Measuring the Stiffness of Ex Vivo Mouse Aortas Using Atomic Force Microscopy


Your institution must subscribe to JoVE's Biology section to access this content.

Fill out the form below to receive a free trial or learn more about access:



We present detailed protocols for isolation of aortas from mouse and measurement of their elastic modulus using atomic force microscopy.

Cite this Article

Copy Citation | Download Citations | Reprints and Permissions

Bae, Y. H., Liu, S. l., Byfield, F. J., Janmey, P. A., Assoian, R. K. Measuring the Stiffness of Ex Vivo Mouse Aortas Using Atomic Force Microscopy. J. Vis. Exp. (116), e54630, doi:10.3791/54630 (2016).


Arterial stiffening is a significant risk factor and biomarker for cardiovascular disease and a hallmark of aging. Atomic force microscopy (AFM) is a versatile analytical tool for characterizing viscoelastic mechanical properties for a variety of materials ranging from hard (plastic, glass, metal, etc.) surfaces to cells on any substrate. It has been widely used to measure the stiffness of cells, but less frequently used to measure the stiffness of aortas. In this paper, we will describe the procedures for using AFM in contact mode to measure the ex vivo elastic modulus of unloaded mouse arteries. We describe our procedure for isolation of mouse aortas, and then provide detailed information for the AFM analysis. This includes step-by-step instructions for alignment of the laser beam, calibration of the spring constant and deflection sensitivity of the AFM probe, and acquisition of force curves. We also provide a detailed protocol for data analysis of the force curves.


The biomechanical properties of arteries are a critical determinant in cardiovascular disease (CVD) and aging. Arterial stiffness, a major cholesterol independent risk factor and an indicator for the progression of CVD, increases with vascular injury, atherosclerosis, age, and diabetes1-8. Arterial wall stiffening is associated with increased dedifferentiation, migration, and proliferation of vascular smooth muscle cells9-12. In addition, increased arterial stiffness has been linked to enhanced macrophage adhesion1, endothelial permeability and leukocyte transmigration13, and vessel wall remodeling14,15. Thus, therapies that could prevent arterial stiffening in CVD or aging might complement currently available pharmacological interventions that treat CVD by reducing high blood cholesterol.

AFM is a powerful analytical tool used for various physical and biological applications. AFM is increasingly used to obtain the high-resolution images and characterize the biomechanical properties of soft biological samples such as tissues and cells1,2,10,16,17 with a great degree of accuracy at nanoscale levels. A major advantage of AFM is the fact that it can be used with living cells.

This paper describes our method for measuring the elastic modulus of mouse arteries ex vivo using AFM. The described method shows how we 1) properly isolate mouse arteries (descending aorta and aortic arch) and 2) measure the elastic modulus of these tissues by AFM. Measurements of unloaded elastic moduli in arteries can help to elucidate changes in the extracellular matrix (ECM) that occur in response to vascular injury, CVD, and aging.

Subscription Required. Please recommend JoVE to your librarian.


Animal work in this study was approved by the Institutional Animal Care and Use Committees of the University of Pennsylvania. The methods were carried out in accordance with the approved guidelines.

1. Preparing the Mouse and Isolation of the Aorta

  1. Anesthetize a mouse with ketamine (80 - 100 mg/kg), xylazine (8 - 10 mg/kg) and acepromazine (1 - 2 mg/kg) intraperitoneally. Confirm anesthesia with a tail pinch test. Once the mouse is fully anesthetized, euthanize the mouse by cervical dislocation.
  2. Place the mouse on its back and pin the mouse to a dissection board. Clean the abdomen area with 70% (v/v) ethanol wipes.
  3. Pinch the skin at the mid-line and make a small initial incision with medium sized microsurgery scissors at the abdomen. While holding the skin with forceps, use medium sized microsurgery scissors to cut the skin and peritoneum from the abdomen to the sternum.
  4. Cut away the ribs on both sides with medium sized microsurgery scissors. Carefully remove the lungs and liver with small sized microsurgery scissors, and leave the heart and aorta. Transfer the mouse and dissection board to a dissecting microscope.
  5. Grasp the fat surrounding the aorta with small forceps and use small scissors to carefully cut away fat around the aorta.
  6. Gently grab the aorta with forceps, make one cut with small sized microsurgery scissors at the beginning of the ascending aorta and another cut at the end of the descending aorta, just above the abdominal aorta.
  7. Transfer the dissected aorta to a 60-mm dish containing 1x phosphate-buffered saline (PBS; without calcium and magnesium).
  8. Continue to dissect away any remaining fatty tissue from the aorta using small sized microsurgery scissors. Use small scissors to open the aorta longitudinally.
  9. Use small sized microsurgery scissors to cut a small piece (~ 2 x 4 mm) of the descending aorta and aortic arch for AFM analysis (Figure 1). Place the tissue in a 60-mm plastic dish and keep it moist in a drop of PBS .

