A new force-clamp rheometry technique is used to investigate the mechanical properties of low-volume protein-based hydrogel samples tethered between a voice-coil motor and a force sensor. An analog proportional-integral-derivative (PID) system allows for the 'clamping' of the force experienced to the desired protocol.
Here, we describe a force-clamp rheometry method to characterize the biomechanical properties of protein-based hydrogels. This method uses an analog proportional-integral-derivative (PID) system to apply controlled-force protocols on cylindrical protein-based hydrogel samples, which are tethered between a linear voice-coil motor and a force transducer. During operation, the PID system adjusts the extension of the hydrogel sample to follow a predefined force protocol by minimizing the difference between the measured and set-point forces. This unique approach to protein-based hydrogels enables the tethering of extremely low-volume hydrogel samples (< 5 µL) with different protein concentrations. Under force-ramp protocols, where the applied stress increases and decreases linearly with time, the system enables the study of the elasticity and hysteresis behaviors associated with the (un)folding of proteins and the measurement of standard elastic and viscoelastic parameters. Under constant-force, where the force pulse has a step-like shape, the elastic response, due to the change in force, is decoupled from the viscoelastic response, which comes from protein domain unfolding and refolding. Due to its low-volume sample and versatility in applying various mechanical perturbations, force-clamp rheometry is optimized to investigate the mechanical response of proteins under force using a bulk approach.
Apart from having unique physical properties, protein-based hydrogels hold the promise of revolutionizing force spectroscopy by enabling the measurement of several billion molecules in one 'pull', thus enabling the study of proteins in crowded environments, similar to those encountered in skin and other tissues. Protein domains remain folded inside hydrogels, allowing the study of their biomechanical response to force, binding partners, and chemical conditions. Additionally, the biomechanical response of protein domains inside hydrogels resembles the response seen with single-molecule force spectroscopy techniques. For example, chemical denaturants and oxidizing agents decrease the stability of the folded state, both at the single protein domain level1,2,3 and at the macroscopic level4,5,6,7. Similarly, osmolytes increase the stability of single proteins8,9, leading to a decrease in the viscoelastic response of hydrogels, for the same force conditions7,10.
Several approaches have been implemented to synthesize protein-based hydrogels, by either using physical interactions11,12 or covalent cross-linking4,13. Covalent reactions allow for fixed cross-linking locations and these hydrogels can recover the initial state upon a removal of the mechanical or chemical perturbations. A successful approach for covalent cross-linking relies on forming covalent carbon-carbon bonds between exposed tyrosine amino acids using ammonium persulfate (APS) as an oxidant and a ruthenium (II) salt as an initiator (Figure 1)14. Upon exposure to white light, a solution of concentrated proteins can be turned into a hydrogel. By controlling when the reaction starts, the protein-APS mix can be injected into any casting form, such as polytetrafluoroethylene (PFTE) tubes (Figure 1B and 1C), allowing the use of an extremely small solution volume15. Furthermore, the use of white light to trigger the cross-linking reaction results in a limited bleaching of fluorescent proteins and allows the formulation of composite hydrogels with fluorescent markers (Figure 1). Other protein-based hydrogel formation methods use cross-linking based on the SpyTag-SpyCatcher covalent interaction16, amine cross-linking via glutaraldehyde13, or biotin-streptavidin interactions17.
Dynamic mechanical analysis (DMA) is currently a technique extensively used to study polymer-based hydrogels13,18. While DMA can apply constant force protocols to biomaterials, it requires Young's moduli over 10 kPa, and large sample volumes of more than 200 µL19. Due to these limitations, protein hydrogels are generally too soft to be investigated by this technique. As engineered polyproteins are harder to synthesize than polymers, since they require a living system to produce, such high volumes are inefficient, at best4,15. Furthermore, most biological tissues are softer than 10 kPa. Several approaches were developed for biological samples, especially in the study of muscle elasticity20,21. These techniques can also operate under feedback to apply constant force but are optimized for samples with small diameters (in the micron range) exposed to force for very short times (typically less than 1 s).
Protein-based hydrogels were successfully studied with modified rheometry techniques. For example, casting the hydrogel in a ring shape allows the use of extensional rheometry to measure the change in the experienced force as a function of extension4,22. Other approaches for studying the rheological properties of protein-based hydrogels use controlled shear-stress rheometry. These techniques can also achieve low sample volume and tolerate soft materials. However, these methods lack the ability to mimic the pulling forces that cause protein unfolding in vivo, and Young's modulus is calculated based on complex theories that require various assumptions and corrections23.
