This work was supported by the Engineering and Physical Sciences Research Council [grant number EP/M028739/1]. RSE was supported by a Santander Postgraduate Research Award 2015.

Caution: Please consult biological safety protocols and all relevant material safety data sheets (MSDS) before use. The laser employed in these experiments is a Class 3B laser; compliance with local rules for a safe use of the system is required. Please use all appropriate safety practices when performing a laser spectroscopy measurement including the use of personal protective equipment (safety goggles).
Tail tendons were obtained from 7-8 week old Wistar rats euthanized for other purposes in accordance with EU regulation 1099/2009 and The Welfare of Animals (slaughter or killing) Regulations 1995. Bovine nuchal ligaments were obtained from a local abattoir.
1. Preparation of Sample Fibers
NOTE: Protein fibers of the extracellular matrix can be extracted from various tissues, using different procedures. Protocols were refined based on widely applied procedures.
<ol>
	<li>Extraction of collagen fibers from rat tail
	<ol>
		<li>Sacrifice a rat by intra-peritoneal injection of 100 mg/kg of body weight sodium pentobarbitone. Then sever the tail directly at the point of contact with the body, pressing down with a single-edge razor blade. Wrap the tail in cling film and store it frozen at -20 &#176;C until required.</li>
		<li>Collect the tail from the freezer, cut a 20 mm long segment from the proximal end whilst still frozen and then leave it to thaw in a Petri dish filled with phosphate buffered saline (PBS) solution (pH 7.4) at RT.</li>
		<li>Once the tail is thawed, make an incision along the length of the segment using a scalpel to split the skin. Then peel back to reveal four sheathed tendon bundles about the tail vertebra.</li>
		<li>Using fine forceps and being careful not to apply any pre-strain, gently draw each fiber out of the sheath and place it in a vial containing distilled water with 0.01% w/v sodium azide (NaN3) to prevent bacterial growth, and store refrigerated. A single tail yields around thirty tendon fibers.</li>
		<li>To obtain pure fibrous type I collagen, apply a three part enzymatic digestion process10 to the tendon fibers to remove the proteoglycans and all other noncollagenous material.
		<ol>
			<li>First, immerse the fibers in 0.125 U/ml chondroitinase ABC in 0.05 M Tris buffer and 0.06 M sodium acetate (CH3COONa) at pH 8.0 for 24 hr at 37 &#176;C in a shaking incubator at 200 rpm.</li>
			<li>Then, immerse the fibers in 1 U/ml streptomyces hyaluronidase in 0.05 M Tris buffer and 0.15 M sodium chloride (NaCl) at pH 6.0 and return to the shaking incubator for 24 hr at 37 &#176;C.</li>
			<li>Finally, immerse the fibers in 1 mg/ml of trypsin in 0.05 M sodium phosphate (NaHPO4) and 0.15 M NaCl at pH 7.2 for 16 hr in the shaking incubator at 37 &#176;C.</li>
		</ol>
		</li>
		<li>Store the purified fibers refrigerated in vials containing distilled water, with 0.01% NaN3 to prevent bacterial growth, until required for measurement.</li>
	</ol>
	</li>
	<li>Extraction of elastin fibers from bovine nuchal ligament
	<ol>
		<li>Obtain bovine nuchal ligament from the abattoir, wrap it in cling film and store it frozen at -20 &#176;C until use.</li>
		<li>To produce pure elastin, collect the ligament from the freezer, allow it to thaw at RT, defat it using a scalpel and digest the ligament in a boiling water bath according to the Lansing procedure,11 as follows.
		<ol>
			<li>Prepare a 0.1 M solution of sodium hydroxide (NaOH) in distilled water and add it to the defatted ligament in a conical flask, covering the tissue.</li>
			<li>Boil the flask in a water bath at 95 &#176;C for 45 min.</li>
			<li>Remove the ligament from the digestion flask and wash the insoluble tissue block repeatedly in distilled water until pH 7.0 (monitored using a pH meter) is obtained.</li>
			<li>Remove the tissue from the final wash solution and submerge it in distilled water (mixed with 0.01% NaN3 to prevent bacterial growth) in a sealed container and store it refrigerated.</li>
		</ol>
		</li>
		<li>Collect the tissue from the refrigerator and, being careful not to apply too much force and pre-strain, use tweezers to gently pull smaller elastin segments (20 to 50 mm long, ca. 2 mm thick) away from the larger block and place them in a Petri dish with PBS solution (pH 7.4).</li>
		<li>Using fine forceps, gently tease small fiber bundles around 1 mm thick and cut them to lengths of a few mm using a scalpel.</li>
		<li>Transfer the fibers to vials containing distilled water (with 0.01% NaN3 to prevent bacterial growth) and store them refrigerated until required for measurement.</li>
	</ol>
	</li>
	<li>Mounting the fibers onto reflective substrate
	<ol>
		<li>Using a diamond cutter, cut a piece of reflective silicone slide.</li>
		<li>To create a hydrated compartment, cut a strip of Parafilm to fit over the silicone slide with a hollow cut in the center (large enough to fit a fiber) and place it onto the silicone substrate. 
		NOTE: For dry fiber measurements, cut the parafilm into a U-shape so that one of the four sides stays open to the air when sealed in step 1.3.4.</li>
		<li>Remove the fibers from the refrigerator, use a pair of fine forceps to collect a single fiber from the storage solution and place it in a small Petri dish filled with pure water at RT for 5 min to wash the sample. Then, collect the fiber and transfer it to the center of the parafilm hollow on the silicone substrate. 
		Careful: Avoid damaging the fiber by stretching it during this operation, and avoid reorienting the sample on the substrate as this may cause a change in mechanical properties.</li>
		<li>Place a thin glass coverslip over the fiber and seal the chamber by passing a heated soldering iron gently over the glass surface to melt the parafilm beneath the glass. 
		Careful: Avoid damaging the fiber by not bringing the soldering tip too close or heating the substrate excessively.</li>
		<li>Place the sealed chamber on a flat surface under a small weight and leave it for around 12 hr to achieve a good contact between the sample and silicon substrate while avoiding damage to the specimen.</li>
		<li>Remove the weight and secure the chamber in place on the substrate, using screws.</li>
	</ol>
	</li>
</ol>
2. Setting up the Brillouin Experiment and Acquiring Fiber Spectra
<ol>
	<li>Preparation of sample compartment
	<ol>
		<li>Mount the sample prepared as in part 1.3 onto a vertical holder equipped with a goniometer to enable in-plane rotation of the sample while maintaining a constant scattering angle (2&#934; = 90&#176;; see Figure SI-1) and scattering volume position.</li>
		<li>Perform an accurate focus adjustment of the laser light on the sample through the lens.9 
		Careful: The laser output power may be too high and produce a burn in the sample. Make sure that it is set sufficiently high to give a good sensitivity but not too high to avoid damage to the sample. Here we used a power of ca. 76 mW on the sample. This was sufficient to get a good sensitivity without burning the sample, also considering that this is thin and in contact with a substrate that helps dissipating the heat generated by laser illumination.</li>
		<li>Position the sample at a 45&#176; angle (&#934;) to the incident laser beam using a Vernier scale. Achieve optimal positioning by running a measurement and maximizing the intensity of the peaks in the spectrum (see below).</li>
	</ol>
	</li>
	<li>Setting up the spectrometer
	<ol>
		<li>Open the software for acquisition and manipulation of the data and set up the acquisition of a Brillouin spectrum of the sample12. The procedure described here applies to the multipass tandem interferometer (Figure SI-1A).</li>
		<li>Align the two Fabry-Perot (FP) interferometers independently changing the voltages applied to the piezo by the control unit. For this pre-alignment procedure, observe the light reflected by each FP. When the intensity reflected by the two FPs tends to zero, the correct alignment is reached.</li>
		<li>Calibrate the spectrum: the accessible frequency range, or free spectral range (FSR), is dependent on the distance between the two mirrors of the first FP cavity, L, through FSR = c/2L, where c is the speed of light and L is measured by a dial-gauge.</li>
		<li>Synchronize the scans of the two FP interferometers and switch the optical system to the tandem multipass configuration. A feedback control of the transmitted laser light intensity will automatically maintain the alignment of the two FPs during the measurement.</li>
	</ol>
	</li>
	<li>Measurement of Brillouin Spectra 
	Careful: The Brillouin spectrum is highly dependent on the temperature and hydration of the sample and so careful control of these parameters is key to obtaining reproducible spectra.
	<ol>
		<li>Start the acquisition of a Brillouin spectrum of the sample and run it until a good signal-to-noise ratio is achieved. This may take several minutes depending on the scattering cross section, concentration and thickness of the sample. 
		NOTE: There is not a rule of thumb for the signal-to-noise ratio but the spectral quality is checked by the experimentalist based on the specific sample analyzed. There is a trade-off between spectral quality and duration of the measurement, therefore the experimental parameters need to be selected according to the specific application.</li>
		<li>For the measurement of a dry specimen, take successive spectra&#160;&#8212; for each of them, following step 2.3.1&#160;&#8212; until no changes in the position of the peaks is observed. This is achieved when the sample is at equilibrium with the room atmosphere and no further drying will affect the spectrum.</li>
		<li>Select the light polarization (VV or VH; V stands for vertical and H for horizontal direction of the light polarization relative to the scattering plane) and acquire spectra at each angle to fiber axis (&#952; ; Figure SI-1) by rotating the sample in plane by hand.</li>
		<li>Save the Brillouin spectra to file for subsequent processing.</li>
	</ol>
	</li>
</ol>
3. Analysis of Brillouin Spectra
NOTE: Fit analysis of Brillouin peaks can be performed using various functions. A damped harmonic oscillator (DHO) function4,13 was selected as this is a valid model for peaks originating from damped acoustic modes in viscoelastic media.
<ol>
	<li>Fit analysis of Brillouin peaks
	<ol>
		<li>Select the spectral range for the peak of interest in the Brillouin spectrum.</li>
		<li>Enable a baseline in the fit if the spectral background is much higher than zero. 
		NOTE: The baseline can vary between spectra. Ensure that the correction is applied in a systematic and reproducible manner.</li>
		<li>Apply a detailed least squares fitting using a DHO function4,13 to the Brillouin peak of interest iteratively until convergence is achieved and the best fitting curve is obtained. Then, save the fit results to file.</li>
		<li>Obtain average values from the fit parameters of the two peaks of each Brillouin doublet.</li>
		<li>Calculate the acoustic wave velocity from the peak frequency (using the expression below).</li>
		<li>Plot the fit results through graphs, e.g., acoustic wave velocity vs. angle to fiber axis,&#160;&#952; , and apply relevant models (e.g., for acoustically anisotropic systems9) to extract mechanical quantities such as elasticity tensor coefficients.</li>
	</ol>
	</li>
</ol>