Figure 1
Figure 1: An Image Showing the Location of the Different Aortic Segments in a Mouse. The aorta was isolated from the heart to the diaphragm, and a small portion of the descending aorta and the aortic arch were used to determine the elastic moduli. Scale bar, 1 mm. Please click here to view a larger version of this figure.

2. Preparing Tissue Samples for the AFM Measurements

  1. Carefully remove the PBS using a lab-wipe without touching the aorta. Be certain that the luminal side of the tissue is facing up.
  2. Gently glue each end of the opened aorta to the plate by adding 5 - 10 μl of cyanoacrylate adhesive with a gel-loading tip (Figure 2).
    NOTE: The amount of glue needed to firmly attach the tissue at each end must be determined empirically. It is critical that the aorta is not stretched during this process.
  3. Check the glued aorta to make certain that it is not folded or floating. After air-drying the glue on the aorta (30 - 60 sec), gently add PBS and submerge the sample.
    NOTE: Preparation the AFM (steps 3 - 5) can be carried out while the tissue is being prepared for analysis.

Figure 2
Figure 2: Cartoon of an Aortic Segment Glued onto a 60-mm Culture Dish using Cyanoacrylate Adhesive. The cyanoacrylate adhesive is being applied to the edge of an aortic sample in preparation for AFM measurements. Please click here to view a larger version of this figure.

3. Loading the Probe

  1. Mount a fluid probe holder onto the probe load stand.
  2. Using tweezers, slide a silicon nitride AFM probe (0.06 N/m cantilever) with a spherical tip (we have used a 1-µm diameter SiO2 particle but larger sizes may also be used) on the probe holder. Make sure that the AFM probe is firmly secured to the probe holder.
  3. Slide the probe holder onto the Z-scanner mount of the AFM head, and ensure that the probe holder is securely attached.

4. Aligning the Laser on the Probe

  1. Open the AFM software. Choose the experiment type on the software; Experiment Category to Contact Mode, Experiment Group to Contact Mode in fluid and Experiment to Contact Mode in fluid. Click Load experiment in the software; this will turn on the laser.
  2. Add 3 ml of distilled water to a 50-mm glass bottom dish and place the dish on the stage of the laser alignment unit. This unit simplifies the process of focusing the laser beam onto the back of cantilever.
  3. Mount the AFM head in an upright position onto the laser alignment unit and power on the laser alignment unit. Add approximately 50 μl of distilled water to form a droplet on the AFM tip.
  4. Using the joystick, lower the AFM head so the AFM tip makes contact with water in the dish. If contact is not made between the AFM tip and water in the dish, gently raise the dish until contact is made. Adjust the focus, brightness and XY position so the AFM tip is in view on the LCD screen of the alignment unit.
  5. Position the laser spot onto the tip of the AFM probe by adjusting the laser positioning knobs of the AFM head. Using the detector positioning knobs on the AFM head, adjust the position of the photodiode until values between 0 and -1 V are obtained for the vertical deflection and ~ 0 V is obtained for the horizontal deflection.
  6. Check to ensure the laser sum signal is maximized. If necessary, repeat step 4.5 to re-adjust the position of the laser beam on the AFM tip and the position of the photodiode to obtain the maximum sum signal.
    NOTE: It may be necessary to reposition the AFM probe on the probe holder to obtain a maximum sum signal even if step 4.5 is repeated.

