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REVIEW 4 major objections 5 minor 36 references

Influence of applied stress on energy dissipation and crack growth in articular cartilage

T0 review · 4 major / 5 minor · reviewed 2026-08-12 · deepseek-v4-flash

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Pith's one-line read This paper establishes power-law relationships between applied compressive stress amplitude and both crack growth and bulk softening in articular cartilage under cyclic loading.

desk verdict Useful empirical damage fits for cartilage fatigue, but the crack-growth law needs a check for initial crack-length imbalance. read the letter →

arxiv 2411.15316 v1 pith:5LW6MJQ3 submitted 2024-11-22 physics.med-ph

Dipul Chawla , Eric Kazyak , Melih Eriten , Corinne R. Henak This is my paper · ORCID
classification physics.med-ph
keywords articularcartilagecrackgrowthcyclicloadingpower-lawregressionVeronda-Westmannmodelenergydissipationphaseangleosteoarthritis
verification ladder T0 review T1 audit T2 compute T3 formal

The pith

A machine-rendered reading of the paper's core claim, the machinery that carries it, and where it could break.

The reading

This paper asks whether the damage that accumulates in articular cartilage under repeated compressive loading can be captured by simple stress-based laws, analogous to fatigue crack growth laws used for metals. Using porcine patellar cartilage plugs with microscale cracks introduced by microindentation, the authors cyclically compressed samples at six physiologically relevant stress amplitudes and measured surface crack extension alongside bulk changes in thickness, stiffness, energy dissipation, and phase angle. They report that both local and global damage intensify with stress amplitude: normalized thickness falls as $y = 1.004x^{-0.171}$, apparent stiffness falls as $y = 1.810x^{-0.386}$, and crack growth rises as $\Delta a = 18.720x^{0.347}$. Energy dissipation and phase angle drop after fatigue loading, but with no dependence on stress level. If these empirical laws hold, cartilage fatigue damage becomes predictable from load level alone, which would aid efforts to prevent or delay osteoarthritis and guide bio-inspired soft materials.

What carries the argument

The argument is carried by two measured damage channels linked through power-law regressions on stress amplitude. The local channel is the surface crack: cracks nucleated by microindentation are imaged before and after loading, and the change in crack length $\Delta a$ is regressed against $\Delta\sigma$. The global channel is the material response: the loading part of the first diagnostic cycle is fit to an incompressible Veronda-Westmann strain-energy function, whose parameter product $C_1C_2$ serves as apparent stiffness, alongside normalized thickness and dynamic phase angle and energy dissipation from sinusoidal fits. The single empirical law $\Delta a = 18.720(\Delta\sigma)^{0.347}$ is the paper's compact statement that localized damage scales with applied stress.

What would settle it

Repeat the fatigue protocol at the same stress amplitudes but at a different loading frequency, such as 0.1 Hz or 5 Hz; if the normalized $C_1C_2$ versus $\Delta\sigma$ curves shift substantially, the fitted softening includes rate-dependent poroviscoelastic contributions rather than pure damage. Alternatively, measure crack growth at $\Delta\sigma \approx 12$ MPa and compare with the predicted $\Delta a = 18.720(\Delta\sigma)^{0.347}$: a value outside the 95% confidence interval would falsify the power law.

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Extended reading notes

Core claim

Under compressive cyclic loading at 1 Hz for 3000 cycles, applied stress amplitude controls both forms of cartilage damage. Surface crack length increases with stress amplitude following $\Delta a = 18.720(\Delta\sigma)^{0.347}$ ($R^2=0.42$), and the normalized change in crack length follows $y = 0.050x^{0.308}$. In parallel, bulk tissue damage appears as irreversible compaction, with normalized thickness following $y = 1.004x^{-0.171}$ ($R^2=0.65$), and as softening measured through the Veronda-Westmann apparent stiffness $C_1C_2$, which falls by 55.2% from the lowest to the highest stress level following $y = 1.810x^{-0.386}$. Dynamic dissipation metrics, phase angle and energy dissipation, decrease after fatigue but do not correlate with stress level, suggesting that frequency and cycle count matter more for those quantities. The paper's central claim is that both local damage (crack growth) and global damage (thickness loss and softening) are governed by power-law functions of applied stress amplitude, establishing empirical fatigue laws for a poroviscoelastic tissue.

