widely available tissue culture supplies. This model can be applied in endothelial cell experiments to provide unidirectional and periodic flow patterns within physiological and pathophysiological levels.

<table><tbody><tr><td>100 x 20 mm plastic tissue culture dish</td><td>Corning</td><td>430167</td><td>The dishes must be polystyrene</td></tr><tr><td>150 x 25 mm plastic tissue culture dish</td><td>Corning</td><td>430599</td><td>The dishes must be polystyrene</td></tr><tr><td>150 mm glass Petri dish</td><td>Fisher</td><td>3160150BO</td><td></td></tr><tr><td>15 ml polystyrene tissue culture plastic tubes</td><td>Falcon</td><td>352099</td><td></td></tr><tr><td>Methylene chloride</td><td>Sigma-Aldrich</td><td>D65100</td><td></td></tr><tr><td>silicone rubber sealant</td><td>DAP</td><td>7079808641</td><td></td></tr><tr><td>ethanol</td><td>Decon</td><td>2701</td><td></td></tr><tr><td>3 ml transfer pipette</td><td>Becton-Dickinson</td><td>357524</td><td></td></tr><tr><td>printer paper</td><td></td><td></td><td></td></tr><tr><td>scissors</td><td></td><td></td><td></td></tr><tr><td>gloves</td><td></td><td></td><td></td></tr><tr><td>rotary tool and set</td><td>Dremel</td><td>4000-6/50</td><td></td></tr><tr><td>rotary tool cutting head</td><td>Dremel</td><td>EZ476</td><td></td></tr><tr><td>rotary tool drill head</td><td></td><td></td><td></td></tr><tr><td>distilled water</td><td></td><td></td><td></td></tr><tr><td>orbital shaker</td><td>VWR</td><td>57018-754</td><td></td></tr><tr><td>incubator</td><td></td><td></td><td></td></tr><tr><td>Rat retinal microvascular endothelial cells</td><td>Cell Biologics</td><td>RA-6065</td><td></td></tr></tbody></table>

the assembly and application of 'shear rings': a novel endothelial model for orbital, unidirectional and periodic fluid flow and shear stress

Deviations from normal levels and patterns of vascular fluid shear play important roles in vascular physiology and pathophysiology by inducing adaptive as well as pathological changes in endothelial phenotype and gene expression. In particular, maladaptive effects of periodic, unidirectional flow induced shear stress can trigger a variety of effects on several vascular cell types, particularly endothelial cells. While by now endothelial cells from diverse anatomic origins have been cultured, in-depth analyses of their responses to fluid shear have been hampered by the relative complexity of shear models (e.g., parallel plate flow chamber, cone and plate flow model). While these all represent excellent approaches, such models are technically complicated and suffer from drawbacks including relatively lengthy and complex setup time, low surface areas, requirements for pumps and pressurization often requiring sealants and gaskets, creating challenges to both maintenance of sterility and an inability to run multiple experiments. However, if higher throughput models of flow and shear were available, greater progress on vascular endothelial shear responses, particularly periodic shear research at the molecular level, might be more rapidly advanced. Here, we describe the construction and use of shear rings: a novel, simple-to-assemble, and inexpensive tissue culture model with a relatively large surface area that easily allows for a high number of experimental replicates in unidirectional, periodic shear stress studies on endothelial cells.