We have recently reported a new approach that utilizes a small volume of proteins, polymerized inside tubes with diameters < 1 mm. Our first implementation of this technique was operating in length-clamp mode, where the gel was extended following the desired protocol15. In this method, the proteins experience a continuous change in both extension and force while the domains unfold, making the data interpretation cumbersome. Recently, we have reported a new force-clamp rheometry technique, where a feedback loop can expose low-volume protein hydrogels to a predefined force protocol7 (Figure 2). An analog PID system compares the force measured by the force sensor with the set point sent from the computer and adjusts the gel extension by moving the voice coil to minimize the difference between the two inputs. This 'clamping' of the force now allows for new types of experiments to measure the biomechanics of protein hydrogels.
In the force-ramp mode, a tethered protein hydrogel experiences a constant increase and decrease of force with time. The PID compensates for any viscoelastic deformation by changing the extension in a non-linear way, depending on the type of protein and hydrogel formulation. The main advantage of force ramp is that it allows the quantification of standard parameters, such as Young's modulus and energy dissipation, due to an unfolding and refolding of protein domains.
In constant-force mode, the applied force changes in a step-like fashion. In this mode, the gel extends and contracts elastically when the force is increased or decreased, respectively, followed by a time-dependent deformation. This viscoelastic deformation, taking place while the gel experiences a constant force, is directly related to domain unfolding/refolding. In a simplified way, this extension can be seen as the equivalent of several billion single molecule traces averaged together and measured all at once. Constant-force protocols can be used to study the creep and relaxation of protein hydrogels as a function of force and time. As a function of force, for BSA-based protein hydrogels, we have recently shown that there is a linear dependency between the elastic and viscoelastic extension and recoil with the applied strain7.
Here we detail the operation of a force-clamp rheometer using composite gels made from a mixture of protein L (8 domains24, depicted as L8) and a protein L-eGFP construct (L-eGFP), which makes the overall hydrogel fluorescent and easy to demonstrate.
1. Reagents Solution Preparation
2. Protein-based Hydrogel Synthesis
3. Protein-based Hydrogel Attachment and Force-Clamp Rheometer Set-up
4. Protein-based Hydrogel Characterization using Controlled Force-Ramp and Constant-Force Measurements
5. Data Analysis
Figure 1A shows the scheme of the photoactive reaction used to synthesize the L-EGP/L8 hydrogel. Figure 1B shows the hydrogel mixture in the PTFE tube before and after the photoactivation. Figure 1C presents the extruded L-eGFP-L8 hydrogel inside a Tris solution. The hydrogel sample has no structural defects such as notches. Hydrogels with clearly visible damage should be discarded.
The rendering of the assembled and exploded views of the force-clamp rheometer are presented in Figure 2A and 2B. Figure 2C shows the force-clamp rheometer scheme, where the hydrogel sample is tethered between the hooks connected to the linear voice-coil and the force sensor and immersed in a buffer solution. The analog PID system adjusts the hydrogel extension by controlling the linear-voice coil position to follow the force set point. Figure 2D shows the tuning of the PID using various increments for the integral gain.
Figure 3 shows a typical attachment process of a hydrogel sample. After tethering the hydrogel between the aligned hooks, the suture loops are tightened around the hydrogel near the bends to prevent the sample from slipping and to allow for the precise determination of the hydrogel length.
Force-ramp Measurement and Analysis of Protein-based Hydrogels:
Representative measurements of the force-ramp protocol are shown in Figure 4A – 4C. Each new pull starts with a slack measurement, as shown in Figure 4A. Then, the force curve is obtained by applying an inverted "V" protocol as the load increases and decreases linearly with time. Afterward, the hydrogel is held at a 0 mN force for 200 s, to allow the protein domains inside the hydrogel sample to refold (Figure 4B). During stress, the PID system modifies the hydrogel extension represented by the coil position to follow the predefined force set point. For each slack curve, we fit 2 lines (Figure 4C). The blue line is used to fit the first regime when the hydrogel recoils and the orange line is used to fit the regime when the hydrogel becomes slack. The intersection between the two lines is used to calculate the true gel length with a micrometer resolution (Figure 4A). Afterward, the extension of the hydrogel sample is calculated by subtracting the initial coil position from the coil position trace (Figure 4D). Figure 4F presents the stress-strain curve. The stress is calculated by dividing the applied force by the cross-sectional area of the hydrogel sample and the strain is calculated by dividing the extension (Figure 4E) by the true gel length calculated from the slack curve as presented in Figure 4A.
Constant-force Measurement and Analysis of Protein-based Hydrogels:
Representative measurements of a constant-force protocol are shown in Figure 5A – 5D. A constant force of 0.1 mN is applied to the hydrogel sample for 30 s, the force is then changed to 1 mN for 120 s, and finally, the force is quenched back to 0.1 mN for 300 s to allow the protein domains to refold (Figure 5A). During the first 30 s at low force, there is no notable change in the gel extension. When increasing the force to 1 mN, the hydrogel shows a fast elastic extension. Following this initial extension, the hydrogel keeps extending over time, while keeping the force constant (1 mN). Afterward, the force is quenched back to the initial low value (0.1 mN) and the hydrogel recovers to its initial length (Figure 5B). The extension of the hydrogel sample (Figure 5C) and the force are used to calculate the strain (top) and stress (bottom) in a similar fashion as in the force ramp measurements (Figure 5D).