Load-bearing premise

The load-bearing premise is that the Veronda-Westmann stiffness fit on a single loading cycle isolates true material softening, rather than being contaminated by poroviscoelastic fluid flow, strain-rate effects, or platen friction; if those effects dominate the pre-to-post change, the global-damage laws do not measure what they claim.

Editorial extensions

If this is right

  • Fatigue damage in cartilage can be described by power-law functions of applied stress amplitude, giving a predictive form analogous to classical crack-propagation laws used for engineering materials.
  • Higher physiological stress levels produce both greater irreversible thinning and greater softening, so strenuous loading damages bulk tissue more than light loading.
  • Crack extension occurs even at the lowest tested stress, meaning cyclic loading at light-activity levels propagates existing microfissures.
  • Energy dissipation and phase angle decline after fatigue regardless of stress level, indicating that these dynamic properties capture cycle-induced damage rather than stress-level-dependent damage.
  • The reported constants provide a baseline for comparing future studies on other cartilage types, loading frequencies, or cycle counts.

Reading between the lines

Editorial extensions of the paper, not claims the author makes directly.

  • Replacing applied stress amplitude with a local crack-tip quantity, such as strain-energy release rate or stress intensity factor, could recast the measured $\Delta a$ curve in standard fatigue-crack coordinates and reveal whether a single mechanism governs the growth.
  • If the same power-law structure holds at other frequencies, the frequency dependence reported in prior work could be absorbed into the prefactor, yielding a master curve for cartilage fatigue over a wider loading range.
  • The stress-independent drop in phase angle and energy dissipation may indicate saturation after a moderate number of cycles or dominance of fluid-flow losses; measuring platen adhesion and crack-surface friction directly would test this.
  • The sublinear exponent of 0.347 implies that doubling stress amplitude does not double crack growth, a nonlinearity that could inform the design of cartilage repair or replacement materials tolerant of overloads.
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Editorial analysis

A structured set of objections, weighed in public.

Desk editor's note, referee report, and a circularity audit.

Referee Report

4 major / 5 minor

Summary. The manuscript reports an experimental study of fatigue damage in porcine patellar cartilage under compressive cyclic loading. Eighteen cylindrical plugs were microindented to nucleate surface cracks and then loaded at 1 Hz for 3000 cycles at six stress levels corresponding to physiological activities. The authors measure changes in cartilage thickness, Veronda-Westmann material constants (C1C2 as apparent stiffness), phase angle, energy dissipation, and crack length, and fit power-law relationships between these damage metrics and applied stress amplitude. The central claims are that normalized thickness and apparent stiffness decrease with increasing stress, that energy dissipation and phase angle decrease after fatigue loading but without a clear stress-level dependence, and that crack growth follows an empirical power law (Δa = 18.72 Δσ^0.347, R²=0.42). The paper interprets these trends as linking global damage (bulk mechanical changes) and local damage (crack extension) under physiological loading.