Here we present representative results from both hCMEC/D3 brain endothelial cell and rat retinal microvascular endothelial cell monolayers, cultured in shear rings.
After allowing hCMEC/D3 brain endothelial cell monolayers to grow to confluence in complete EBM, the shear rings were placed on an orbital shaker for 72 hours. Using the equation from step 3.5, the calculated maximal shear stress <img alt="Equation 6" src="/files/ftp_upload/54632/54632eq6.jpg" /> was approximately 2.8 dynes/cm2 (with parameters&#160;<img alt="Equation 2" src="/files/ftp_upload/54632/54632eq2.jpg" /> = 0.95 cm, <img alt="Equation 3" src="/files/ftp_upload/54632/54632eq3.jpg" /> = 0.0101 poise,&#160;<img alt="Equation 4" src="/files/ftp_upload/54632/54632eq4.jpg" /> = 0.9973 g/ml24, <img alt="Equation 5" src="/files/ftp_upload/54632/54632eq5.jpg" /> = 1.5 rotations/second). We have found that these endothelial cell monolayers sometimes exhibit alignment in parallel with the direction of the periodic flow (Figure 3), although this is not uniformly observed because cell layers usually have excellent adhesion to the shear ring surface throughout the study.
After allowing the rat retinal microvascular endothelial cell monolayers to grow to confluence in complete rat endothelial cell medium, including EGF/VEGF growth factor supplements, the shear rings were placed on an orbital shaker for 72 hours. Using the equation from step 3.5, the calculated maximal shear stress <img alt="Equation 6" src="/files/ftp_upload/54632/54632eq6.jpg" /> was approximately 12 dynes/cm2 (with parameters <img alt="Equation 2" src="/files/ftp_upload/54632/54632eq2.jpg" /> = 0.95 cm, <img alt="Equation 3" src="/files/ftp_upload/54632/54632eq3.jpg" /> = 0.0101 poise, <img alt="Equation 4" src="/files/ftp_upload/54632/54632eq4.jpg" /> = 0.9973 g/ml24, <img alt="Equation 5" src="/files/ftp_upload/54632/54632eq5.jpg" /> = 4 rotations/second). Figure 4 shows that compared to the loading control of &#946;-actin, there was a large and significant loss of platelet endothelial cell adhesion molecule (PECAM-1/CD31) from the endothelial cell surface.
PECAM-1 is an integral membrane protein which is a member of the immunoglobulin (Ig)-superfamily that contains an immunoreceptor tyrosine-dependent inhibitory motif or &#39;ITIM&#39;26. PECAM-1 is not only expressed on endothelial cells but is also found on hematopoietic cells. PECAM-1 plays significant roles in endothelial cell-cell adhesion, leukocyte junctional transmigration, cell signaling, and importantly, mechano-transduction of shear stress. PECAM-1&#39;s role in sensing shear stress is critical for the functions of vascular endothelial cells and homeostasis17. When endothelial monolayers are exposed to shear stress, PECAM-1 responds directly to the mechanical force being exerted on it by altering its tyrosine phosphorylation, and subsequent activation of the ERK1/2 signaling cascade27. Furthermore, the PECAM-1-eNOS complex association is interrupted by disturbances in shear stress28. Therefore, PECAM-1 enables vascular endothelial cells to sense changes in fluid shear stress forces which can lead to reactive dilation of the vessel wall29.
These data support this model showing that endothelial cells respond to exposure to periodic, unidirectional fluid shear by down-regulating an important junctional and adhesive determinant, which mediates intercellular contact as well as transvascular cell exchange.
<img alt="Figure 3" src="/files/ftp_upload/54632/54632fig3.jpg" /> 
Figure 3. Brain endothelial cell morphology in a shear ring. The appearance of hCMEC/D3endothelial cell monolayers in shear rings following 48 hours of periodic fluid shear or static exposure. Alignment of cultures is not always observed parallel to flow direction (shown by arrow).&#160; <a href="https://cloudflare-jove-com.bdigitaluss.remotexs.co/files/ftp_upload/54632/54632fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" src="/files/ftp_upload/54632/54632fig4.jpg" /> 
Figure 4. Cell responses to periodic shear. Rat retinal microvascular endothelial cell monolayers cultured in shear rings showed a reduction in PECAM1/CD31 relative to &#946;-actin (n=3 each, students unpaired t-test, *-p&#60;0.05, error bars refer to standard deviation), following 72 hours of periodic fluid shear in shear rings.

Watch this Scientific Journal Video about The Assembly and Application of 'Shear Rings': A Novel Endothelial Model for Orbital, Unidirectional and Periodic Fluid Flow and Shear Stress at JoVE.com

The Assembly and Application of 'Shear Rings': A Novel Endothelial Model for Orbital, Unidirectional and Periodic Fluid Flow and Shear Stress

Different levels and patterns of fluid shear are known to modulate endothelial gene expression, phenotype and susceptibility to disease. We discuss the assembly and use of 'shear rings': a model that produces unidirectional, periodic shear stress patterns. Shear rings are simple to assemble, economical and can produce high cell yields.

Deviations from normal levels and patterns of vascular fluid shear play important roles in vascular physiology and pathophysiology by inducing adaptive as ...

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Biology

8.0K Views.  Louisiana State University Health Sciences Center in Shreveport. Different levels and patterns of fluid shear are known to modulate endothelial gene expression, phenotype and susceptibility to disease. We discuss the assembly and use of 'shear rings': a model that produces unidirectional, periodic shear stress patterns. Shear rings are simple to assemble, economical and can produce high cell yields.

