# A new analytical method for estimating lumped parameter constants of linear viscoelastic models from strain rate tests

## Abstract

We introduce a new function, the apparent elastic modulus strain-rate spectrum, \(E_{\mathrm{app}} ( \dot{\varepsilon} )\), for the derivation of lumped parameter constants for Generalized Maxwell (GM) linear viscoelastic models from stress-strain data obtained at various compressive strain rates (\(\dot{\varepsilon}\)). The \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) function was derived using the tangent modulus function obtained from the GM model stress-strain response to a constant \(\dot{\varepsilon}\) input. Material viscoelastic parameters can be rapidly derived by fitting experimental \(E_{\mathrm{app}}\) data obtained at different strain rates to the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) function. This single-curve fitting returns similar viscoelastic constants as the original epsilon dot method based on a multi-curve global fitting procedure with shared parameters. Its low computational cost permits quick and robust identification of viscoelastic constants even when a large number of strain rates or replicates per strain rate are considered. This method is particularly suited for the analysis of bulk compression and nano-indentation data of soft (bio)materials.

## Keywords

Strain rate Epsilon dot Mechanical properties Viscoelastic models Soft materials## 1 Introduction

To date, different testing and analysis methods are used to derive quantitative mechanical properties for describing intrinsic material behavior and predicting material responses under specific loading conditions (Mattei and Ahluwalia 2016). Although mechanical characterization is often limited to the derivation of elastic properties, many materials, such as soft tissues and hydrogels, are known to exhibit viscoelastic behavior with time-dependent responses (Fung 1993; Mattei et al. 2014, 2015b, 2017a; Oyen 2013; Tirella et al. 2014; Zhao et al. 2010). Creep and stress-relaxation tests are among the most common methods used to characterize material viscoelastic properties (Chaudhuri et al. 2015; Chin et al. 2011; Higgs and Ross-Murphy 1990). If a material is subjected to strain or stress inputs small enough so that its rheological functions do not depend on the input level, the material response is said to be within the linear viscoelastic range (LVR).

Another popular method to characterize material viscoelastic behavior is through dynamic mechanical analysis (DMA), based on applying a small amplitude cyclic strain (or stress) input on a sample and measuring the resultant cyclic stress (or strain) response (Gabler et al. 2009; Kiss et al. 2004; Soong et al. 2006). For a given sinusoidal strain input the resulting stress response will be sinusoidal if the applied strain is small enough so that the tissue can be approximated as linearly viscoelastic. Viscoelastic material response is characterized by a phase lag (\(\delta\)) between the strain input and the stress response, which is comprised between 0° (purely elastic) and 90° (purely viscous). The dynamic mechanical properties are quantified using the complex modulus (\(E^{*}\)) which can be thought of as an overall resistance to deformation under dynamic loading. The complex modulus is composed of the storage (\(E'\), elastic component) and the loss (\(E{''}\), viscous component) moduli, which are additive under the linear theory of viscoelasticity (\(E^{*} = E' + iE{''}\)) (Menard 2008).

However, it is well known that these viscoelastic testing methods may pose some limitations in the case of very compliant materials, such as soft tissues and hydrogels (Tirella et al. 2014). Indeed, both step-response and dynamic mechanical tests require the establishment of an initial contact between the sample and the testing apparatus to “trigger” measurements. Starting from this contact point, a given stimulus (e.g. step of deformation or force in the case of stress relaxation or creep, respectively, or cyclic stress or strain in the case of DMA) is applied to the sample under testing, then the resultant response is measured. As a consequence, force- or strain-triggered methods are likely to cause significant pre-stress on very soft samples, altering their status. Moreover, they generally require quite long measurement trials, which may result in sample deterioration during tests (Mattei et al. 2014). To address these issues, we have recently proposed the epsilon dot method (\(\dot{\varepsilon} M\)) for deriving material viscoelastic constants through rapid measurements performed at different strain rates within the LVR (Mattei et al. 2015b; Tirella et al. 2014). However, as it is based on a global multi-curve fitting with shared parameters of stress-time data acquired at different constant strain rates, the method becomes computationally expensive when a large number of strain rates and/or replicates per strain rate are considered. Here, we introduce the apparent elastic modulus strain-rate spectrum, \(E_{\mathrm{app}}(\dot{\varepsilon} )\), as a function to derive lumped parameter constants for Generalized Maxwell (GM) linear viscoelastic models from a single-curve fitting of experimental \(E_{\mathrm{app}}\) data obtained at different \(\dot{\varepsilon} \).

