Quantifying the Mechanical Properties of the Endothelial Glycocalyx with Atomic Force Microscopy

Summary

The mechanical characteristics of endothelial glycocalyx were measured by indentation using micron sized spheres on AFM cantilevers. Endothelial cells were cultured in a custom chamber under physiological flow conditions to induce glycocalyx expression. Data were analyzed using a thin film model to determine the glycocalyx thickness and modulus.

Abstract

Our understanding of the interaction of leukocytes and the vessel wall during leukocyte capture is limited by an incomplete understanding of the mechanical properties of the endothelial surface layer. It is known that adhesion molecules on leukocytes are distributed non-uniformly relative to surface topography ³, that topography limits adhesive bond formation with other surfaces ⁹, and that physiological contact forces (≈ 5.0 − 10.0 pN per microvillus) can compress the microvilli to as little as a third of their resting length, increasing the accessibility of molecules to the opposing surface ^{3, 7}. We consider the endothelium as a two-layered structure, the relatively rigid cell body, plus the glycocalyx, a soft protective sugar coating on the luminal surface ⁶. It has been shown that the glycocalyx can act as a barrier to reduce adhesion of leukocytes to the endothelial surface ⁴. In this report we begin to address the deformability of endothelial surfaces to understand how the endothelial mechanical stiffness might affect bond formation. Endothelial cells grown in static culture do not express a robust glycocalyx, but cells grown under physiological flow conditions begin to approximate the glycocalyx observed in vivo ². The modulus of the endothelial cell body has been measured using atomic force microscopy (AFM) to be approximately 5 to 20 kPa ⁵. The thickness and structure of the glycocalyx have been studied using electron microscopy ⁸, and the modulus of the glycocalyx has been approximated using indirect methods, but to our knowledge, there have been no published reports of a direct measurement of the glycocalyx modulus in living cells. In this study, we present indentation experiments made with a novel AFM probe on cells that have been cultured in conditions to maximize their glycocalyx expression to make direct measurements of the modulus and thickness of the endothelial glycocalyx.

Protocol

1. Methods

1.1 Cell Flow Chamber

A flow chamber, shown in Figure 1, was constructed so that cells could be grown under a shear of 1.0 Pa (10 dyn/cm²) and then transferred directly to an Asylum MFP3D AFM (Santa Barbara, CA).

1. The flow chamber was prepared for the experiment by first cleaning the glass slides in piranha solution (3:1 H₂SO₄:H₂O₂) for 15 min and then washing them with distilled water. They were then baked to dry and coated with aminopropyl triethoxy silane (APTES) in a vacuum deposition chamber.
2. A silicone gasket was cut using a Silhouette SD cutting tool. This allowed us to finely control the flow chamber dimensions for control of the flow rate and shear stress during cell growth. Typically, a channel was cut 6.4 mm wide by 19 mm long from a sheet of 0.4 mm silicone. The flow rate necessary to generate a shear stress of 1.0 Pa (10 dyn/cm²) is calculated assuming laminar flow in a rectangular channel with the equation:

where Q is the flow rate, τ is the shear stress, μ is the viscosity of the medium, assumed here to be 1.0 mPa (0.01 dyn*sec/cm²), h is the height and w is the width of the flow chamber.

3. The top piece of the flow chamber was aligned with the gasket in the cell culture dish and secured with a magnetic ring. The assembly was filled with isopropyl alcohol (IPA) for sterilization.
4. The full flow system was assembled. The flow ports in the cell culture dish were connected to three-way valves. The valves were connected to open 30 ml syringes. IPA was flushed through the system, which was then washed with 30 ml of McCoy's medium with 4% Fetal Calf Serum (FCS). The system was then filled with 20 ml of the Vec Technologies cell growth medium. Covers were placed on the tops of the syringes. The catch reservoir syringe cap had a needle in place to move medium back to the feed reservoir. Sterile 0.2 μm filters were attached to the air inlets in the covers to prevent contamination of the system. The flow chamber was then ready for cell seeding.

1.2 Cell Culture

1. Human umbilical vein endothelial cells (HUVEC's) and growth medium were purchased from Vec Technologies (Rensselaer, NY) and grown to confluence in a T25 Flask.
2. The growth medium was removed from the flask and the monolayer of cells released with 2 ml of 2.5% trypsin. Once the cells were in solution, the trypsinization was quenched with the addition of 10 ml of cell culture medium to the flask.
3. The cell suspension was centrifuged for 5 min and the supernatant was removed. The cells were resuspended in 1 ml of cell culture medium (containing serum) for injection into the flow chamber.
4. The cell suspension (0.5 ml, ~50,000 cells) was loaded into a syringe and injected into the flow chamber through a three-way valve.
5. The cells were allowed to settle and adhere to the glass substrate for 2 hr before flow was started. The cells were grown under flow in an incubator at 37 °C for 1 to 5 days until confluent.