<ol>
	<li>Brillouin, L. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Diffusion+de+la+lumi&#232;re+et+des+rayonnes+X+par+un+corps+transparent+homog&#232;ne;+influence+de+l'agitation+thermique.">Diffusion de la lumi&#232;re et des rayonnes X par un corps transparent homog&#232;ne; influence de l'agitation thermique.</a> Ann. Phys. 17, 88-122 (1922).</li><li>Caponi, S., Corezzi, S., Mattarelli, M., Fioretto, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Stress+effects+on+the+elastic+properties+of+amorphous+polymeric+materials.">Stress effects on the elastic properties of amorphous polymeric materials.</a> J. Chem. Phys. 141 (21), 214901 (2014).</li><li>Mattarelli, M., Montagna, M., Still, T., Schneider, D., Fytas, G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Vibration+spectroscopy+of+weakly+interacting+mesoscopic+colloids.">Vibration spectroscopy of weakly interacting mesoscopic colloids.</a> Soft Matter. 8 (15), 4235-4243 (2012).</li><li>Comez, L., Masciovecchio, C., Monaco, G., Fioretto, D., Robert, E. C., Robert, L. S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> Solid State Physics. 63, 1-77 (2012).</li><li>Madami, M., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Direct+observation+of+a+propagating+spin+wave+induced+by+spin-transfer+torque.">Direct observation of a propagating spin wave induced by spin-transfer torque.</a> Nat. Nanotechnol. 6 (10), 635-638 (2011).</li><li>Harley, R., James, D., Miller, A., White, J. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Phonons+and+the+elastic+moduli+of+collagen+and+muscle.">Phonons and the elastic moduli of collagen and muscle.</a> Nature. 267 (5608), 285-287 (1977).</li><li>Cusack, S., Miller, A. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Determination+of+the+elastic+constants+of+collagen+by+Brillouin+light+scattering.">Determination of the elastic constants of collagen by Brillouin light scattering.</a> J. Mol. Biol. 135 (1), 39-51 (1979).</li><li>Vaughan, J. M., Randall, J. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Brillouin+scattering,+density+and+elastic+properties+of+the+lens+and+cornea+of+the+eye.">Brillouin scattering, density and elastic properties of the lens and cornea of the eye.</a> Nature. 284 (5755), 489-491 (1980).</li><li>Palombo, F., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Biomechanics+of+fibrous+proteins+of+the+extracellular+matrix+studied+by+Brillouin+scattering.">Biomechanics of fibrous proteins of the extracellular matrix studied by Brillouin scattering.</a> J. R. Soc. Interface. 11 (101), (2014).</li><li>Sivan, S. S., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Age-related+accumulation+of+pentosidine+in+aggrecan+and+collagen+from+normal+and+degenerate+human+intervertebral+discs.">Age-related accumulation of pentosidine in aggrecan and collagen from normal and degenerate human intervertebral discs.</a> Biochem. J. 399 (1), 29-35 (2006).</li><li>Soskel, N. T., Wolt, T. B., Sandberg, L. B., Leon, W. C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> Methods in Enzymology. 144, 196-214 (1987).</li><li>Fioretto, D., Scarponi, F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Dynamics+of+a+glassy+polymer+studied+by+Brillouin+light+scattering.">Dynamics of a glassy polymer studied by Brillouin light scattering.</a> Mater. Sci. Eng. A. 521-522, 243-246 (2009).</li><li>Palombo, F., Madami, M., Stone, N., Fioretto, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Mechanical+mapping+with+chemical+specificity+by+confocal+Brillouin+and+Raman+microscopy.">Mechanical mapping with chemical specificity by confocal Brillouin and Raman microscopy.</a> Analyst. 139 (4), 729-733 (2014).</li><li>Scarcelli, G., Yun, S. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Multistage+VIPA+etalons+for+high-extinction+parallel+Brillouin+spectroscopy.">Multistage VIPA etalons for high-extinction parallel Brillouin spectroscopy.</a> Opt. Express. 19 (11), 10913-10922 (2011).</li><li>Scarcelli, G., Kim, P., Yun, S. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=In+Vivo+Measurement+of+Age-Related+Stiffening+in+the+Crystalline+Lens+by+Brillouin+Optical+Microscopy.">In Vivo Measurement of Age-Related Stiffening in the Crystalline Lens by Brillouin Optical Microscopy.</a> Biophys. J. 101 (6), 1539-1545 (2011).</li><li>Scarcelli, G., Yun, S. 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The authors have nothing to disclose.