## 2 Methods

For very high (\(\dot{\varepsilon} \to\infty\)) and low (\(\dot {\varepsilon} \to0\)) strain rates, the \(E_{t}\) becomes independent of the strain and is, respectively, equal to the sum of all the spring constants present in the lumped model (namely the instantaneous modulus, \(E_{\mathrm{inst}} = E_{0} + \sum_{i = 1}^{N} E_{i}\) for \(\dot{\varepsilon} \to\infty\)), or to \(E_{0}\) (generally noted as the equilibrium modulus \(E_{\mathrm{eq}} = E_{0}\)) for \(\dot{\varepsilon} \to0\) as expected from classical viscoelastic theory (Lakes 2009).

Zhang et al. showed that: (i) the tangent modulus for constant strain-rate tests, \(E_{t}(t)\), is equivalent to the relaxation modulus from stress-relaxation tests, \(E(t) = \sigma(t) / \varepsilon_{0}\), where \(\sigma(t)\) is the stress measured over time in response to a step strain input \(\varepsilon_{0}\), and (ii) the plot of \(\sigma(t) / \dot{\varepsilon} \) versus \(\varepsilon(t) / \dot{\varepsilon} \), whose tangent returns \(E_{t}(t) = E(\varepsilon(t) / \dot{\varepsilon} )\), is no longer dependent on the strain rate (i.e. curves obtained at different strain rates can be merged into one) for linear viscoelasticity (Zhang et al. 2002). Note that if \(\sigma(t) / \dot{\varepsilon} \) versus \(\varepsilon(t) / \dot{\varepsilon} \) curves collected at different strain rates cannot be merged into one, the viscoelasticity of the material under testing is non-linear and the linear superposition principle cannot be applied.

If a material is known to exhibit pure linear viscoelastic behavior, then in principle the lumped constants of a given linear viscoelastic model (i.e. spring \(E_{i}\) and dashpot \(\eta_{i}\) values) can be derived by fitting the non-linear stress-strain data acquired at a single constant strain-rate to Eq. (2). The strain-range considered in the fitting should extend up to the region in which the stress-strain tangent (\(E_{t}\)) becomes independent of the strain in order to ensure that all the viscoelastic relaxation phenomena have occurred and hence are included in the fitted dataset. However, many real materials are non-linearly elastic, viscoelastic or inelastic. Thus, they generally exhibit either strain-hardening (concave up) or strain-softening (concave-down) stress-strain responses to a constant strain rate. Most biomedical materials, including soft tissues and hydrogels, exhibit concave up \(\sigma- \varepsilon\) curves (Fung 1993; Jaspers et al. 2014; De Pascalis et al. 2014; Rimmer 2011; Vena et al. 2006), a clear indication of non-linear strain-dependent behavior. As a consequence, linear viscoelastic models cannot be used to describe the material mechanics. Conversely, in the case of concave-down stress-strain curves it is almost impossible to determine a priori whether the non-linear behavior observed comes from linear viscoelastic phenomena or non-linear material characteristics.

As discussed above, viscoelastic materials do not exhibit an initial linear portion on their \(\sigma- \varepsilon\) curve to calculate a Young’s modulus. Nonetheless, from an engineering point of view, they are often treated as linearly viscoelastic in the region of small deformations (Mattei et al. 2014; Tirella et al. 2014; Yan and Pochan 2010). Hence, it is common practice to identify an initial linear region (called the linear viscoelastic region, LVR) for deriving an apparent (i.e. strain-rate dependent) elastic modulus (\(E_{\mathrm{app}}\)), which is independent of the magnitude of the applied strain or stress. The LVR can be considered as the first *nearly linear**tract* of the non-linear stress-strain response exhibited by linear viscoelastic materials: within this region the material’s molecular arrangements are close to equilibrium and the mechanical response is essentially a reflection of internal dynamic processes at the molecular level (Choi et al. 2015). Since material rheological functions do not depend on the input level within the LVR, linear viscoelastic models can be reasonably employed to analyze experimental mechanical data. Depending on the testing method chosen to characterize material linear viscoelastic properties, mechanical data within LVR are typically acquired at: (i) multiple stress or strain step-input amplitudes (in the case of creep-compliance or stress-relaxation tests, respectively), (ii) constant stress or strain rate (constant-rate tests like the epsilon-dot method, \(\dot{\varepsilon} M\)), or (iii) multiple frequencies (dynamic mechanical analysis, DMA).