Significance. If the reported empirical laws are reliable, they would provide a quantitative starting point for relating applied stress amplitude to cartilage fatigue damage, with potential relevance for understanding osteoarthritis progression and for designing bio-inspired soft materials. The study has clear strengths: a well-described experimental protocol, repeated imaging of crack morphology, use of complementary constitutive and phenomenological fits, and explicit acknowledgment of several limitations. However, the significance is tempered by the modest statistical support (R² of 0.37–0.65, n≈3 per stress level, no inferential statistics) and by the post-hoc selection of the power-law form on the same data used to report the fits. The qualitative trends are plausible and consistent with prior literature, but the quantitative 'laws' as stated should be treated as descriptive correlations until validated on independent data.

major comments (4)
  1. [§3.3, Fig. 7] The central crack-growth claim (Δa = 18.72 Δσ^0.347, R²=0.42) is potentially confounded by variability in initial crack length across the six stress groups. The manuscript states in §2.2 that indentation conditions were chosen to produce 'comparable' crack lengths, but §2.4 and Fig. 3A report only a pooled histogram, with no per-group initial crack length summary, balance check, or blocking/randomization description. With only 18 samples and about three per stress level, chance imbalance in initial crack geometry could bias the regression of Δa on Δσ, especially since standard fracture mechanics relate crack growth to stress-intensity factor range, which scales with both stress and crack length. The authors should report initial crack lengths per group, include initial crack length as a covariate, or perform an analysis of Δa/a stratified by initial length to support the claim that the observed trend is driven by applied stress rather than initial crack geometry.
  2. [§2.3, Eqs. (1)–(2)] The apparent stiffness C1C2 is obtained by fitting a rate-independent, incompressible Veronda-Westmann hyperelastic model to the loading portion of the first diagnostic cycle at 1 Hz. Cartilage is poroviscoelastic, so changes in the fitted C1C2 between pre- and post-diagnostics could reflect changes in fluid flow, strain-rate effects, or platen friction rather than true intrinsic softening. The claim in §3.1 that C1C2 decreases following a power law with stress level (Fig. 5B) is load-bearing for the global-damage interpretation, but the fitting procedure does not separate rate-dependent and rate-independent contributions. The authors should either justify that the 1 Hz loading portion is dominated by elastic behavior, or supplement the analysis with an equilibrium or multi-rate characterization to confirm that the fitted parameter changes represent material softening rather than poroviscoelastic response.
  3. [§2.5 and Supplementary Fig. S1] The power-law form of all reported empirical laws was selected as the best-fitting functional form to the same data on which the fits are reported (Supplementary Fig. S1). This post-hoc selection, combined with modest R² values (0.37–0.65 for the global-damage metrics) and the absence of p-values, confidence intervals on the fitted parameters, or out-of-sample validation, means the fitted equations in §3.1 and §3.3 are descriptive correlations, not established laws. The authors should report parameter uncertainties, perform a formal model comparison (e.g., AIC or BIC) that accounts for the number of parameters, and ideally validate the predictive performance on hold-out data or a new set of specimens before referring to these relationships as empirical laws.
  4. [§3.1 and Fig. 5] The interpretation that C1C2 decreases with stress level is based on an aggregate fit with R²=0.37, and the data in Fig. 5 show substantial scatter, including an apparent increase in C1C2 at low stress levels. The text acknowledges this non-monotonicity in §4.2, but the power-law fit with R²=0.37 is still presented as a quantitative relationship. Given the small sample size per group and the large standard deviations (e.g., C1C2 at L1 is 1.52 ± 0.71), the authors should state explicitly whether the trend is statistically significant when accounting for within-group variability, and should avoid over-interpreting a fit that explains only 37% of the variance.
minor comments (5)
  1. [Abstract] The abstract states 'fracture imitation'; this appears to be a typo for 'fracture initiation'.
  2. [Eq. (3)] Equation (3) has a mismatched parenthesis: the right-hand side is written as σ = A(e^{B*ε}) − 1), which should be σ = A(e^{B*ε} − 1).
  3. [§4.2] The text refers to 'normalized cartilage thickness (τh) decreased with increasing load levels (Figure 5)', but the thickness data are shown in Figure 4; the cross-reference should be corrected.
  4. [§3.3] The caption of Figure 7 and the text 'Crack length, Δa, followed a power' should read 'followed a power law' for clarity.
  5. [Introduction / References] The spelling of 'Veronda-Westman' in §4.1 should be 'Veronda-Westmann' for consistency with Eqs. (1)–(2), and the references list should be checked for duplicated entries (e.g., Sadeghi et al. 2018a/2018b appear to be the same paper).