Video: The Assembly and Application of 'Shear Rings': A Novel Endothelial Model for Orbital, Unidirectional and Periodic Fluid Flow and Shear Stress

Parallel-plate Flow Chamber and Continuous Flow Circuit to Evaluate Endothelial Progenitor Cells under Laminar Flow Shear Stress

The overall goal of this method is to describe a technique to subject adherent cells to laminar flow conditions and evaluate their response to well quantifiable fluid shear stresses1.
Our flow chamber design and flow circuit (Fig. 1) contains a transparent viewing region that enables testing of cell adhesion and imaging of cell morphology immediately before flow (Fig. 11A, B), at various time points during flow (Fig. 11C), and after flow (Fig. 11D). These experiments are illustrated with human umbilical cord blood-derived endothelial progenitor cells (EPCs) and porcine EPCs2,3.
This method is also applicable to other adherent cell types, e.g. smooth muscle cells (SMCs) or fibroblasts.
The chamber and all parts of the circuit are easily sterilized with steam autoclaving. In contrast to other chambers, e.g. microfluidic chambers, large numbers of cells (&gt; 1 million depending on cell size) can be recovered after the flow experiment under sterile conditions for cell culture or other experiments, e.g. DNA or RNA extraction, or immunohistochemistry (Fig. 11E), or scanning electron microscopy5. The shear stress can be adjusted by varying the flow rate of the perfusate, the fluid viscosity, or the channel height and width. The latter can reduce fluid volume or cell needs while ensuring that one-dimensional flow is maintained. It is not necessary to measure chamber height between experiments, since the chamber height does not depend on the use of gaskets, which greatly increases the ease of multiple experiments. Furthermore, the circuit design easily enables the collection of perfusate samples for analysis and/or quantification of metabolites secreted by cells under fluid shear stress exposure, e.g. nitric oxide (Fig. 12)6.

We are describing a method to subject adherent cells to laminar flow shear stress in a sterile continuous flow circuit. The cells' adhesion, morphology can be studied through the transparent chamber, samples obtained from the circuit for metabolite analysis and cells harvested after shear exposure for future experiments or culture.

The overall goal of this method is to describe a technique to subject adherent cells to laminar flow conditions and evaluate their response to well ...

Bioengineering

Directed Cellular Self-Assembly to Fabricate Cell-Derived Tissue Rings for Biomechanical Analysis and Tissue Engineering

Each year, hundreds of thousands of patients undergo coronary artery bypass surgery in the United States.1 Approximately one third of these patients do not have suitable autologous donor vessels due to disease progression or previous harvest. The aim of vascular tissue engineering is to develop a suitable alternative source for these bypass grafts. In addition, engineered vascular tissue may prove valuable as living vascular models to study cardiovascular diseases. Several promising approaches to engineering blood vessels have been explored, with many recent studies focusing on development and analysis of cell-based methods.2-5 Herein, we present a method to rapidly self-assemble cells into 3D tissue rings that can be used in vitro to model vascular tissues.
To do this, suspensions of smooth muscle cells are seeded into round-bottomed annular agarose wells. The non-adhesive properties of the agarose allow the cells to settle, aggregate and contract around a post at the center of the well to form a cohesive tissue ring.6,7 These rings can be cultured for several days prior to harvesting for mechanical, physiological, biochemical, or histological analysis. We have shown that these cell-derived tissue rings yield at 100-500 kPa ultimate tensile strength8 which exceeds the value reported for other tissue engineered vascular constructs cultured for similar durations (&lt;30 kPa).9,10 Our results demonstrate that robust cell-derived vascular tissue ring generation can be achieved within a short time period, and offers the opportunity for direct and quantitative assessment of the contributions of cells and cell-derived matrix (CDM) to vascular tissue structure and function.

This article outlines a versatile method to create cell-derived tissue rings by cellular self-assembly. Smooth muscle cells seeded into ring-shaped agarose wells aggregate and contract to form robust three-dimensional (3D) tissues within 7 days. Millimeter-scale tissue rings are conducive to mechanical testing and serve as building blocks for tissue assembly.

Each year, hundreds of thousands of patients undergo coronary artery bypass surgery in the United States.1 Approximately one third of these patients do ...