## 3 Results

Maxwell SLS viscoelastic parameters estimated for gelatin and PDMS samples through \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting of apparent moduli obtained at various strain rates. \(E_{\mathrm{inst}}\), \(E_{\mathrm{eq}}\) and \(\tau\) results are expressed as estimated parameter value ± standard error of estimation along with those obtained using the \(\dot{\varepsilon} M\) for comparison. The last row reports the mean ± standard deviation of the computation time for the 7 different sets of initial guess values investigated

Gelatin | PDMS | |||
---|---|---|---|---|

\(E_{\mathrm{app}} ( \dot{\varepsilon} )\) | | \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) | | |

\(E_{\mathrm{inst}}\) (kPa) | 11.12 ± 1.00 | 11.23 ± 0.45 | (2.58 ± 0.11)⋅10 | (2.55 ± 0.04)⋅10 |

\(E_{\mathrm{eq}}\) (kPa) | 3.42 ± 0.77 | 2.43 ± 0.10 | (2.18 ± 0.03)⋅10 | (2.14 ± 0.01)⋅10 |

| 4.69 ± 1.76 | 4.85 ± 0.47 | 0.81 ± 0.28 | 0.66 ± 0.25 |

\(R^{2}\) | 0.98 | 0.92 | 0.98 | 0.98 |

Computation time (s) | 1.26 ± 0.03 | 8.59 ± 0.39 | 1.34 ± 0.07 | 7.78 ± 0.22 |

Fitting results were independent of the set of initial guess parameter values both for the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) and the \(\dot{\varepsilon} M\) method (Supplementary Information SI 2). No statically significant differences were found between the viscoelastic parameters estimated with the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting and the \(\dot{\varepsilon} M\) for either gelatin or PDMS samples, demonstrating the equivalence of the two analysis methods (Table 1). Moreover, the significantly lower computational cost highlights the efficiency of the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting method with respect to the original \(\dot{\varepsilon} M\).

## 4 Discussion

To overcome the issues of pre-stress and long experimental testing trials for viscoelastic characterization of soft materials using classical testing methods, we developed the epsilon dot method (\(\dot{\varepsilon} M\)) which is based on a series of rapid strain rate measurements (Mattei et al. 2015b; Tirella et al. 2014). However, the \(\dot{\varepsilon} M\) derivation of material viscoelastic constants involves a global multi-curve fitting of stress-time data obtained at different constant strain rates, performing chi-square minimization in a combined parameter space where viscoelastic constants to estimate are shared between the globally fitted curves (Tirella et al. 2014). As a result, this method is computationally expensive and difficult to automate when a large number of strain rates and/or replicates per strain rate are considered.

Starting from the strain-rate dependent apparent elastic modulus (\(E_{\mathrm{app}}\)) typically used for describing material viscoelastic behavior, we introduce the concept of the \(E_{\mathrm{app}}\) epsilon dot spectrum, \(E_{\mathrm{app}} ( \dot{\varepsilon} )\). This function enables the calculation of viscoelastic constants for Generalized Maxwell (GM) models through a single-curve fit of \(E_{\mathrm{app}}\) data obtained at different constant strain rate (\(\dot{\varepsilon}\)) versus \(\dot{\varepsilon}\), according to Eq. (4). The \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) can be interpreted as the strain-rate domain equivalent of the storage modulus frequency spectrum, \(E ' (f)\), typical of DMA analysis.