5. Calibrating the Deflection Sensitivity and Spring Constant of the AFM Probe

  1. Make a scratch on a 60-mm culture dish with a forcep and fill the dish with distilled water. Place the culture dish on the sample holder plate. In this case, mount the dish on the motorized XY scan stage of an inverted microscope.
  2. Place a magnetic plate holder on top of the plate to keep it secure during imaging.
  3. Click 'Up' arrow in the Navigation menu on the software to move the AFM head up to nearly its highest position to ensure that the AFM probe will not touch the dish.
    NOTE: This step is very important as it avoids breaking the AFM tip.
  4. Place the AFM head on the microscope stage.
  5. Use the microscope to focus on the scratch on the plate. Use the joystick, or click the 'Down' arrow in the Navigation menu, to slowly and carefully lower the AFM probe into the PBS. Position the head slightly above the scratch in the plate.
    NOTE: If the initial position of the AFM head is closer to the sample, the engage time will be significantly reduced.
  6. Before engaging, re-adjust the position of the laser beam on the AFM tip and the position of the photodiode to obtain the maximum SUM signal as necessary.
  7. Select a tip type by clicking Change Probe in the Setup menu.
  8. Click Check Parameters and set the parameters: Scan Size to 0, Scan Rate to 1 Hz, Sample/line to 256 and Deflection Setpoint to 20 nm. Click Engage. The Engage Status window will remain open until the probe makes contact with the surface of the plate. After engaging the probe, click Ramp.
  9. Click Expanded Mode in the Scan Toolbar menu and set the parameters: Ramp Size to between 500 nm and 1 µm, Ramp Rate to 2 Hz, Number of Samples to 256, Tip Radius to 500 nm, Sample Poisson's Ratio to 0.5 (assumes the material to be measured is perfectly incompressible), Tip Half Angle to 0, Trigger Mode to Relative and Trigger Threshold to between 20 and 100 nm.
  10. Click Ramp Continuous in the Ramp Toolbar menu to obtain a force curve on the plate (Figure 3A). In this force curve, set channel 1 to deflection error.
    NOTE: This will allow the software to graph the results as vertical deflection vs. z position.
    1. Click at the left or right ends of the force curve and drag the cursor to encompass a linear region of the force curve (Figure 3A, dashed red lines). Use these two lines to mark the boundaries of the sloped region to be fit with a straight line.
  11. Select Ramp in the Toolbar and click Update Sensitivity. Record the value and repeat this step four more times. Select Calibrate in the Toolbar and then click Detector. Input an average value from the five measurements in the Deflection Sensitivity box.
  12. Click Withdraw 2 - 3 times to raise the AFM head. This step is important to prevent interaction between the AFM tip and the plate during the thermal tune process. Click Thermal Tune in the Toolbar.
  13. Set Thermal Tune Range of 1 - 100 kHz (This information can be obtained from the manufacturer's catalog) and Deflection Sensitivity Correction to 1.144 for v-shaped cantilevers and 1.106 for rectangular cantilevers.
  14. In the Thermal Tune menu, click Acquire Data to obtain a thermal tune curve (Figure 3B). Using the AFM software, place red dashed lines on either side of the curve (as shown in Figure 3B) by dragging the mouse in from the edge of the graph to define the boundaries for fitting. Select either the Lorentzian (Air) or the Simple Harmonic oscillator (Fluid) model depending on which better fits the data.
  15. Click Fit Data, then Calculate Spring K and save this value. Repeat the spring constant calibrations several times and use the average value. Click Withdraw several times.
  16. Remove the AFM head from the microscope stage and place it on the alignment unit. Remove the dish from the microscope stage.

Figure 3
Figure 3: AFM Force Curves Used in the Calibration of AFM Probes. (A) A representative AFM force curve (a calibration curve). The extension portion of the force curve between the vertical red dashed lines was used to determine the cantilever deflection sensitivity. (B) A simple harmonic oscillator fit graph used to calculate the spring constant of the cantilever as previously described20. Please click here to view a larger version of this figure.