Brillouin scattering spectroscopy is a unique tool by which the individual components of the elasticity tensor of a protein fiber can be characterized in unprecedented detail. Furthermore, the measurements can be made on a microscopic scale and thereby will provide us with novel insights into the micro-scale mechanics of biological structures, allowing us, for the first time, to understand the mechanical, and probably functional, significance of the complexities in matrix architecture and biochemistry which has been revealed in recent years.
The technique measures mechanical properties in a GHz frequency range. This domain has never been explored before for structural biopolymers and it both raises and provides the means to answer fundamental questions about molecular mechanisms of elasticity.
We described the steps to extract collagen and elastin fibers from animal tissues and to measure Brillouin scattering spectra using a reflective substrate to achieve the complete description of fiber biomechanics. Critical steps within the protocol are those that ensure that purified fibers are obtained and appropriate experimental conditions are in place for reproducible measurements of the fibrous proteins. However, it must be borne in mind that the extraction procedures may modify the mechanical properties of the fibers.
Modifications of the technique involve the coupling with optical microscopy for microfocused Brillouin scattering and mapping approaches13 and the possible combination with complementary techniques (e.g., Raman scattering). Current applications of the technique are mainly focused on excised biological materials, but important developments, e.g., those based on multiple VIPA etalons14, are making possible the translation of this technique from the benchtop to the bedside with a range of applications already demonstrated15,16 including potential in vivo applications. The VIPA approach is an alternative to what we describe; it has faster acquisition time but is not necessarily appropriate in the case of opaque samples such as those analyzed here. Moreover, the use of a reflective substrate is not practical in set-ups that use the VIPA etalons because their contrast would not be sufficient to reject the quasi-elastic light. Limitations related to the speed of acquisition of a spectral dataset and the inherently weak scattering cross section of the material may limit applications to dynamic biological systems and to the acquisition of data from deep within tissues, but technical refinements may improve on current performance.
BLS promises to be a major tool in fundamental biophysical research on the extracellular matrix and thereby to produce new insights into the evolution of mechanical properties during matrix growth and their loss in pathological degeneration. However, it is important to remember that the measurements are noninvasive and might therefore be undertaken in vivo. Indeed, this has already been achieved in the cornea16 and such work may provide a platform for the development of new diagnostic tools for a wide range of connective tissue disorders.
Ultrasound elastography and atomic force microscopy (AFM) are alternative methods of micromechanical measurement, but the BLS technique offers better spatial resolution (on a subcellular scale) than the former and, unlike AFM, imposes no mechanical forces on the specimen and is not restricted to the analysis only of surface features. Brillouin moduli of collagen and elastin are in the GPa range, whilst Young&#39;s moduli from macroscopic strains are of the order of MPa (further details will be reported elsewhere). This result indicates a differential elastic modulus with a strong dependence on the excitation frequency, owing to the viscoelastic behavior of the fibers. BLS can be applied to a wide range of problems and materials in biomedical science. It can help in answering questions on physiology and pathology of biological tissues, as well as provide a physical tool for the fundamental understanding of materials and interactions at the molecular level.

The Brillouin light scattering (BLS) effect was discovered by L&#233;on Brillouin in 1922.1 It consists of the inelastic scattering of visible light by thermally activated acoustic phonons in a material. In solid state physics, acoustic phonons are coherent vibrations of all atoms in a lattice. A one-dimensional chain of two alternating types of atoms in a lattice is a simple model illustrating the difference between acoustic phonons, revealed by BLS, and optical phonons, probed by IR absorption and Raman scattering (Figure 1). Acoustic phonons are in-phase movements of atoms in the chain with a displacement along the direction of propagation (longitudinal acoustic phonons) or perpendicular to the propagation direction (transverse acoustic phonons), whilst optical phonons are out-of-phase movements of the atoms producing an oscillating electrical dipole moment (longitudinal or transverse modes).
BLS spectroscopy has been used in analytical science since the 1920s; however, only since the 1980s have high contrast measurements been possible through the use of the tandem multipass Fabry-Perot spectrometer. Since then, an increasing number of advances in BLS for analytical applications in condensed matter (where the photon-phonon interaction is exploited)2-4 and magnetic materials (through the photon-magnon interaction)5 has been brought about. Seminal works on biomedical applications6-8 have paved the route to the development of various approaches, including the one applied here and the one described previously9 using a reflective substrate in a platelet-like configuration to achieve the full description of the elasticity tensor of a sample.
In the present work, we apply BLS spectroscopy to the fundamental constituents of the extracellular matrix in connective tissues, the fibrous proteins elastin and type I-collagen. Type I collagen is a rigid, triple helical molecule which assembles laterally and longitudinally with extensive cross linking to form essentially rigid fibers in tissues such as tendons. Networks of collagen often co-exist with networks of elastin, a protein which, unusually, generates long range elasticity through a combination of entropy and hydrophobic interactions with its environment and is essential to the functions of tissues such as lung and skin. Both fibers are modeled using a hexagonal crystal model in the current research.9 In part 1, we describe the protocol to extract the fibers from animal tissues and to prepare the sample for the spectroscopic measurements. In part 2, the procedure for setting up the Brillouin apparatus and acquiring spectra from the fibers is presented. Part 3 gives details of data analysis applied to the Brillouin spectra to extract the relevant mechanical information contained therein. Then, representative results are presented and discussed.