On-Chip Endothelial Inflammatory Phenotyping

Atherogenesis is potentiated by metabolic abnormalities that contribute to a heightened state of systemic inflammation resulting in endothelial dysfunction. However, early functional changes in endothelium that signify an individual's level of risk are not directly assessed clinically to help guide therapeutic strategy. Moreover, the regulation of inflammation by local hemodynamics contributes to the non-random spatial distribution of atherosclerosis, but the mechanisms are difficult to delineate in vivo. We describe a lab-on-a-chip based approach to quantitatively assay metabolic perturbation of inflammatory events in human endothelial cells (EC) and monocytes under precise flow conditions. Standard methods of soft lithography are used to microfabricate vascular mimetic microfluidic chambers (VMMC), which are bound directly to cultured EC monolayers.1 These devices have the advantage of using small volumes of reagents while providing a platform for directly imaging the inflammatory events at the membrane of EC exposed to a well-defined shear field. We have successfully applied these devices to investigate cytokine-,2 lipid-3, 4 and RAGE-induced5 inflammation in human aortic EC (HAEC). Here we document the use of the VMMC to assay monocytic cell (THP-1) rolling and arrest on HAEC monolayers that are conditioned under differential shear characteristics and activated by the inflammatory cytokine TNF-&alpha;. Studies such as these are providing mechanistic insight into atherosusceptibility under metabolic risk factors.

Microfluidic flow chambers etched by photolithography and fabricated from PDMS are applied to probe functional outcomes associated with EC dysfunction and inflammation. In a representative experiment, the ability of differential shear stress to modulate monocytic cell adhesion to cytokine activated EC monolayers is demonstrated.

Atherogenesis is potentiated by metabolic abnormalities that contribute to a heightened state of systemic inflammation resulting in endothelial ...

Generation of Shear Adhesion Map Using SynVivo Synthetic Microvascular Networks

Cell/particle adhesion assays are critical to understanding the biochemical interactions involved in disease pathophysiology and have important applications in the quest for the development of novel therapeutics. Assays using static conditions fail to capture the dependence of adhesion on shear, limiting their correlation with in vivo environment. Parallel plate flow chambers that quantify adhesion under physiological fluid flow need multiple experiments for the generation of a shear adhesion map. In addition, they do not represent the in vivo scale and morphology and require large volumes (~ml) of reagents for experiments. In this study, we demonstrate the generation of shear adhesion map from a single experiment using a microvascular network based microfluidic device, SynVivo-SMN. This device recreates the complex in vivo vasculature including geometric scale, morphological elements, flow features and cellular interactions in an in vitro format, thereby providing a biologically realistic environment for basic and applied research in cellular behavior, drug delivery, and drug discovery. The assay was demonstrated by studying the interaction of the 2 &#181;m biotin-coated particles with avidin-coated surfaces of the microchip. The entire range of shear observed in the microvasculature is obtained in a single assay enabling adhesion vs. shear map for the particles under physiological conditions.

Flow chambers used in adhesion experiments typically consist of linear flow paths and require multiple experiments at different flow rates to generate a shear adhesion map. SynVivo-SMN enables the generation of shear adhesion map using a single experiment utilizing microliter volumes resulting in significant savings in time and consumables.

Cell/particle adhesion assays are critical to understanding the biochemical interactions involved in disease pathophysiology and have important ...

Micropatterning and Assembly of 3D Microvessels

In vitro platforms to study endothelial cells and vascular biology are largely limited to 2D endothelial cell culture, flow chambers with polymer or glass based substrates, and hydrogel-based tube formation assays. These assays, while informative, do not recapitulate lumen geometry, proper extracellular matrix, and multi-cellular proximity, which play key roles in modulating vascular function. This manuscript describes an injection molding method to generate engineered vessels with diameters on the order of 100 &#181;m. Microvessels are fabricated by seeding endothelial cells in a microfluidic channel embedded within a native type I collagen hydrogel. By incorporating parenchymal cells within the collagen matrix prior to channel formation, specific tissue microenvironments can be modeled and studied. Additional modulations of hydrodynamic properties and media composition allow for control of complex vascular function within the desired microenvironment. This platform allows for the study of perivascular cell recruitment, blood-endothelium interactions, flow response, and tissue-microvascular interactions. Engineered microvessels offer the ability to isolate the influence from individual components of a vascular niche and precisely control its chemical, mechanical, and biological properties to study vascular biology in both health and disease.

This manuscript presents an injection molding method to engineer microvessels that recapitulate physiological properties of endothelium. The microfluidic-based process creates patent 3D vascular networks with tailorable conditions, such as flow, cellular composition, geometry, and biochemical gradients. The fabrication process and examples of potential applications are described.

In vitro platforms to study endothelial cells and vascular biology are largely limited to 2D endothelial cell culture, flow chambers with polymer or glass ...