6. Measuring the Elastic Modulus on Mouse Arteries Ex Vivo

  1. Place the 60-mm culture dish containing the aortic tissue on the microscope stage, and secure the plate with the magnetic plate holder.
  2. Place the AFM head on the microscope stage. Make certain that the AFM probe does not make contact with the aorta but gently makes contact with PBS and forms a meniscus. If necessary, place the AFM head on the alignment unit and click Withdraw until there is enough clearance to prevent contact, then place the AFM head on the microscope stage.
  3. Click Navigate. Using the joystick or clicking 'Down' arrow, slowly lower the AFM probe to locate the cantilever above the aorta. Adjust the photodiode position using the detector positioning knobs on the AFM head if necessary.
  4. Click Engage to allow the cantilever to make contact with the aorta.
  5. Once the aorta is engaged, ensure that the piezo center is stable and click Ramp. If the piezo center is fluctuating, this may be the result of a false engagement. Withdraw the probe and increase the vertical offset of the laser on the photodiode by small increments (~ 0.5 V) and re-engage.
    1. Also, if the probe is far above the sample surface, manually lower the probe closer to the sample surface before re-engaging. If the previous steps do not eliminate the fluctuation, try exchanging the probe.
  6. Set the Ramp Size to 3 µm, the Trigger Mode to Relative and the Trigger Threshold to 100 nm and click Ramp Continuous. Observe that the point of contact between the probe and the sample occurs at approximately the center to the lower ¾ of the Z ramp cycle. If this is not observed, disengage from the sample, adjust the Ramp size as needed, and re-engage the sample.
  7. Click Microscope in the Menu Bar and then Engage Settings. Change the SPM Withdraw to 30 µm. Click Ramp Continuous in the Ramp Toolbar menu.
  8. After observing the force curve, click Capture in the Menu bar and then Capture Filename. Enter a desired file name with the ending ".000" (this will allow additional captured files to increase in number by 1). Select a designated-folder and save the data.
  9. Click Capture in the Capture Toolbar menu. Click Withdraw and then Navigate. Use the Joystick or software controls to position the cantilever over another area of the aorta (next to the initially measured point; see Figure 4).
  10. Click Engage, Ramp, and Ramp Continuous, respectively. After observing the force curve, click Stop and then Capture.
  11. Repeat steps 6.9 - 6.10. Capture at least 5 measurements per area as shown in Figure 4. NOTE: We typically collect 15 - 25 force curves from 3 - 5 different locations in each tissue as shown in Figure 4, respectively.

Figure 4
Figure 4: Cartoon of a Cantilever Approaching and Indenting the Tissue (Area 1). This AFM measurement is repeated up to 15 - 25 times from 3 - 5 different locations (Areas 1 - 5) in each artery to acquire the stiffness of the overall tissue sample. Please click here to view a larger version of this figure.

7. Data Analysis

  1. Open force curve analysis software.
  2. Click Find and Open in the menu bar, and double click on a file to be analyzed.
  3. Click Modify Force Parameters in the toolbar menu to check the deflection sensitivity, Spring Constant, Tip Radius, Tip Half Angle and Poisson's ratio. To change the parameters check the box next to it and enter the correct values in the new value column. Then click Execute.
  4. If force curves are noisy, click Boxcar Filter and set inputs for Direction to Extend, Average Points to 3 and Filter Order to 0th. Click Execute to smooth the data.
  5. Click Baseline Correction in the menu bar and set inputs for Direction to Extend, Plot Units to Force, Type to Separation, Correction Order to 1st and Extend Baseline Source to Extend. Adjust the vertical dotted blue lines to encompass the flat portion of force curve and then click Execute.
  6. Click Indentation in the toolbar menu and set inputs for Active Curve to Extended, Fit Method to Contact Point Based, Contact Point Algorithm to Treat as Fit Variable, Include Adhesion Force to No, Max Force Fit Boundary to 30%, Min Force Fit Boundary to 0% and Fit Model to Hertzian (Spherical).
    NOTE: In our measurements, significant adhesion between the tip and sample (a negative deflection of the cantilever in the retraction curve) was rarely observed. In cases where such adhesion is observed, the appropriate model (DMT or JKR) should be used for analysis18,19.
  7. Save the values of Young's modulus. Analyze the Young's (elastic) modulus of each of the 3 - 5 areas (5 force curves per area) taken within a small distance of each other as shown in Figure 4.
    NOTE: To remove artifacts, exclude Young's moduli > 100 kPa (normally ~10% of total measurements) from the analysis.
  8. Calculate a mean Young's modulus value for each of the 3 - 5 areas (that have been measured) and use these values to calculate a mean elastic modulus for the aorta as a whole.
    NOTE: At least 3 and more often 4 - 6 individual aortas are used to obtain an accurate assessment of arterial stiffness. The final results are plotted as mean + SEM of "n" independent experiments. The exact number of aortas needed will, of course, depend on the level of accuracy required.