<table border="0" cellpadding="0" cellspacing="0" width="762">
	<tbody>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Chondroitinase ABC</td>
			<td style="width:119px;">Sigma-Aldrich</td>
			<td style="width:151px;">C2905</td>
			<td style="width:291px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Tris Buffer</td>
			<td style="width:119px;">Fluka</td>
			<td style="width:151px;">93358</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Sodium Acetate</td>
			<td style="width:119px;">Fisher Scientific</td>
			<td>S608-500</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">PBS</td>
			<td style="width:119px;">Sigma-Aldrich</td>
			<td>P4417</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Sodium Azide</td>
			<td style="width:119px;">Fisher Scientific</td>
			<td>S2002</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Streptomyces Hyaluronidase&#160;</td>
			<td style="width:119px;">Sigma-Aldrich</td>
			<td>H1136-1AMP</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Sodium Chloride</td>
			<td style="width:119px;">Fisher Scientific</td>
			<td>S7653</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Trypsin</td>
			<td style="width:119px;">Sigma-Aldrich</td>
			<td style="width:151px;">T4665</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Sodium Phosphate</td>
			<td style="width:119px;">Sigma-Aldrich</td>
			<td style="width:151px;">S9638</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Sodium Hydroxide</td>
			<td style="width:119px;">Fisher Scientific</td>
			<td>S320-500</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Pure Water</td>
			<td style="width:119px;">Millipore</td>
			<td>ZRQS0P3WW</td>
			<td>Produced In-House&#160;</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:204px;">Distilled Water</td>
			<td style="width:119px;">Bibby Scientific Limited</td>
			<td style="width:151px;">D4000</td>
			<td>Produced In-House from water still</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Euthatal</td>
			<td style="width:119px;">Merial&#160;</td>
			<td style="width:151px;">J01601A&#160;</td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:204px;">Tandem Interferometer TFP-1</td>
			<td style="width:119px;">JRS Scientific Instruments</td>
			<td style="width:151px;"></td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Freezer</td>
			<td style="width:119px;">Lec</td>
			<td style="width:151px;">TU55144</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Refrigerator</td>
			<td style="width:119px;">Zanussi</td>
			<td style="width:151px;">ZBA15021SA</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Hot Plate</td>
			<td style="width:119px;">Fisher Scientific</td>
			<td>SP88857206</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Clamps</td>
			<td style="width:119px;">VWR</td>
			<td>241-7311 &#38; 241-7201</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Clamp Stand</td>
			<td style="width:119px;">VWR</td>
			<td>&#160;241-0093</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Thermometer</td>
			<td style="width:119px;">Fisher Scientific</td>
			<td>13-201-401</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Cling Film</td>
			<td style="width:119px;">Sainsbury&#39;s</td>
			<td>7650540</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Parafilm</td>
			<td style="width:119px;">Sigma-Aldrich</td>
			<td>P7793-1EA</td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:204px;">Silicone</td>
			<td style="width:119px;">IDB Technologies</td>
			<td>N/A</td>
			<td>No catalogue number. Order upon request</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Cover Glass</td>
			<td style="width:119px;">VWR</td>
			<td>631-1571</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Conical Flask</td>
			<td style="width:119px;">VWR</td>
			<td>214-1175</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Beaker</td>
			<td style="width:119px;">VWR</td>
			<td>213-0469</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Measuring Cylinder</td>
			<td style="width:119px;">VWR</td>
			<td>612-3838</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Vial</td>
			<td style="width:119px;">VWR</td>
			<td>548-0051 &#38; 548-0863</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Petri Dish</td>
			<td style="width:119px;">VWR</td>
			<td>391-0441</td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:204px;">Scalpel</td>
			<td style="width:119px;">Swann Morton Ltd</td>
			<td>&#160;0914 &#38; 0308</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Diamond Scribe</td>
			<td style="width:119px;">RS Instruments</td>
			<td>394-217</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Soldering Iron</td>
			<td style="width:119px;">RS Instruments</td>
			<td>231-5332</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Fine Forceps</td>
			<td style="width:119px;">VWR</td>
			<td style="width:151px;">232-0188</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:204px;">Double Micro-Spatula</td>
			<td style="width:119px;">VWR</td>
			<td>Various Sizes</td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:204px;">pH Meter</td>
			<td style="width:119px;">Hanna Instruments</td>
			<td style="width:151px;">HI-2210-02</td>
			<td></td>
		</tr>
		<tr height="22">
			<td height="22" style="height:22px;width:204px;">Orbital Shaker</td>
			<td style="width:119px;">IKA</td>
			<td style="width:151px;">&#160;0002819000</td>
			<td></td>
		</tr>
	</tbody>
</table>

preparation of extracellular matrix protein fibers for brillouin spectroscopy

Brillouin spectroscopy is an emerging technique in the biomedical field. It probes the mechanical properties of a sample through the interaction of visible light with thermally induced acoustic waves or phonons propagating at a speed of a few km/sec. Information on the elasticity and structure of the material is obtained in a nondestructive contactless manner, hence opening the way to in vivo applications and potential diagnosis of pathology. This work describes the application of Brillouin spectroscopy to the study of biomechanics in elastin and trypsin-digested type I collagen fibers of the extracellular matrix. Fibrous proteins of the extracellular matrix are the building blocks of biological tissues and investigating their mechanical and physical behavior is key to establishing structure-function relationships in normal tissues and the changes which occur in disease. The procedures of sample preparation followed by measurement of Brillouin spectra using a reflective substrate are presented together with details of the optical system and methods of spectral data analysis.