Circularity Check

0 steps flagged · score 0.0 of 10

No significant circularity: the empirical power laws are labeled as fits, no prediction is derived from an input that is itself the fitted target, and self-citations are not load-bearing.

full rationale

The paper is an empirical study that fits regression curves to measured data; it does not claim a first-principles derivation or an out-of-sample prediction. In Section 2.5 the authors state that 'power-law based regression analyses were performed on the normalized variables as function of applied stress amplitude,' and Section 3 reports the resulting fits as 'following a trend' with R² values. The Supplementary Information explicitly notes that the power-law form was selected because it 'had the highest correlation coefficient, hence used in the main text.' This is an in-sample goodness-of-fit choice, not a fitted parameter renamed as a prediction. No quantity is defined in terms of another in a way that forces the outcome: crack growth Δa is directly measured from microscopy images, applied stress Δσ is independently set by the loading protocol, and the Veronda-Westmann constants are fitted from diagnostic loading cycles that are separate from the fatigue stress levels. The only self-citations (Chawla et al. 2021, 2022, 2024) support the crack-nucleation technique and recovery-time sufficiency; neither is the basis of the central stress–damage trends, and the present data themselves carry those trends. The skeptic's concern about initial crack-length imbalance is a statistical validity issue (potential confounding), not a circularity of the derivation chain. Accordingly, no circular step can be quoted or reduced by construction, and the honest finding is no significant circularity, score 0.

Assumptions & free parameters 6 free parameters · 5 assumptions · 0 invented entities

The central claims rest on fitted power-law coefficients, per-sample hyperelastic constants, and several domain assumptions about how stress, stiffness, and crack length are inferred from macroscopic measurements. No new physical entities are introduced. The most consequential assumption is treating cartilage as a rate-independent hyperelastic material for stiffness extraction despite its known poroviscoelastic behavior.

free parameters (6)
  • Power-law coefficient and exponent for normalized thickness = 1.004 (coefficient), -0.171 (exponent)
    Fit to normalized thickness vs stress amplitude data, R²=0.65 (Section 3.1).
  • Power-law coefficient and exponent for normalized C2 = 8.840 (coefficient), -0.918 (exponent)
    Fit to normalized C2 vs stress amplitude data, R²=0.37 (Section 3.1).
  • Power-law coefficient and exponent for normalized C1C2 = 1.810 (coefficient), -0.386 (exponent)
    Fit to normalized apparent stiffness C1C2 vs stress amplitude data, R²=0.37 (Section 3.1).
  • Power-law coefficient and exponent for crack growth = 18.720 (coefficient), 0.347 (exponent)
    Fit to change in crack length vs stress amplitude data, R²=0.42 (Section 3.3).
  • Power-law coefficient and exponent for normalized crack growth = 0.050 (coefficient), 0.308 (exponent)
    Fit to normalized change in crack length vs stress amplitude data, R²=0.32 (Supplementary Figure S4).
  • Veronda-Westmann constants C1 and C2 per sample = per-sample fitted values not reported
    Fitted from Eq. (1) to diagnostic loading curves and used to compute apparent stiffness C1C2; these are model parameters, not physical constants.
assumptions (5)
  • domain assumption Incompressible, isotropic Veronda-Westmann hyperelastic model describes the diagnostic loading response of cartilage.
    Used to extract apparent stiffness C1C2 from the loading part of the first diagnostic cycle (Eqs. 1-2, Section 2.3); cartilage is poroviscoelastic, so a rate-independent hyperelastic fit may alias fluid-flow effects into material constants.
  • domain assumption Uniaxial stress and incompressibility hold in converting measured force and displacement to stress and stretch.
    Section 2.3 states 'assuming isotropic behavior, incompressibility, and approximating the stress to uniaxial in the depth direction'; lateral confinement and platen friction would bias fitted constants.
  • domain assumption Surface crack length measured from 2D laser microscopy images equals the true crack extension.
    Section 2.4 describes crack measurement on the articular surface using India ink and LEXT; subsurface or out-of-plane growth is not captured, and ink penetration may overstate length.
  • domain assumption The 15-minute recovery after fatigue loading fully separates irreversible compaction from recoverable deformation.
    Section 2.3 states the recovery time was based on prior work (Chawla et al., 2024); the thickness change is interpreted as irrecoverable damage.
  • ad hoc to paper The functional form of the damage relationships is a power law.
    Supplementary Figure S1: linear, exponential, and power-law fits were compared and the power law had the highest R², so it was selected; this choice is data-driven, not mechanistically derived.