Subscription Required. Please recommend JoVE to your librarian.

Representative Results

Figure 5A shows a phase contrast image of the descending (thoracic) aorta from a 6-month old, male C57BL/6 mouse. The AFM cantilever is in place directly above the tissue and ready for indentation. Figures 5B and 5C demonstrate representative force curves obtained by AFM indentation in contact mode. Green lines shown in Figures 5B and 5C represent the best fit curves obtained using the Hertzian model for a sphere. In Figure 5D, the mean stiffness of the descending aortas and aortic arches were determined from three individual mice as described in the text. Note that the descending aorta and aortic arch represent regions of laminar and disturbed flow, respectively. Nevertheless, their (mechanically unloaded) elastic moduli are similar as determined by AFM.

Figure 5
Figure 5: The Analyzed Force-Indentation Curves and Stiffness Data. (A) Phase contrast micrograph showing an AFM cantilever over a mouse descending aorta ex vivo. Scale bar, 100 µm. (B-C) A set of two representative force-indentation curves acquired for (B) the descending aorta and (C) the aortic arch. (D) Mean stiffness of the mouse descending aorta and aortic arch was determined as described above. Error bars show mean + SEM; n= 3 independent biological replicates. Please click here to view a larger version of this figure.

Subscription Required. Please recommend JoVE to your librarian.


AFM indentation can be used to characterize the stiffness (elastic modulus) of cells and tissues. In this paper, we provide detailed step-by-step protocols to isolate the descending aorta and aortic arch in the mouse and determine the elastic moduli of these arterial regions ex vivo. We now summarize and discuss the technical issues and limitations of the method described in this paper.

Several technical issues can arise in the isolation and analysis of mouse aortas given their small and thin nature. When the cleaned arteries are being opened longitudinally, care must be taken not to disrupt the intima (luminal surface) where the elastic modulus data is collected. Excess PBS in the final sample dish prevents proper gluing of the arteries onto the dish, and this needs to be carefully removed using a paper tissue without touching the artery before gluing. Note, however, that the isolated artery can stick to the paper tissue while attempting to remove excessive PBS, and this can damage the sample. While gluing the arteries to the culture dish, it is extremely important that the artery is not stretched and that only a small amount of adhesive is applied bit-by-bit to each end of the artery. When performing the AFM-indentation, it is critical to avoid probing at the ends of the artery where the adhesive has been applied. Lastly, because freshly isolated arteries are used for the measurements of elastic modulus, the time elapsed from harvesting to measurement should be minimized.

Since the spherical tips used in this study have a radius of 500 nm, an indentation depth of up to 500 nm can be accurately analyzed using the Hertz model. This indentation depth would correlate with the top layer of endothelial cells located in the intima21. To probe the mechanics of the sub-endothelial layers of arterial samples, larger colloidal probes (10 - 20 µm in diameter) could be used for indentation and changes in the calculated stiffness with indentation depth could be determined22,23. Also, since biological samples are usually viscoelastic rather than purely elastic, stress relaxation measurements (monitoring the decay in applied force at a constant indentation depth) could be used to determine the viscous component of arterial mechanical properties24,25.

A potential limitation of AFM analysis is the scan size, which only measures a small region of the tissue. Most biological samples, including arteries and cells, are not topographically and biomechanically homogeneous, and this heterogeneity can potentially result in artifactually large variations of the elastic modulus depending on smoothness of the indentation site, indentation depth, and the amount of force applied to the sample surface. To obtain a representative mean value of the overall elastic modulus, it is important to perform repeated AFM-indentation at multiple random locations through the arteries, as shown in Figure 4. Furthermore, we use an appropriately-sized spherical tip, as previous studies have demonstrated that AFM-indentation with a sharp pyramidal tip resulted in higher estimates of the elastic modulus and damaged soft biological samples26,27.

Even though our ex vivo AFM measurements of arterial stiffness appear to agree well with molecular markers of smooth muscle cell stiffening2, it is important to realize that these arterial samples are not mechanically loaded, and mechanical load is likely to play an important role in overall arterial mechanics. Comparisons of arterial stiffness as determined by AFM, myography (an ex vivo method compatible with mechanical loading)28 and pulse-wave velocity (an in vivo measurement of arterial stiffness)29 will likely provide the most comprehensive understanding of arterial mechanics.