The Brillouin spectroscopy apparatus used in this experiment (Figure SI-1A) has been previously described.9 It employs a single-mode 532 nm solid-state laser with 76 mW output power at the sample. A 20 cm achromatic lens focuses the laser light onto the sample and collects the scattered light from the sample in a backscattering geometry. A tandem multipass Fabry-Perot interferometer is used for filtering the scattered light, which is then detected by a low-noise photodiode detector. This approach gives extremely high contrast (ca. 120 dB) and stability through self-aligning piezo-scanning of the etalons. A polarizer and analyzer are introduced to select the polarization of the incident and scattered light. Spectra are usually obtained with the polarizer kept fixed selecting the vertical (V) direction of the incident light polarization and the analyzer selecting alternatively the vertical (V) or horizontal (H) direction of the scattered light polarization. In this configuration, longitudinal and transverse acoustic modes are detected respectively.
A typical Brillouin spectrum has an intense central peak due to elastic scattering and one or more sets of equally shifted peaks, or Brillouin doublets, which are the signature of the mechanics of the sample. In these measurements, the scattered light can originate both from bulk phonons travelling quasi-orthogonal to the sample and, after reflection of the incident light at the sample-substrate interface, from bulk phonons travelling parallel to the surface (PS modes).9
Figure 2 shows BLS spectra of dry and hydrated trypsin-digested collagen fibers obtained with VV polarization at 0.2 GHz resolution, with a 30 GHz free spectral range and approximately 10 min collection time per spectrum. Each spectrum corresponds to a specific angle of rotation,&#160;&#952; (Figure SI-1C). In dry collagen fiber at&#160;&#952; = 0&#176;, longitudinal modes give rise to a bulk peak at (18.92 &#177; 0.02) GHz whilst the PS mode is at (9.85 &#177; 0.03) GHz (Figure 2A). The PS peak shifts to lower frequencies as &#952; goes from 0&#176; (phonon probing the axial orientation of the fiber) to 90&#176; (phonon probing the radial orientation), whereas the bulk peak only slightly red-shifts upon changing&#160;&#952; in the same range (phonon probing a quasi-radial direction throughout the rotation). In wet collagen fiber, the two peaks due to longitudinal phonons are essentially unchanged throughout the experiment, with the bulk peak at ca. 10.5 GHz and the PS peak at 4.9 GHz (Figure 2B). This indicates an 80 to 100% reduction in peak frequency (relative to the data of 18.92 and 9.85 GHz, respectively), and hence of stiffness of the material, due to hydration. Note that the bulk and PS modes of hydrated collagen lie close in frequency to the modes of pure water, suggesting that its elastic constants are a combination of the water and fiber contributions, with a dominant role played by water.
Figure 3 shows a spectrum of dry trypsin-digested collagen fiber measured at&#160;&#952; = 30&#176; with VH polarization; a leakage of the VV polarization enables the PS and bulk peaks to still be observed. Transverse modes account for a peak at (4.1 &#177; 0.2) GHz (&#952; = 0&#176;) which slightly blue-shifts as&#160;&#952; changes from 0&#176; to 90&#176;. Fit results for both the transverse and PS peaks are also shown. Peak parameters were extracted and acoustic wave velocities were derived as VL = v&#955;/&#8730;2, where&#160;v is the frequency of the mode obtained by curve-fit analysis of the peaks and&#160;&#955; is the excitation wavelength, 532 nm. Note that in this geometry, knowledge of the refractive index of the material is not required to obtain the acoustic mode velocity (owing to the scattering geometry, qs = 2ki sin(&#934;); Figure SI-1b,c), hence making this approach especially advantageous.
Figure 4 is a plot of the acoustic wave velocities obtained from longitudinal and transverse modes (PS and T peaks) as a function of the angle&#160;&#952; . Fit analysis to a model of hexagonally symmetric elastic solid7 &#8212; Equations A1 and A2 below&#160;&#8212; provides the five components of the elasticity tensor of dry trypsin-digested type I collagen fibers (Table 1).
The longitudinal and transverse acoustic wave velocities are given by9
<img alt="Equation 1" src="/files/ftp_upload/54648/54648eq1.jpg" />, (A1)
<img alt="Equation 2" src="/files/ftp_upload/54648/54648eq2.jpg" />, (A2)
where&#160;&#961; is the density of the material, and c11, c33, c44 and c13 are four of the five elastic constants that characterize systems with a hexagonal symmetry. The fifth constant, c12, can be derived from the approximate relation c12 ~ c11 - 2c44.7
Coefficients are similar to those previously obtained from unpurified collagen fibers.9 A noticeable difference occurs for the coefficient c13 that is reflected into similar values of the elastic moduli E&#449; and E<img alt="Perpendicular" src="/files/ftp_upload/54648/54648fig_flippedT.jpg" /> (approximately 7.2 and 7.7 GPa) for the purified collagen.
Figure 5 is a plot of the longitudinal acoustic wave velocity of wet collagen versus&#160;&#952; . In this case, no periodic change in frequency is observed, giving a constant velocity within the error. Figure 6 shows the spectra of dry and hydrated elastin fibers measured at&#160;&#952; = 0&#176;. Transverse modes were not detected for these samples. In dry elastin, the bulk peak occurs at 16.8 GHz whilst the PS mode at 8.2 GHz9 (13 and 20% lower than the corresponding peaks of dry collagen). Wet elastin fibers present a bulk peak at (12.30 &#177; 0.01) GHz (37% lower in frequency than the bulk peak of dry elastin). The PS mode of wet elastin is not apparent in the spectrum because of the intense tail of the elastic peak at those frequencies. On the other hand, the peak at ca. 7.5 GHz is attributed to the bulk water.
Figure 7 shows the dependence of acoustic wave velocity in dry elastin fiber on &#952;. From these data, the elasticity tensor components (and mechanical moduli) were obtained (Table 1).9 As in wet collagen, there is evidence of isotropy in the mechanical modulus of hydrated elastin fibers. These results indicate how Brillouin spectroscopy can give relevant information on stiffness, composition and structural aspects of a material.
<img alt="Figure 1" src="/files/ftp_upload/54648/54648fig1.jpg" /> 
Figure 1. Acoustic and optical phonons in one-dimensional chain of atoms. Schematic diagram of acoustic and optical vibrations in a one-dimensional diatomic chain. Atoms have mass m1 and m2 and are alternated. Arrows indicate the displacements of the atoms. <a href="https://www.jove.com/files/ftp_upload/54648/54648fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" src="/files/ftp_upload/54648/54648fig2.jpg" /> 
Figure 2. Brillouin spectra of trypsin-purified type I collagen fibers from rat tail tendon. Spectra of (A) dry fiber and (B) hydrated fiber from VV measurements at different angle to fiber axis &#952;, in degrees. A spectrum of pure distilled water is also shown. Spectra were normalized to the intensity (height) of the bulk peak. Labels B and PS denote peaks related to bulk and parallel-to-surface modes, respectively. Error bars indicate the standard error (square root of number of counts). <a href="https://www.jove.com/files/ftp_upload/54648/54648fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" src="/files/ftp_upload/54648/54648fig3.jpg" /> 
Figure 3. Brillouin spectrum of dry trypsin-purified type I collagen fibers from rat tail tendon. Spectrum from a VH measurement at&#160;&#952; = 30&#176;. Labels T, PS and B denote peaks related to transverse, parallel-to-surface and bulk modes, respectively. Results of fit analysis using a damped harmonic oscillator (DHO) model for both T and PS modes are also shown. Error bars indicate the standard error (square root of number of counts). <a href="https://www.jove.com/files/ftp_upload/54648/54648fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" src="/files/ftp_upload/54648/54648fig4.jpg" /> 
Figure 4. Plot of the acoustic wave velocity in dry trypsin-purified collagen vs angle to fiber axis. Longitudinal and transverse acoustic wave velocities of dry collagen fiber derived from fit analysis of the Brillouin peaks. Data are fitted to a model of hexagonally symmetric elastic solid. Red line: Equation A1 (R2 = 0.99); blue line: Equation A2 (R2 = 0.36). Error bars indicate the standard errors obtained from the square root of the diagonal elements of the covariance matrix after a Levenberg-Marquardt nonlinear least squares fit of Brillouin spectra. <a href="https://www.jove.com/files/ftp_upload/54648/54648fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 5" src="/files/ftp_upload/54648/54648fig5.jpg" /> 
Figure 5. Plot of the longitudinal acoustic wave velocity in wet trypsin-purified collagen vs angle to fiber axis. Longitudinal acoustic wave velocity of hydrated collagen fiber derived from fit analysis of the Brillouin peaks. The line shown is a guide for the eye and gives the average value of the acoustic wave velocity in this range. Error bars indicate the standard errors obtained from the square root of the diagonal elements of the covariance matrix after a Levenberg-Marquardt nonlinear least squares fit of Brillouin spectra. <a href="https://www.jove.com/files/ftp_upload/54648/54648fig5large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 6" src="/files/ftp_upload/54648/54648fig6.jpg" /> 
Figure 6. Brillouin spectra of elastin fibers from bovine nuchal ligament. Spectra of dry and hydrated fiber at&#160;&#952; = 0&#176;. Spectra were normalized to the intensity (height) of the bulk peak. Labels B and PS denote peaks related to bulk and parallel-to-surface modes, respectively. BF and BW refer to the bulk peaks of the fiber and water, respectively. Error bars indicate the standard error (square root of number of counts). <a href="https://www.jove.com/files/ftp_upload/54648/54648fig6large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 7" src="/files/ftp_upload/54648/54648fig7.jpg" /> 
Figure 7. Plot of the longitudinal acoustic wave velocity in dry elastin vs angle to fiber axis. Longitudinal acoustic wave velocity of dry elastin fiber derived from fit analysis of the Brillouin peaks. Data are fitted to a model of hexagonally symmetric elastic solid. Red line: Equation A19 (R2 = 0.74). Error bars indicate the standard errors obtained from the square root of the diagonal elements of the covariance matrix after a Levenberg-Marquardt nonlinear least squares fit of Brillouin spectra. <a href="https://www.jove.com/files/ftp_upload/54648/54648fig7large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Supplemental Figure 1" src="/files/ftp_upload/54648/54648supfig1.jpg" />
Figure SI-1. Schematic of the Brillouin set-up and BLS scattering geometry. (A) The incident light emitted by a solid-state laser is sent to the sample through an achromatic lens. The light scattered by bulk acoustic phonons and by those resulting from reflection of light at the substrate surface, which is in contact with the sample, is collected by the lens, filtered by a tandem-multipass Fabry-Perot interferometer and detected by a photomultiplier. FP1 and FP2 indicate the two interferometers constituting the tandem set-up. A polarizer selects the polarization of incident light, and an analyzer is used to select the polarization of scattered light. (B) BLS geometry with a specimen in contact with the surface of a reflective silicon substrate. A glass slide (not shown) is placed above the specimen to seal the compartment, and gentle pressure is applied through pads at the corners of the substrate. The incident light (ki) passes through the lens, is refracted at the air-sample interface (k&#39;i) and focused at the sample-substrate interface. The scattered light collected by the same lens (k&#39;s) results from interaction with both bulk phonons (qb) and those travelling PS of the sample (qs). Angles between the directions of light and the normal to the surface are indicated as&#160;&#934; and &#934;&#39;. (C) Schematic diagram of the sample and of the adopted coordinate system; z defines the extraordinary axis parallel to the direction of the fibres. Angles&#160;&#952; and &#945; are those between the direction of phonons qs and qb to the z-axis, respectively. ki, k&#39;i, ks, k&#39;s: wavenumbers of the incident and scattered light; qb, qs, wave vectors of the bulk and PS modes, respectively. (Reprinted from ref 9.) <a href="https://www.jove.com/files/ftp_upload/54648/54648supfig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
Table 1. Elastic tensor coefficients derived from fit analysis of the acoustic wave velocities. Elastic tensor coefficients of dry trypsin-purified type I collagen fibers (this work) and elastin fibers (ref 9).
<table border="1" fo:keep-together.within-page="1">
	<tbody>
		<tr>
			<td>sample</td>
			<td colspan="2">elastic coefficients (GPa)</td>
		</tr>
		<tr>
			<td>trypsin-digested collagen</td>
			<td>c33</td>
			<td>18.7 &#177; 0.1</td>
		</tr>
		<tr>
			<td></td>
			<td>c11</td>
			<td>14.4 &#177; 0.2</td>
		</tr>
		<tr>
			<td></td>
			<td>c44</td>
			<td>3.4 &#177; 0.1</td>
		</tr>
		<tr>
			<td></td>
			<td>c12</td>
			<td>7.2 &#177; 0.2</td>
		</tr>
		<tr>
			<td></td>
			<td>c13</td>
			<td>11.2 &#177; 0.3</td>
		</tr>
		<tr>
			<td>elastin</td>
			<td>c33</td>
			<td>11.5 &#177; 0.2</td>
		</tr>
		<tr>
			<td></td>
			<td>c11</td>
			<td>10.4 &#177; 0.1</td>
		</tr>
		<tr>
			<td></td>
			<td>c44</td>
			<td>1.9 &#177; 0.2</td>
		</tr>
		<tr>
			<td></td>
			<td>c12</td>
			<td>6.6 &#177; 0.2</td>
		</tr>
		<tr>
			<td></td>
			<td>c13</td>
			<td>6.8 &#177; 0.3</td>
		</tr>
	</tbody>
</table>