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Pith. "Pith review of Influence of applied stress on energy dissipation and crack growth in articular cartilage." pith.science (2026). https://pith.science/paper/5LW6MJQ3

@misc{pith2026241115316,
  author       = {Pith},
  title        = {Pith review of: Influence of applied stress on energy dissipation and crack growth in articular cartilage},
  year         = {2026},
  howpublished = {\url{https://pith.science/paper/5LW6MJQ3}},
  note         = {Machine review of arXiv:2411.15316}
}
read the original abstract

Mechanical stress-induced damage to the articular cartilage can result in fracture imitation or significant tissue degeneration leading to osteoarthritis (OA) compromising joint mobility. Despite the clinical significance, a comprehensive understanding of the crack progression in cartilage damage remains elusive due to complex mechanical responses and variable initial crack geometry. This study investigated the impact of physiologically relevant stress levels, ranging from light-weight to high stress activities, on crack propagation in cartilage under compressive cyclic loading. Through empirical analysis, interconnections between localized damage (crack growth) and global damage (changes in material properties) across various levels of applied stress were established. Microscale cracks were nucleated in cylindrical cartilage plugs extracted from porcine patella specimens via microindentation and then subjected to controlled cyclic loading to examine changes in structural integrity, mechanical properties, and crack extension. Results demonstrated a decrease in cartilage thickness and apparent stiffness with increasing stress levels, indicative of bulk material damage. Dynamic mechanical properties such as energy dissipation and phase angle showed an overall reduction after fatigue loading. Crack growth followed an empirical law with increasing applied stress, reflective of greater mechanical damage at higher stress values. The findings of the study showed the interplay between global and local damage in cartilage under cyclic loading, suggesting insights into the fundamental changes occurring within the tissue. The outcomes of this investigation contributed to detailed understanding of the cartilage fatigue behavior through empirical laws and could potentially serve to prevent or delay tissue degeneration in OA.

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Works this paper leans on

36 extracted references · 26 canonical work pages

  1. [13]

    J Mech Behav Biomed Mater 75, 293–301

    Viscoelasticity of articular cartilage: Analysing the effect of induced stress and the restraint of bone in a dynamic environment. J Mech Behav Biomed Mater 75, 293–301. https://doi.org/https://doi.org/10.1016/j.jmbbm.2017.07.040 Li, Weichao, Qiao, K., Zheng, Y., Yan, Y., Xie, Y., Liu, Y., Ren, H.,

    work page doi:10.1016/j.jmbbm.2017.07.040 2017

  2. [14]

    J Mech Behav Biomed Mater 126, 105009

    Preparation, mechanical properties, fatigue and tribological behavior of double crosslinked high strength hydrogel. J Mech Behav Biomed Mater 126, 105009. https://doi.org/10.1016/j.jmbbm.2021.105009 Li, Weizheng, Zheng, S., Zou, X., Ren, Y., Liu, Z., Peng, W., Wang, X., Liu, D., Shen, Z., Hu, Y., Guo, J., Sun, Z., Yan, F.,

    arXiv 2021

  3. [15]