We have described the AFM in contact mode to measure the ex vivo stiffness of mouse arteries. This method estimates the average tissue stiffness by randomly indenting on multiple regions of the aorta. To examine the spatial distribution of stiffness from bigger regions of tissues, a recent paper has used AFM in force-volume mode30. This approach simultaneously obtained a map of stiffness variations and a high-resolution image of topographical surface of the tissue. In addition to measuring the stiffness of tissue samples, the AFM in force-volume mode can be used in cells to monitor the spatial distributions of intracellular stiffness10,31.

Subscription Required. Please recommend JoVE to your librarian.


The authors have nothing to disclose.


AFM analysis was performed on instrumentation supported by the Pennsylvania Muscle Institute and the Institute for Translational Medicine and Therapeutics, Perelman School of Medicine, the University of Pennsylvania. This work was supported by NIH grants HL62250 and AG047373. YHB was supported by post-doctoral fellowship from the American Heart Association.


Name Company Catalog Number Comments
BioScope Catalyst AFM system Bruker
Nikon Eclipse TE 200 inverted microscope Nikon Instruments
Silicon nitride AFM probe Novascan Technologies PT.SI02.SN.1 0.06 N/m cantilever; 1 µm SiO2 particle
Dumont #5 forceps Fine Science Tools 11251-10 See section 1.4
Dumont #5SF forceps Fine Science Tools 11252-00 See section 1.8
Fine Scissors-ToughCut Fine Science Tools 14058-11 See section 1.4 (medium sized)
Vannas-Tübingen spring scissors Fine Science Tools 15008-08 See section 1.6 (small sized)
60 mm TC-treated cell culture dish Corning 353004
Dulbecco's Phosphate-Buffered Saline, 1x Corning 21-031-CM Without calcium and magnesium
Krazy Glue instant all purpose liquid Krazy Glue KG58548R See section 2.2
Gel-loading tips, 1 - 200 µl Fisher 02-707-139 See section 2.2
Tip Tweezers Electron Microscopy Sciences 78092-CP See section 3.2
50-mm, clear wall glass bottom dishes TED PELLA 14027-20 See section 4.4