Watch this Scientific Journal Video about Preparation of Extracellular Matrix Protein Fibers for Brillouin Spectroscopy at JoVE.com

Preparation of Extracellular Matrix Protein Fibers for Brillouin Spectroscopy

We present a protocol for the application of Brillouin light scattering spectroscopy to elastin and trypsin-purified type I collagen fibers of the extracellular matrix to extract their full elastic properties.

Brillouin spectroscopy is an emerging technique in the biomedical field. It probes the mechanical properties of a sample through the interaction of ...

preparation-extracellular-matrix-protein-fibers-for-brillouin

Research

JoVE Journal

Bioengineering

10.3K Views.  University of Exeter. We present a protocol for the application of Brillouin light scattering spectroscopy to elastin and trypsin-purified type I collagen fibers of the extracellular matrix to extract their full elastic properties.

Video: Preparation of Extracellular Matrix Protein Fibers for Brillouin Spectroscopy

Non-contact, Label-free Monitoring of Cells and Extracellular Matrix using Raman Spectroscopy

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, currently available routine methods require processing steps and alter sample integrity. Raman spectroscopy is a fast method that enables the measurement of biological samples without the need for further processing steps. This laser-based technology detects the inelastic scattering of monochromatic light.6 As every chemical vibration is assigned to a specific Raman band (wavenumber in cm-1), each biological sample features a typical spectral pattern due to their inherent biochemical composition.7-9 Within Raman spectra, the peak intensities correlate with the amount of the present molecular bonds.1 Similarities and differences of the spectral data sets can be detected by employing a multivariate analysis (e.g. principal component analysis (PCA)).10
Here, we perform Raman spectroscopy of living cells and native tissues. Cells are either seeded on glass bottom dishes or kept in suspension under normal cell culture conditions (37 &deg;C, 5% CO2) before measurement. Native tissues are dissected and stored in phosphate buffered saline (PBS) at 4 &deg;C prior measurements. Depending on our experimental set up, we then either focused on the cell nucleus or extracellular matrix (ECM) proteins such as elastin and collagen. For all studies, a minimum of 30 cells or 30 random points of interest within the ECM are measured. Data processing steps included background subtraction and normalization.