The \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) method proposed in this study was validated versus the original \(\dot{\varepsilon} M\) described in Tirella et al. (2014). As discussed in Sect. 2, unlike purely elastic materials, viscoelastic materials do not exhibit an initial linear portion on their stress-strain curve. Thus, the selection of the LVR is critical for any study dealing with viscoelastic material characterization and it is likely to affect the derived mechanical properties. According to our previous work on the \(\dot{\varepsilon} M\) (Tirella et al. 2014), we here identified the LVR as the region in which stress varies linearly with strain with \(R^{2} > 0.999\). To obtain meaningfully comparable results, two experimental \(E_{\mathrm{app}}\) vs. \(\dot{\varepsilon}\) datasets to analyze with the new \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting method were obtained from the same apparent elastic moduli reported in Tirella et al. (2014) for gelatin and PDMS samples. For the same reason, the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting was performed considering the same LVR range (\(0 \div0.01\) strain range) and linear viscoelastic model (Maxwell SLS) previously used to derive lumped viscoelastic constants with the \(\dot{\varepsilon} M\).

Viscoelastic parameters for a Maxwell SLS model estimated using the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) equation were found to be statistically similar to those obtained with the \(\dot{\varepsilon} M\), demonstrating the equivalence of the two fitting approaches. Notably, the standard error of parameter estimations obtained with the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting are slightly higher than those of the \(\dot{\varepsilon} M\), because fewer data are considered in the fitting procedure. In fact, for each experimental measurement made at a given strain rate, the former method considers only \(n=1\) representative point (i.e. \(E_{\mathrm{app}}\)) instead of the entire stress-time curve within LVR considered by the \(\dot{\varepsilon} M\).

It should be noted that, although based on a non-linear function (Eq. (4)), the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) method can only be used to characterize linear viscoelastic properties. Indeed, the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) function is non-linear only with respect to the testing input variable (i.e. the strain rate, \(\dot{\varepsilon}\)), but not to its viscoelastic parameters (i.e. spring \(E_{i}\) and dashpot \(\eta_{i}\) values), which are considered constants. This is similar to the function used to fit stress-time data in the original \(\dot{\varepsilon} M\) or to those used to fit storage and loss moduli obtained from DMA, which are both non-linear in their respective testing input variable (i.e. strain rate in the case of \(\dot{\varepsilon} M\) or frequency in the case of DMA), but constant in their viscoelastic parameters. Therefore, like \(\dot{\varepsilon} M\) and DMA, this method can only be used to analyze LVR data and describe material linear viscoelastic properties.

In conclusion, the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting method presented in this work is robust and accurate and, more importantly, because a single curve is used to describe material behavior over the strain-rate spectrum, it is computationally more efficient than the original \(\dot{\varepsilon} M\) (as demonstrated by the significantly reduced computation time, Table 1). Hence it could facilitate the adoption of strain-rate mechanical testing methods and subsequent calculation of viscoelastic parameters among researchers interested in characterizing viscoelastic (bio)materials. Nano-indentation methods are particularly suited for the automated derivation of material viscoelastic properties with this approach, since they allow the acquisition of \(E_{\mathrm{app}}\) data at several strain rates in different locations of the same sample (Mattei et al. 2015b). Besides nano-indentation, it is worth noting that the \(E_{\mathrm{app}} ( \dot{\varepsilon} )\) fitting method presented in this work can be adopted to analyze LVR stress-strain data obtained from any type of constant strain-rate testing approach, regardless of the measurement length-scale, such as bulk compression (as in this work) or tension and macro-indentation. Potential applications of this viscoelastic characterization method range from mechanical and structural design for (bio)material and civil engineering (Jelen et al. 2013; Öchsner and Altenbach 2015), to tissue engineering (Mattei et al. 2017b; Tirella et al. 2015) and cell mechano-biology (Mammoto et al. 2013; Mattei et al. 2015a).

## Notes

### Acknowledgements

The work leading to these results has received funding from the European Union’s Seventh Framework Programme (FP7/2007-2013) under grant agreement no. 304961 (ReLiver), from the European Union’s Horizon 2020 research and innovation programme under the Marie Sklodowska-Curie grant agreement No 705296 (ENDYVE), and from the PRA_2016_56 of the University of Pisa.