  1. Kothapalli, D., et al. Cardiovascular Protection by ApoE and ApoE-HDL Linked to Suppression of ECM Gene Expression and Arterial Stiffening. Cell Rep. 2, 1259-1271 (2012).
  2. Liu, S. -L., et al. Matrix metalloproteinase-12 is an essential mediator of acute and chronic arterial stiffening. Sci Rep. 5, 17189 (2015).
  3. Lakatta, E. G. Central arterial aging and the epidemic of systolic hypertension and atherosclerosis. J Am Soc Hypertens. 1, 302-340 (2007).
  4. Stehouwer, C. D. A., Henry, R. M. A., Ferreira, I. Arterial stiffness in diabetes and the metabolic syndrome: a pathway to cardiovascular disease. Diabetologia. 51, 527-539 (2008).
  5. Steppan, J., Barodka, V., Berkowitz, D. E., Nyhan, D. Vascular Stiffness and Increased Pulse Pressure in the Aging Cardiovascular System. Cardiol Res Pract. 2011, 263585 (2011).
  6. Duprez, D. A., Cohn, J. N. Arterial stiffness as a risk factor for coronary atherosclerosis. Curr Atheroscler Rep. 9, 139-144 (2007).
  7. Mitchell, G. F., et al. Arterial Stiffness and Cardiovascular Events: The Framingham Heart Study. Circulation. 121, 505-511 (2010).
  8. Sutton-Tyrrell, K., et al. Elevated Aortic Pulse Wave Velocity, a Marker of Arterial Stiffness, Predicts Cardiovascular Events in Well-Functioning Older Adults. Circulation. 111, 3384-3390 (2005).
  9. Klein, E. A., et al. Cell-Cycle Control by Physiological Matrix Elasticity and In Vivo Tissue Stiffening. Curr Biol. 19, 1511-1518 (2009).
  10. Bae, Y. H., et al. A FAK-Cas-Rac-lamellipodin signaling module transduces extracellular matrix stiffness into mechanosensitive cell cycling. Sci signal. 7, ra57 (2014).
  11. Thyberg, J., Hedin, U., Sjölund, M., Palmberg, L., Bottger, B. A. Regulation of differentiated properties and proliferation of arterial smooth muscle cells. Arterioscler Thromb Vasc Biol. 10, 966-990 (1990).
  12. Owens, G. K., Kumar, M. S., Wamhoff, B. R. Molecular Regulation of Vascular Smooth Muscle Cell Differentiation in Development and Disease. Physiol Rev. 84, 767-801 (2004).
  13. Huynh, J., et al. Age-Related Intimal Stiffening Enhances Endothelial Permeability and Leukocyte Transmigration. Sci Transl Med. 3, 112ra122 (2011).
  14. Safar, M. E., Levy, B. I., Struijker-Boudier, H. Current Perspectives on Arterial Stiffness and Pulse Pressure in Hypertension and Cardiovascular Diseases. Circulation. 107, 2864-2869 (2003).
  15. Raffetto, J. D., Khalil, R. A. Matrix metalloproteinases and their inhibitors in vascular remodeling and vascular disease. Biochem Pharmacol. 75, 346-359 (2008).
  16. Muller, D. J., Dufrene, Y. F. Atomic force microscopy as a multifunctional molecular toolbox in nanobiotechnology. Nat Nanotechnol. 3, 261-269 (2008).
  17. Hsu, B. Y., Bae, Y. H., Mui, K. L., Liu, S. -L., Assoian, R. K. Apolipoprotein E3 Inhibits Rho to Regulate the Mechanosensitive Expression of Cox2. PLoS ONE. 10, e0128974 (2015).
  18. Johnson, K. L., Kendall, K., Roberts, A. D. Surface Energy and the Contact of Elastic Solids. Proc R Soc Lond A. 324, 301-313 (1971).
  19. Derjaguin, B. V., Muller, V. M., Toporov, Y. P. Effect of contact deformations on the adhesion of particles. J Colloid Interface Sci. 53, 314-326 (1975).
  20. Hutter, J. L., Bechhoefer, J. Calibration of atomic-force microscope tips. Rev Sci Instrum. 64, 1868-1873 (1993).
  21. Pries, A. R., Secomb, T. W., Gaehtgens, P. The endothelial surface layer. Pflugers Arch EJP. 440, 653-666 (2000).
  22. Pogoda, K., et al. Depth-sensing analysis of cytoskeleton organization based on AFM data. Eur Biophys J. 41, 79-87 (2012).
  23. Mendez, M. G., Restle, D., Janmey, P. A. Vimentin Enhances Cell Elastic Behavior and Protects against Compressive Stress. Biophys J. 107, 314-323 (2014).
  24. Moreno-Flores, S., Benitez, R., Md Vivanco,, Toca-Herrera, J. L. Stress relaxation and creep on living cells with the atomic force microscope: a means to calculate elastic moduli and viscosities of cell components. Nanotechnology. 21, 445101 (2010).
  25. Darling, E. M., Topel, M., Zauscher, S., Vail, T. P., Guilak, F. Viscoelastic properties of human mesenchymally-derived stem cells and primary osteoblasts, chondrocytes, and adipocytes. J Biomech. 41, 454-464 (2008).
  26. Dimitriadis, E. K., Horkay, F., Maresca, J., Kachar, B., Chadwick, R. S. Determination of Elastic Moduli of Thin Layers of Soft Material Using the Atomic Force Microscope. Biophys J. 82, 2798-2810 (2002).
  27. Mahaffy, R. E., Shih, C. K., MacKintosh, F. C., Käs, J. Scanning Probe-Based Frequency-Dependent Microrheology of Polymer Gels and Biological Cells. Phys Rev Lett. 85, 880-883 (2000).
  28. Amin, M., Le, V. P., Wagenseil, J. E. Mechanical Testing of Mouse Carotid Arteries: from Newborn to Adult. J Vis Exp. e3733 (2012).
  29. Laurent, S., et al. Expert consensus document on arterial stiffness: methodological issues and clinical applications. Eur Heart J. 27, 2588-2605 (2006).
  30. Plodinec, M., et al. The nanomechanical signature of breast cancer. Nat Nano. 7, 757-765 (2012).
  31. Raman, A., et al. Mapping nanomechanical properties of live cells using multi-harmonic atomic force microscopy. Nat Nano. 6, 809-814 (2011).



    Post a Question / Comment / Request

    You must be signed in to post a comment. Please or create an account.

    Usage Statistics