Raman spectroscopy is a suitable technique for the non-contact, label-free analysis of living cells, tissue-engineered constructs and native tissues. Source-specific spectral fingerprints can be generated and analyzed using multivariate analysis.

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, ...

Preparation of Light-responsive Membranes by a Combined Surface Grafting and Postmodification Process

In order to modify the surface tension of commercial available track-edged polymer membranes, a procedure of surface-initiated polymerization is presented. The polymerization from the membrane surface is induced by plasma treatment of the membrane, followed by reacting the membrane surface with a methanolic solution of 2-hydroxyethyl methacrylate (HEMA). Special attention is given to the process parameters for the plasma treatment prior to the polymerization on the surface. For example, the influence of the plasma-treatment on different types of membranes (e.g.&#160;polyester, polycarbonate, polyvinylidene fluoride) is studied. Furthermore, the time-dependent stability of the surface-grafted membranes is shown by contact angle measurements. When grafting poly(2-hydroxyethyl methacrylate) (PHEMA) in this way, the surface can be further modified by esterification of the alcohol moiety of the polymer with a carboxylic acid function of the desired substance. These reactions can therefore be used for the functionalization of the membrane surface. For example, the surface tension of the membrane can be changed or a desired functionality as the presented light-responsiveness can be inserted. This is demonstrated by reacting PHEMA with a carboxylic acid functionalized spirobenzopyran unit which leads to a light-responsive membrane. The choice of solvent plays a major role in the postmodification step and is discussed in more detail in this paper. The permeability measurements of such functionalized membranes are performed using a Franz cell with an external light source. By changing the wavelength of the light from the visible to the UV-range, a change of permeability of aqueous caffeine solutions is observed.

A plasma-induced polymerization procedure is described for the surface-initiated polymerization on polymer membranes. Further postmodification of the grafted polymer with photochromic substances is presented with a protocol of conducting permeability measurements of light-responsive membranes.

In order to modify the surface tension of commercial available track-edged polymer membranes, a procedure of surface-initiated polymerization is ...

Epithelial Cell Repopulation and Preparation of Rodent Extracellular Matrix Scaffolds for Renal Tissue Development

This protocol details the generation of acellular, yet biofunctional, renal extracellular matrix (ECM) scaffolds that are useful as small-scale model substrates for organ-scale tissue development. Sprague Dawley rat kidneys are cannulated by inserting a catheter into the renal artery and perfused with a series of low-concentration detergents (Triton X-100 and sodium dodecyl sulfate (SDS)) over 26 hr to derive intact, whole-kidney scaffolds with intact perfusable vasculature, glomeruli, and renal tubules. Following decellularization, the renal scaffold is placed inside a custom-designed perfusion bioreactor vessel, and the catheterized renal artery is connected to a perfusion circuit consisting of: a peristaltic pump; tubing; and optional probes for pH, dissolved oxygen, and pressure. After sterilizing the scaffold with peracetic acid and ethanol, and balancing the pH (7.4), the kidney scaffold is prepared for seeding via perfusion of culture medium within a large-capacity incubator maintained at 37 &#176;C and 5% CO2. Forty million renal cortical tubular epithelial (RCTE) cells are injected through the renal artery, and rapidly perfused through the scaffold under high flow (25 ml/min) and pressure (~230 mmHg) for 15 min before reducing the flow to a physiological rate (4 ml/min). RCTE cells primarily populate the tubular ECM niche within the renal cortex, proliferate, and form tubular epithelial structures over seven days of perfusion culture. A 44 &#181;M resazurin solution in culture medium is perfused through the kidney for 1 hr during medium exchanges to provide a fluorometric, redox-based metabolic assessment of cell viability and proliferation during tubulogenesis. The kidney perfusion bioreactor permits non-invasive sampling of medium for biochemical assessment, and multiple inlet ports allow alternative retrograde seeding through the renal vein or ureter. These protocols can be used to recellularize kidney scaffolds with a variety of cell types, including vascular endothelial, tubular epithelial, and stromal fibroblasts, for rapid evaluation within this system.

This protocol describes decellularization of Sprague Dawley rat kidneys by antegrade perfusion of detergents through the vasculature, producing acellular renal extracellular matrices that serve as templates for repopulation with human renal epithelial cells. Recellularization and use of the resazurin perfusion assay to monitor growth is performed within specially-designed perfusion bioreactors.

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High Speed Sub-GHz Spectrometer for Brillouin Scattering Analysis

The goal of this protocol is to build a parallel high-extinction and high-resolution optical Brillouin spectrometer. Brillouin spectroscopy is a non-contact measurement method that can be used to obtain direct readouts of viscoelastic material properties. It has been a useful tool in material characterization, structural monitoring and environmental sensing. In the past, Brillouin spectroscopy has usually employed scanning Fabry-Perot etalons to perform spectral analysis. This process requires high illumination power and long acquisition times, making the technique unsuitable for biomedical applications. A recently introduced novel spectrometer overcomes this challenge by employing two VIPAs in a cross-axis configuration. This innovation enables sub-Gigahertz (GHz) resolution spectral analysis with sub-second acquisition time and illumination power within the safety limits of biological tissue. The multiple new applications facilitated by this improvement are currently being explored in biological research and clinical application.

Here we present a protocol to build a rapid Brillouin spectrometer. Cascading virtually imaged phase array (VIPA) etalons achieve a measurement speed more than 1,000 times faster than traditional scanning Fabry-Perot spectrometers. This improvement provides the means for Brillouin analysis of tissue and biomaterials at low power levels in vivo.

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Engineering Three-dimensional Epithelial Tissues Embedded within Extracellular Matrix

The architecture of branched organs such as the lungs, kidneys, and mammary glands arises through the developmental process of branching morphogenesis, which is regulated by a variety of soluble and physical signals in the microenvironment. Described here is a method created to study the process of branching morphogenesis by forming engineered three-dimensional (3D) epithelial tissues of defined shape and size that are completely embedded within an extracellular matrix (ECM). This method enables the formation of arrays of identical tissues and enables the control of a variety of environmental factors, including tissue geometry, spacing, and ECM composition. This method can also be combined with widely used techniques such as traction force microscopy (TFM) to gain more information about the interactions between cells and their surrounding ECM. The protocol can be used to investigate a variety of cell and tissue processes beyond branching morphogenesis, including cancer invasion.

This manuscript describes a soft lithography-based technique to engineer uniform arrays of three-dimensional (3D) epithelial tissues of defined geometry surrounded by extracellular matrix. This method is amenable to a wide variety of cell types and experimental contexts and allows for high-throughput screening of identical replicates.

The architecture of branched organs such as the lungs, kidneys, and mammary glands arises through the developmental process of branching morphogenesis, ...