Figure 1: L-eGFP/(L)8-based hydrogel synthesis. (A) This panel shows the schematics of an L-eGFP/(L)8 protein hydrogel synthesis using a photoactivated reaction. The protein is mixed with APS and [Ru(bpy)3]2+ and exposed to white light, which promotes the formation of covalent bonds between adjacent tyrosine amino acids (inset). (B) This panel shows an L-eGFP/(L)8-, [Ru(bpy)3]2+-, and APS-mixture loaded into a PTFE tube using a 23 G needle before exposure to white light (top), and after (bottom). (C) This panel shows an extruded L-eGFP/(L)8-based hydrogel into a Tris solution. The inset shows a magnified image of an L-eGFP/(L)8-based hydrogel. The diameter distribution is 552 ± 8 μm, in agreement with the interior diameter of the PFTE tube used during the polymerization (558 μm). Please click here to view a larger version of this figure.
Figure 2: Force-clamp rheometer design and set-up. (A) Rendering of the assembled force-clamp hydrogel rheometer. The inset shows a protein-based hydrogel sample attached to the voice coil and force sensor hooks inside the solution chamber. (B) Rendering of the exploded view of the force-clamp hydrogel rheometer: (a – c) the x–y–z manipulators for adjusting the voice-coil hook position, (d) the linear voice coil motor, (e) the force transducer, (f) the force transducer holder, (g) the solution chamber, and (h – i) the x–y manipulators for adjusting the force transducer position. (C) Scheme of the force-clamp hydrogel rheometer set-up. The scheme shows a protein-based hydrogel sample attached to a force sensor and voice coil hooks using medical sutures. The analog PID system changes the hydrogel length by adjusting the voice-coil position to follow the force set point. (D) PID system response using different integral-gain values (I) to reach the force set point (dashed line). The colored traces represent the measured force (bottom) and strain (top) derived from the PID system response. Please click here to view a larger version of this figure.
Figure 3: L-eGFP/(L)8-based hydrogel attachment process. (A) Close-up view of a suture loop, tied with a loose double overhand knot used to attach the hydrogel sample to the hooks. (B) The two suture loops are placed on the force sensor hook used in protein-based hydrogel attachment. (C) An L-eGFP/(L)8-based hydrogel sample is hung between the hooks (indicated by the arrows). (D) The suture loops on the side of the voice coil (left) and the force sensor hook (right) are tightened around the hydrogel sample at the bend of each hook to prevent the sample from slipping during the measurements. Afterward, the excess sutures are trimmed using medical scissors (indicated by the red arrows). Please click here to view a larger version of this figure.
Figure 4: Representative force-ramp measurement and data analysis curves for an L-eGFP/(L)8-based hydrogel sample. (A) Typical slack measurement curve (red) used to determine the zero force of the force sensor and the true length of the hydrogel. Two linear curves (the blue and the orange lines) are used to fit both regimes: first, when the gel is under force (blue line), and second, when the gel becomes slack (plateau – orange line). The intersection between the two lines is used to calculate the true hydrogel length at zero force. The arrow shows the direction of the motion. The inset shows the location of the zero force and the correction of the hydrogel length. (B) Representative force-ramp curve applied to the hydrogel sample. (C) Trace representing the coil position movement as a function of time. The coil starts from the initial position defined in the protocol at step 3.1 (7.5 mm). (D) Representative curve of the extension of the hydrogel sample as a function of time. The extension is calculated as the displacement between the measured coil position and its initial position. (E) Representative strain-versus-time curve. The strain is calculated by dividing the extension by the true gel length calculated from the slack measurement. (F) Representative stress-strain curve of a hydrogel sample. Please click here to view a larger version of this figure.
Figure 5: Constant-force measurement and data analysis. (A) Representative trace of the constant-force protocol applied to a hydrogel. The hydrogel is exposed to 0.1 mN for 30 s, then the force is increased to 1 mN for 120 s, and finally, the force is quenched back to 0.1 mN for 300 s. (B) This panel shows a coil position trace versus the time representing the change in the length of the hydrogel sample following the force protocol. (C) This panel shows the gel extension measured from the displacement of the voice-coil. (D) Representative figure of stress (bottom) and strain traces (top) after the data analysis. Please click here to view a larger version of this figure.