Modeling Ovarian Cancer Multicellular Spheroid Behavior in a Dynamic 3D Peritoneal Microdevice

Ovarian cancer is characterized by extensive peritoneal metastasis, with tumor spheres commonly found in the malignant ascites. This is associated with poor clinical outcomes and currently lacks effective treatment. Both the three-dimensional (3D) environment and the dynamic mechanical forces are very important factors in this metastatic cascade. However, traditional cell cultures fail to recapitulate this natural tumor microenvironment. Thus, in vivo-like models that can emulate the intraperitoneal environment are of obvious importance. In this study, a new microfluidic platform of the peritoneum was set up to mimic the situation of ovarian cancer spheroids in the peritoneal cavity during metastasis. Ovarian cancer spheroids generated under a non-adherent condition were cultured in microfluidic channels coated with peritoneal mesothelial cells subjected to physiologically relevant shear stress. In summary, this dynamic 3D ovarian cancer-mesothelium microfluidic platform can provide new knowledge on basic cancer biology and serve as a platform for potential drug screening and development.

To study ovarian tumor progression in a physiologically relevant model, multicellular spheroids were cultured in a microdevice under simulated fluid flow. This dynamic 3D model emulates the intraperitoneal environment with the cellular and mechanical components where ovarian cancer metastasis occurs.

Ovarian cancer is characterized by extensive peritoneal metastasis, with tumor spheres commonly found in the malignant ascites. This is associated with ...

Gene Expression Analysis of Endothelial Cells Exposed to Shear Stress Using Multiple Parallel-plate Flow Chambers

We describe a workflow for the analysis of gene expression from endothelial cells subject to a steady laminar flow using multiple monitored parallel-plate flow chambers. Endothelial cells form the inner cellular lining of blood vessels and are chronically exposed to the frictional force of blood flow called shear stress. Under physiological conditions, endothelial cells function in the presence of various shear stress conditions. Thus, the application of shear stress conditions in in vitro models can provide greater insight into endothelial responses in vivo. The parallel-plate flow chamber previously published by Lane et al.9 is adapted to study endothelial gene regulation in the presence and absence of steady (non-pulsatile) laminar flow. Key adaptations in the set-up for laminar flow as presented here include a large, dedicated environment to house concurrent flow circuits, the monitoring of flow rates in real-time, and the inclusion of an exogenous reference RNA for the normalization of quantitative real-time PCR data. To assess multiple treatments/conditions with the application of shear stress, multiple flow circuits and pumps are used simultaneously within the same heated and humidified incubator. The flow rate of each flow circuit is measured continuously in real-time to standardize shear stress conditions throughout the experiments. Because these experiments have multiple conditions, we also use an exogenous reference RNA that is spiked-in at the time of RNA extraction for the normalization of RNA extraction and first-strand cDNA synthesis efficiencies. These steps minimize the variability between samples. This strategy is employed in our pipeline for the gene expression analysis with shear stress experiments using the parallel-plate flow chamber, but parts of this strategy, such as the exogenous reference RNA spike-in, can easily and cost-effectively be used for other applications.

Here, a workflow for the culture and gene expression analysis of endothelial cells under fluid shear stress is presented. Included is a physical arrangement for simultaneously housing and monitoring multiple flow chambers in a controlled environment and the use of an exogenous reference RNA for quantitative PCR.

We describe a workflow for the analysis of gene expression from endothelial cells subject to a steady laminar flow using multiple monitored parallel-plate ...

Segmenting Growth of Endothelial Cells in 6-Well Plates on an Orbital Shaker for Mechanobiological Studies

Shear stress imposed on the arterial wall by the flow of blood affects endothelial cell morphology and function. Low magnitude, oscillatory and multidirectional shear stresses have all been postulated to stimulate a pro-atherosclerotic phenotype in endothelial cells, whereas high magnitude and unidirectional or uniaxial shear are thought to promote endothelial homeostasis. These hypotheses require further investigation, but traditional in vitro techniques have limitations, and are particularly poor at imposing multidirectional shear stresses on cells. 
One method that is gaining increasing use is to culture endothelial cells in standard multi-well plates on the platform of an orbital shaker; in this simple, low-cost, high-throughput and chronic method, the swirling medium produces different patterns and magnitudes of shear, including multidirectional shear, in different parts of the well. However, it has a significant limitation: cells in one region, exposed to one type of flow, may release mediators into the medium that affect cells in other parts of the well, exposed to different flows, hence distorting the apparent relation between flow and phenotype. 
Here we present an easy and affordable modification of the method that allows cells to be exposed only to specific shear stress characteristics. Cell seeding is restricted to a defined region of the well by coating the region of interest with fibronectin, followed by passivation using passivating solution. Subsequently, the plates can be swirled on the shaker, resulting in exposure of cells to well-defined shear profiles such as low magnitude multidirectional shear or high magnitude uniaxial shear, depending on their location. As before, the use of standard cell-culture plasticware allows straightforward further analysis of the cells. The modification has already allowed the demonstration of soluble mediators, released from endothelium under defined shear stress characteristics, that affect cells located elsewhere in the well.