Tunable Hydrogels from Pulmonary Extracellular Matrix for 3D Cell Culture

Here we present a method for establishing multiple component cell culture hydrogels for in vitro lung cell culture. Beginning with healthy en bloc lung tissue from porcine, rat, or mouse, the tissue is perfused and submerged in subsequent chemical detergents to remove the cellular debris. Histological comparison of the tissue before and after processing confirms removal of over 95% of double stranded DNA and alpha galactosidase staining suggests the majority of cellular debris is removed. After decellularization, the tissue is lyophilized and then cryomilled into a powder. The matrix powder is digested for 48 hr in an acidic pepsin digestion solution and then neutralized to form the pregel solution. Gelation of the pregel solution can be induced by incubation at 37 &#176;C and can be used immediately following neutralization or stored at 4 &#176;C for up to two weeks. Coatings can be formed using the pregel solution on a non-treated plate for cell attachment. Cells can be suspended in the pregel prior to self-assembly to achieve a 3D culture, plated on the surface of a formed gel from which the cells can migrate through the scaffold, or plated on the coatings. Alterations to the strategy presented can impact gelation temperature, strength, or protein fragment sizes. Beyond hydrogel formation, the hydrogel stiffness may be increased using genipin.

This is a method to create a 3-dimensional cell culture scaffold from pulmonary extracellular matrix. Intact lung is processed into hydrogels that can support the growth of cells in three-dimensions.

Here we present a method for establishing multiple component cell culture hydrogels for in vitro lung cell culture. Beginning with healthy en bloc lung ...

Fabricating a Kidney Cortex Extracellular Matrix-Derived Hydrogel

Extracellular matrix (ECM) provides important biophysical and biochemical cues to maintain tissue homeostasis. Current synthetic hydrogels offer robust mechanical support for in vitro cell culture but lack the necessary protein and ligand composition to elicit physiological behavior from cells. This manuscript describes a fabrication method for a kidney cortex ECM-derived hydrogel with proper mechanical robustness and supportive biochemical composition. The hydrogel is fabricated by mechanically homogenizing and solubilizing decellularized human kidney cortex ECM. The matrix preserves native kidney cortex ECM protein ratios while also enabling gelation to physiological mechanical stiffnesses. The hydrogel serves as a substrate upon which kidney cortex-derived cells can be maintained under physiological conditions. Furthermore, the hydrogel composition can be manipulated to model a diseased environment which enables the future study of kidney diseases.

Here we present a protocol to fabricate a kidney cortex extracellular matrix-derived hydrogel to retain the native kidney extracellular matrix (ECM) structural and biochemical composition. The fabrication process and its applications are described. Finally, a perspective on using this hydrogel to support kidney-specific cellular and tissue regeneration and bioengineering is discussed.

Extracellular matrix (ECM) provides important biophysical and biochemical cues to maintain tissue homeostasis. Current synthetic hydrogels offer robust ...

Production of Extracellular Matrix Fibers via Sacrificial Hollow Fiber Membrane Cell Culture

Engineered scaffolds derived from extracellular matrix (ECM) have driven significant interest in medicine for their potential in expediting wound closure and healing. Extraction of extracellular matrix from fibrogenic cell cultures in vitro has potential for generation of ECM from human- and potentially patient-specific cell lines, minimizing the presence of xenogeneic epitopes which has hindered the clinical success of some existing ECM products. A significant challenge in in vitro production of ECM suitable for implantation is that ECM production by cell culture is typically of relatively low yield. In this work, protocols are described for the production of ECM by cells cultured within sacrificial hollow fiber membrane scaffolds. Hollow fiber membranes are cultured with fibroblast cell lines in a conventional cell medium and dissolved after cell culture to yield continuous threads of ECM. The resulting ECM fibers produced by this method can be decellularized and lyophilized, rendering it suitable for storage and implantation.

The goal of this protocol is production of whole extracellular matrix fibers targeted for wound repair which are suitable for preclinical evaluation as part of a regenerative scaffold implant. These fibers are produced by the culture of fibroblasts on hollow fiber membranes and extracted by dissolution of the membranes.

Engineered scaffolds derived from extracellular matrix (ECM) have driven significant interest in medicine for their potential in expediting wound closure ...

Pancreatic Tissue-Derived Extracellular Matrix Bioink for Printing 3D Cell-Laden Pancreatic Tissue Constructs

The transplantation of pancreatic islets is a promising treatment for patients who suffer from type 1 diabetes accompanied by hypoglycemia and secondary complications. However, islet transplantation still has several limitations such as the low viability of transplanted islets due to poor islet engraftment and hostile environments. In addition, the insulin-producing cells differentiated from human pluripotent stem cells have limited ability to secrete sufficient hormones that can regulate the blood glucose level; therefore, improving the maturation by culturing cells with proper microenvironmental cues is strongly required. In this article, we elucidate protocols for preparing a pancreatic tissue-derived decellularized extracellular matrix (pdECM) bioink to provide a beneficial microenvironment that can increase glucose sensitivity of pancreatic islets, followed by describing the processes for generating 3D pancreatic tissue constructs using a microextrusion-based bioprinting technique.

Decellularized extracellular matrix (dECM) can provide suitable microenvironmental cues to recapitulate the inherent functions of target tissues in an engineered construct. This article elucidates the protocols for the decellularization of pancreatic tissue, evaluation of pancreatic tissue-derived dECM bioink, and generation of 3D pancreatic tissue constructs using a bioprinting technique.

The transplantation of pancreatic islets is a promising treatment for patients who suffer from type 1 diabetes accompanied by hypoglycemia and secondary ...

A Human 3D Extracellular Matrix-Adipocyte Culture Model for Studying Matrix-Cell Metabolic Crosstalk

The extracellular matrix (ECM) plays a central role in regulating tissue homeostasis, engaging in crosstalk with cells and regulating multiple aspects of cellular function. The ECM plays a particularly important role in adipose tissue function in obesity, and alterations in adipose tissue ECM deposition and composition are associated with metabolic disease in mice and humans. Tractable in vitro models that permit dissection of the roles of the ECM and cells in contributing to global tissue phenotype are sparse. We describe a novel 3D in vitro model of human ECM-adipocyte culture that permits study of the specific roles of the ECM and adipocytes in regulating adipose tissue metabolic phenotype. Human adipose tissue is decellularized to isolate ECM, which is subsequently repopulated with preadipocytes that are then differentiated within the ECM into mature adipocytes. This method creates ECM-adipocyte constructs that are metabolically active and retain characteristics of the tissues and patients from which they are derived. We have used this system to demonstrate disease-specific ECM-adipocyte crosstalk in human adipose tissue. This culture model provides a tool for dissecting the roles of the ECM and adipocytes in contributing to global adipose tissue metabolic phenotype and permits study of the role of the ECM in regulating adipose tissue homeostasis.

We describe a 3D human extracellular matrix-adipocyte in vitro culture system that permits dissection of the roles of the matrix and adipocytes in contributing to adipose tissue metabolic phenotype.

The extracellular matrix (ECM) plays a central role in regulating tissue homeostasis, engaging in crosstalk with cells and regulating multiple aspects of ...