1.3 Cantilever Preparation and Cell Indentation

1. Tipless AFM cantilevers (NanoWorld, Switzerland) were cleaned in nitric acid for 5 min and functionalized with aminopropyl triethoxy silane (APTES) in a vapor deposition chamber.
2. A solution of 5 mg/ml by weight NHS-sulfo-LC-biotin in Hank's Buffered Salt Solution (HBSS) was prepared. The cantilevers were submerged in the solution for 15 min to conjugate the silane with N-Hydroxysuccinimide (NHS) chemistry.
3. A solution of biotin free medium was made by incubating 20 ml of Vec Technologies cell culture medium (including serum) with 200 μl of streptavadin beads for 12 hr. The beads were removed from the medium with a magnet and the medium was filtered through a 0.22 μm sterile filter.
4. The flow chamber was removed from the cell culture dish and the cells were washed in 37 °C biotin-free medium.
5. A stock solution of 1 μl of 2.4 μm beads coated with streptavidin in 1 ml of biotin free medium was prepared, and 100 μl of the stock was added to the cell culture dish.
6. Streptavidin beads were picked up with the cantilever by landing the tip on the glass surface next to a bead, retracting, positioning the apex of the cantilever over the bead, and then pressing the cantilever down onto the bead and resting for several seconds.
7. The sensitivity of the cantilever was measured by indenting onto a region of bare glass and using the slope of the curve to set the tip deflection as a function of voltage.
8. The spring constant of the cantilever was then calculated from a thermal calibration in the MFP3D software.
9. The calibrated cantilever was then used to indent the samples, as shown in Figure 2. These 2.4 μm beads offer a larger contact area with the cell surface so that the mechanical properties of the soft glycocalyx layer can be detected. The cantilever was positioned over a cell near the cell nucleus and a soft approach of the tip onto the cell was used to set the cantilever height approximately 3 μm above the cell surface. The software was set for 20 repeated indentations at a rate of 1 μm/sec to a maximum force of 7 nN. Approximately 6 sec elapsed between successive contacts. It is possible to use different rates of indentation to test for time-dependent properties of the glycocalyx, although in these initial experiments, only a single indentation rate (1 μm/sec) was used.

2. Indentation Theory

Indentation into an elastic half-space with a sphere of radius R can be described using Hertz theory where the force of indentation, F, is given by the equation:

Where δ is the indentation depth and E* is the reduced modulus of the material under test (Figure 3). In the case of an infinitely stiff indenter impinging a uniform elastic half-space, E* is given by the equation:

where E is the elastic modulus and ν is the Poisson ratio of the material. Recent work with polymer films has inspired the development of a two layer model for determining the modulus and thickness of thin films ¹. We are applying this model to cell biology by treating the glycocalyx as a uniform thin soft film on the surface of the cell body. Using this model, the reduced modulus of the system becomes:

Where E_GC is the modulus of the glycocalyx, E_cell is the modulus of the cell body, P, Q and n are constants which have been empirically determined from the polymer fits, and z is given by the equation:

Where t is the thickness of the glycocalyx layer. A schematic of these parameters is shown in Figure 3. The model has been shown to be an accurate way of determining the modulus and thickness of a thin film on stiffer substrate ¹. This equation can be used to fit the curves obtained from indentation into cells to determine the modulus and thickness of the endothelial glycocalyx, as shown in Figure 4.

Results

In a typical experiment, 20 force-vs-distance curves were obtained from a given region of the cell, typically in the perinuclear region, near, but not on, the nucleus (within ~2 μm). The curves were aligned to account for any sample drift over the duration of the measurement and then averaged to remove cantilever noise, as shown in Figure 4. The curves were analyzed and fit with the two layer model that was developed for determining the modulus and thickness of thin polymer films ¹. From fi...

Discussion

We used values calculated from the two-layer model and Hertz theory to model the interaction of a leukocyte circulating in the blood with the endothelial wall. We have calculated that a microvillus on the leukocyte with a diameter of 50 nm under a 10 pN load would indent approximately 150 nm into the glycocalyx, only a fraction of the total thickness. This indicates that the glycocalyx, with properties as measured in this experiment, is a significant barrier to cell-cell interaction and can be a large steric hindrance wh...

Materials

Name	Company	Catalog Number	Comments
McCoy's Medium	Gibco	16600-082
Fetal Calf Serum	Hyclone	SH30070
Endothelial Cell Growth Medium	Vec Technologies	MCDB-131
Pooled Human Umbilical Vein Endothelial Cells	Vec Technologies	PHUVEC/T-25
Sulfuric Acid	JT Baker	9681-02
Hydrogen Peroxide	VWR	BDH3742-1
(3-aminopropyl)triethoxysilane	Aldrich	440140-100ML
Isopropyl Alcohol	VWR	BDH8999-4
Trypsin	Cellgro	25-054-C1
Hank's Buffered Salt Solution	Gibco	14175-095
sulfo-NHS-LC-Biotin	Thermo Scientific	21335
Streptavadin beads	Dynabeads	112.06D
MFP-3D AFM	Asylum Research
Tipless Cantilevers	Nanoworld	ARROW-TL1-50
Silhouette SD	Quickutz	Silhouette-SD
Silicone Rubber	Stockwell Elastomerics	SE50-RS
30 ml Syringes	Benton Dickinson	309650
18 gauge needles	Benton Dickinson	305196
Extension Sets	Hospira	4429-48
4 way valves	Teleflex	W21372
Male/Female Port Caps	Smith’s Medical	MX491B
Peristaltic Pump	Watson-Marlow	401U/D
Peristaltic Tubing	Watson-Marlow	903.0016.016
sterile filters	Pall Life Science	4652