## Supplementary material

## References

- Chaudhuri, O., Gu, L., Darnell, M., Klumpers, D., Bencherif, S.A., Weaver, J.C., Huebsch, N., Mooney, D.J.: Substrate stress relaxation regulates cell spreading. Nat. Commun.
**6**, 6364 (2015). https://doi.org/10.1038/ncomms7365 CrossRefGoogle Scholar - Chin, H.C., Khayat, G., Quinn, T.M.: Improved characterization of cartilage mechanical properties using a combination of stress relaxation and creep. J. Biomech.
**44**, 198–201 (2011). https://doi.org/10.1016/j.jbiomech.2010.09.006 CrossRefGoogle Scholar - Choi, B., Loh, X.J., Tan, A., Loh, C.K., Ye, E., Joo, M.K., Jeong, B.: Introduction to in situ forming hydrogels for biomedical applications. Presented at the 2015 Google Scholar
- De Pascalis, R., Abrahams, I.D., Parnell, W.J.: On nonlinear viscoelastic deformations: a reappraisal of Fung’s quasi-linear viscoelastic model. Proc. Math. Phys. Eng. Sci.
**470**, 20140058 (2014). https://doi.org/10.1098/rspa.2014.0058 CrossRefGoogle Scholar - Fung, Y.C.: Biomechanics: Mechanical Properties of Living Tissues. Springer, New York (1993) CrossRefGoogle Scholar
- Gabler, S., Stampfl, J., Koch, T., Seidler, S., Schuller, G., Redl, H., Juras, V., Trattnig, S., Weidisch, R.: Determination of the viscoelastic properties of hydrogels based on polyethylene glycol diacrylate (PEG-DA) and human articular cartilage. Int. J. Mater. Eng. Innov.
**1**, 3 (2009). https://doi.org/10.1504/IJMATEI.2009.024024 CrossRefGoogle Scholar - Higgs, P.G., Ross-Murphy, S.B.: Creep measurements on gelatin gels. Int. J. Biol. Macromol.
**12**, 233–240 (1990). https://doi.org/10.1016/0141-8130(90)90002-R CrossRefGoogle Scholar - Jaspers, M., Dennison, M., Mabesoone, M.F.J., MacKintosh, F.C., Rowan, A.E., Kouwer, P.H.J.: Ultra-responsive soft matter from strain-stiffening hydrogels. Nat. Commun.
**5**, 5808 (2014). https://doi.org/10.1038/ncomms6808 CrossRefGoogle Scholar - Jelen, C., Mattei, G., Montemurro, F., De Maria, C., Mattioli-Belmonte, M., Vozzi, G.: Bone scaffolds with homogeneous and discrete gradient mechanical properties. Mater. Sci. Eng. C
**33**, 28–36 (2013). https://doi.org/10.1016/j.msec.2012.07.046 CrossRefGoogle Scholar - Kiss, M.Z., Varghese, T., Hall, T.J.: Viscoelastic characterization of in vitro canine tissue. Phys. Med. Biol.
**49**, 4207–4218 (2004) CrossRefGoogle Scholar - Lakes, R.S.: Viscoelastic Materials. Cambridge University Press, Cambridge (2009) CrossRefMATHGoogle Scholar
- Mammoto, T., Mammoto, A., Ingber, D.E.: Mechanobiology and developmental control. Annu. Rev. Cell Dev. Biol.
**29**, 27–61 (2013). https://doi.org/10.1146/annurev-cellbio-101512-122340 CrossRefGoogle Scholar - Mattei, G., Ahluwalia, A.: Sample, testing and analysis variables affecting liver mechanical properties: a review. Acta Biomater.
**45**, 60–71 (2016). https://doi.org/10.1016/j.actbio.2016.08.055 CrossRefGoogle Scholar - Mattei, G., Tirella, A., Gallone, G., Ahluwalia, A.: Viscoelastic characterisation of pig liver in unconfined compression. J. Biomech.
**47**, 2641–2646 (2014). https://doi.org/10.1016/j.jbiomech.2014.05.017 CrossRefGoogle Scholar - Mattei, G., Ferretti, C., Tirella, A., Ahluwalia, A., Mattioli-Belmonte, M.: Decoupling the role of stiffness from other hydroxyapatite signalling cues in periosteal derived stem cell differentiation. Sci. Rep.