Herein, we describe a force-clamp rheometry technique to investigate the biomechanical response of low-volume protein-based hydrogels. Additionally, a protocol is provided to synthesize a uniform cylindrical low-volume protein hydrogel sample. A protocol is also presented which describes how to tie different types of protein-based hydrogels with various elasticities without causing any mechanical deformation or damage to the protein-based hydrogel samples or slippage of the gel on the hooks. The analog PID system, together with the linear voice coil and the force sensor, enable the application of controlled-force protocols such as force ramp and constant force. Recently, this technique has been used to study the biomechanical response of different cross-linked concentrations of BSA-based hydrogels in different experimental solutions7.
An important aspect when formulating and working with protein hydrogels is the reproducibility of the measurements. If gels are formulated with a too low protein concentration or incomplete cross-linking, permanent plastic deformations will appear during extension7. These plastic deformations would drastically limit the data interpretation, as the viscoelastic effects would come from both the domain unfolding and the molecular rearrangement inside the gel. An easy test to see if there complete cross-linking is to immerse the hydrogel in chemical denaturants, such as 6 M guanidinium chloride1. In this case, there should not be any viscoelastic effects in the stress-versus-strain curves, as all domains are unfolded chemically, and the molecules are now behaving as simple polymers4,7,26. Furthermore, the gel should recover its initial elasticity when immersed back in the initial buffer7.
If there are variations in the measured response between traces obtained with different gels, several aspects should be considered for troubleshooting: the protein aggregation in solution, a non-homogeneous mixing of the protein with the cross-linking chemicals, the presence of bubbles, the binding of the protein-based hydrogel to the PFTE tube due to incorrect silanization. Residues of silane on the tube walls may contaminate the hydrogel and lead to structural defects. To avoid this error, more compressed air is needed to ensure a total removal of the silane from the tube. Additionally, bubbles can form during the suction of the hydrogel photoactive mix into the PTFE tube. These bubbles can lead to sample damage and affect the biomechanical response of the hydrogel. To prevent any bubble formation, the end of the PTFE tube must be inside solution mix during the loading process and the syringe plunger must be retracted slowly. Another typical error is an over-tightening of the suture loops around the hydrogel samples during the attachment process, which may lead to a notch formation and the cutting of the hydrogel. The moving range of the voice coil limits the maximum extension of the attached hydrogel sample. This limitation has to be taken into account when measuring gels that extend several hundred percent of their initial length. For example, to extend a hydrogel for more than 200%, an initial length of less than 4 mm is required.
Protein-based hydrogels are a unique class of biomaterials due to their biocompatibility and high stretchability derived from proteins, their main building units, and the inherent folding transition that is characteristic for proteins. Additionally, these hydrogels have an excellent potential for tissue engineering, drug delivery systems, and biological ink (bioink) for 3D printing27. The force-clamp hydrogel rheometer can be used to investigate a large variety of proteins. Furthermore, the force-clamp rheometer enables the application of constant-force protocols on low-volume hydrogel samples. These experiments allow the decoupling of the elastic and viscoelastic behaviors and study (un)folding mechanics in a bulk approach.
The authors have nothing to disclose.
We acknowledge financial support from Research Growth Initiative (Award No. 101X340), National Science Foundation, Major Research Instrumentation Program (Grant No. PHY-1626450), Greater Milwaukee Foundation (Shaw Award) and University of Wisconsin System (Applied Research Grant).
SI-KG4A force transducer | World Precision Instruments (WPI) | SI-KG4A | |
Linear Voice Coil Motor | Equipement Solutions | LFA2010 | |
Bovine serum albumin | Rocky Mountain Biologicals (RMBIO) | BSA-AAF-1XG / 100 G | |
Trizma | Sigma-Aldrich | T1503-1KG | |
Sodium chloride | Sigma-Aldrich | S7653-1KG | |
Ammonium persulfate | Sigma-Aldrich | 248614-100G | |
Tris(bipyridine)ruthenium(II) chloride | Sigma-Aldrich | 544981-1G | |
EXPRESS MEDICAL SUPPLIES 6-0 NYLON SUTURE 12/PK | Fisher Scientific | NC0395626 | |
1mL Syringe Only, Luer-Lok Tip | BD | 309628 | |
Silane, Sigmacote | Sigma-Aldrich | SL2-25ML | |
Microbore PTFE Tubing, 0.022"ID x 0.042"OD, 100 ft/roll | Cole-Parmer | EW-06417-21 | |
Hypodermic Needle, 23 Gauge | Healthcare Supply Pros | 305194 | |
Jensen Global JG24-1.5X Red IT Dispensing Tips – 24 gauge | KIMCO | JG24-1.5X | |
USH-103D USHIO 100W Short Arc Mercury Lamp | ALB | USH-103D USHIO | |
Medical Tweezers | |||
Medical scissors | |||
Olympus | |||
The computer code and CAD design of the custom parts can be made available on request to the corresponding author. |