This protocol describes a coating method to restrict endothelial cell growth to a specific region of a 6-well plate for shear stress application using the orbital shaker model.

Shear stress imposed on the arterial wall by the flow of blood affects endothelial cell morphology and function. Low magnitude, oscillatory and ...

Microfluidic Model to Mimic Initial Event of Neovascularization

Neovascularization is usually initialized from an existing normal vasculature and the biomechanical microenvironment of endothelial cells (ECs) in the initial stage varies dramatically from the following process of neovascularization. Although there are plenty of models to simulate different stages of neovascularization, an in vitro 3D model that capitulates the initial process of neovascularization under the corresponding stimulations of normal vasculature microenvironments is still lacking. Here, we reconstructed an in vitro 3D model that mimics the initial event of neovascularization (MIEN). The MIEN model contains a microfluidic sprouting chip and an automatic control, highly efficient circulation system. A functional, perfusable microchannel coated with endothelium was formed and the process of sprouting was simulated in the microfluidic sprouting chip. The initially physiological microenvironment of neovascularization was recapitulated with the microfluidic control system, by which ECs would be exposed to high luminal shear stress, physiological transendothelial flow, and various vascular endothelial growth factor (VEGF) distributions simultaneously. The MIEN model can be readily applied to the study of neovascularization mechanism and holds a potential promise as a low-cost platform for drug screening and toxicology applications.

Here, we provide a microfluidic chip and an automatically controlled, highly efficient circulation microfluidic system that recapitulates the initial microenvironment of neovascularization, allowing endothelial cells (ECs) to be stimulated by high luminal shear stress, physiological level of transendothelial flow, and various vascular endothelial growth factor (VEGF) distribution simultaneously.

Neovascularization is usually initialized from an existing normal vasculature and the biomechanical microenvironment of endothelial cells (ECs) in the ...

Electrophysiological Recordings of Single-cell Ion Currents Under Well-defined Shear Stress

Fluid shear stress is well known to play a major role in endothelial function. In most vascular beds, elevated shear stress from acute increases in blood flow triggers a signaling cascade resulting in vasodilation thereby alleviating mechanical stress on the vascular wall. The pattern of shear stress is also well known to be a critical factor in the development of atherosclerosis with laminar shear stress being atheroprotective and disturbed shear stress being pro-atherogenic. While we have a detailed understanding of the various intermediate cell signaling pathways, the receptors that first translate the mechanical stimulus into chemical mediators are not completely understood. Mechanosensitive ion channels are critical to the response to shear and regulate shear-induced cell signaling thereby controlling the production of vasoactive mediators. These channels are among the earliest activated signaling components to shear and have been linked to shear-induced vasodilation through promoting nitric oxide production (e.g., inwardly rectifying K+ [Kir] and transient receptor potential [TRP] channels) and endothelium hyperpolarizing factor (e.g., Kir and calcium-activated K+ [KCa] channels) and shear-induced vasoconstriction through an undetermined mechanism that involves piezo channels. Understanding the biophysical mechanism by which these channels are activated by shear forces (i.e., directly or through a primary mechano-receptor) could provide potential new targets to resolve the pathophysiology associated with endothelial dysfunction and atherogenesis. It is still a major challenge to record flow-induced activation of ion channels in real time using electrophysiology. The standard methods to expose cells to well-defined shear stress, such as the cone and plate rheometer and closed parallel plate flow chamber do not allow real time study of ion channel activation. The goal of this protocol is to describe a modified parallel plate flow chamber that allows real time electrophysiological recording of mechanosensitive ion channels under well-defined shear stress.

The goal of this protocol is to describe a modified parallel plate flow chamber for use in investigating real time activation of mechanosensitive ion channels by shear stress.

Fluid shear stress is well known to play a major role in endothelial function. In most vascular beds, elevated shear stress from acute increases in blood ...