**5**, 10778 (2015a). https://doi.org/10.1038/srep10778 CrossRefGoogle Scholar - Mattei, G., Gruca, G., Rijnveld, N., Ahluwalia, A.: The nano-epsilon dot method for strain rate viscoelastic characterisation of soft biomaterials by spherical nano-indentation. J. Mech. Behav. Biomed. Mater.
**50**, 150–159 (2015b). https://doi.org/10.1016/j.jmbbm.2015.06.015 CrossRefGoogle Scholar - Mattei, G., Cacopardo, L., Ahluwalia, A.: Micro-mechanical viscoelastic properties of crosslinked hydrogels using the nano-epsilon dot method. Materials
**10**, 889 (2017a). https://doi.org/10.3390/ma10080889 CrossRefGoogle Scholar - Mattei, G., Magliaro, C., Giusti, S., Ramachandran, S.D., Heinz, S., Braspenning, J., Ahluwalia, A.: On the adhesion-cohesion balance and oxygen consumption characteristics of liver organoids. PLoS ONE
**12**, e0173206 (2017b). https://doi.org/10.1371/journal.pone.0173206 CrossRefGoogle Scholar - Menard, K.P.: Dynamic Mechanical Analysis: A Practical Introduction. CRC Press, Boca Raton (2008) CrossRefGoogle Scholar
- Öchsner, A., Altenbach, H.: Mechanical and Materials Engineering of Modern Structure and Component Design. Springer, Cham (2015) CrossRefGoogle Scholar
- Oyen, M.L.: Mechanical characterisation of hydrogel materials. Int. Mater. Rev.
**59**, 44–59 (2013). https://doi.org/10.1179/1743280413Y.0000000022 CrossRefGoogle Scholar - Rimmer, S.: Biomedical Hydrogels: Biochemistry, Manufacture and Medical Applications. Elsevier, Amsterdam (2011) CrossRefGoogle Scholar
- Roylance, D.: Engineering Viscoelasticity, vol. 2139, pp. 1–37. Dep. Mater. Sci. Eng. Inst. Technol., Cambridge (2001) Google Scholar
- Soong, S.Y., Cohen, R.E., Boyce, M.C., Mulliken, A.D.: Rate-dependent deformation behavior of POSS-filled and plasticized poly(vinyl chloride). Macromolecules
**39**, 2900–2908 (2006). https://doi.org/10.1021/ma052736s CrossRefGoogle Scholar - Tirella, A., Mattei, G., Ahluwalia, A.: Strain rate viscoelastic analysis of soft and highly hydrated biomaterials. J. Biomed. Mater. Res., Part A
**102**, 3352–3360 (2014). https://doi.org/10.1002/jbm.a.34914 CrossRefGoogle Scholar - Tirella, A., La Marca, M., Brace, L.-A., Mattei, G., Aylott, J.W., Ahluwalia, A.: Nano-in-micro self-reporting hydrogel constructs. J. Biomed. Nanotechnol.
**11**, 1451–1460 (2015). https://doi.org/10.1166/jbn.2015.2085 CrossRefGoogle Scholar - Vena, P., Gastaldi, D., Contro, R.: A constituent-based model for the nonlinear viscoelastic behavior of ligaments. J. Biomech. Eng.
**128**, 449–457 (2006). https://doi.org/10.1115/1.2187046 CrossRefGoogle Scholar - Yan, C., Pochan, D.J.: Rheological properties of peptide-based hydrogels for biomedical and other applications. Chem. Soc. Rev.
**39**, 3528–3540 (2010). https://doi.org/10.1039/b919449p CrossRefGoogle Scholar - Zhang, X.R.R., Pang, J.H.L.H.L., Shi, X.Q.Q., Wang, Z.P.P.: On the moduli of viscoelastic materials. In: 4th Electron. Packag. Technol. Conf. 2002. 639798, pp. 318–322 (2002). https://doi.org/10.1109/EPTC.2002.1185690 CrossRefGoogle Scholar
- Zhao, X., Huebsch, N., Mooney, D.J., Suo, Z.: Stress-relaxation behavior in gels with ionic and covalent crosslinks. J. Appl. Phys.
**107**, 63509 (2010). https://doi.org/10.1063/1.3343265 CrossRefGoogle Scholar

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