    Adv Funct Mater 32, 1–13

    Tough Hydrogels with Isotropic and Unprecedented Crack Propagation Resistance. Adv Funct Mater 32, 1–13. https://doi.org/10.1002/adfm.202207348 Liu, H.W.,

    work page doi:10.1002/adfm.202207348

  4. [28]

    Osteoarthritis Cartilage 23, 2252–2258

    Effect of the variation of loading frequency on surface failure of bovine articular cartilage. Osteoarthritis Cartilage 23, 2252–2258. https://doi.org/10.1016/j.joca.2015.06.002 Scetta, G., Selles, N., Heuillet, P., Ciccotti, M., Creton, C.,

    work page doi:10.1016/j.joca.2015.06.002 2015

  5. [29]

    Polym Test 97, 107140

    Cyclic fatigue failure of TPU using a crack propagation approach. Polym Test 97, 107140. https://doi.org/10.1016/j.polymertesting.2021.107140 Simon, S.R., Paul, I.L., Mansour, J., Munro, M., Abernethy, P.J., Radin, E.L.,

    arXiv 2021

  6. [33]

    Journal of biomechanical engineering 144, 1–11

    Effect of Articular Surface Compression on Cartilage Extracellular Matrix Deformation. Journal of biomechanical engineering 144, 1–11. https://doi.org/10.1115/1.4054108 Vazquez, K.J., Andreae, J.T., Henak, C.R.,

    work page doi:10.1115/1.4054108

  7. [34]

    J Mech Behav Biomed Mater 98, 262–267

    Cartilage-on-cartilage cyclic loading induces mechanical and structural damage. J Mech Behav Biomed Mater 98, 262–267. https://doi.org/https://doi.org/10.1016/j.jmbbm.2019.06.023 Veronda, D.R., Westmann, R.A.,

    work page doi:10.1016/j.jmbbm.2019.06.023 2019

  8. [37]

    Advanced Materials 2300937, 1–12

    Room-Temperature Self-Healing Soft Composite Network with Unprecedented Crack Propagation Resistance Enabled by a Supramolecular Assembled Lamellar Structure. Advanced Materials 2300937, 1–12. https://doi.org/10.1002/adma.202300937 Zhao, X., Wu, J., Zhou, Y., Pan, Y., Lu, T., Song, X., Hu, J.,

    work page doi:10.1002/adma.202300937

Show all 36 references
  1. [38]

    Extreme Mech Lett 46, 101320

    Fatigue behaviors of physical hydrogels based on hydrogen bonds. Extreme Mech Lett 46, 101320. https://doi.org/10.1016/j.eml.2021.101320 1 Supplementary Information for: Influence of applied stress on energy dissipation and crack growth in articular cartilage Dipul Chawla, Eri...

    2021

  2. [131]

    V., Adams, M.A., Sharif, M.,

    https://doi.org/10.1115/1.3005199 Clements, K.M., Bee, Z.C., Crossingham, G. V., Adams, M.A., Sharif, M.,

    doi

  3. [1953]

    The growth of fatigue cracks

    XCVIII. The growth of fatigue cracks. The London, Edinburgh, and Dublin Philosophical Magazine and Journal of Science 44, 925–938. https://doi.org/10.1080/14786440908521062 Hodge, W.A., Fijan, R.S., Carlson, K.L., Burgess, R.G., Harris, W.H., Mann, R.W.,

    doi

  4. [1958]

    Journal of the Mechanics and Physics of Solids 6, 92–110

    The propagation of fatigue cracks in sheet specimens. Journal of the Mechanics and Physics of Solids 6, 92–110. https://doi.org/https://doi.org/10.1016/0022-5096(58)90018-8 Gao, L.L., Qin, X.Y., Zhang, C.Q., Gao, H., Ge, H.Y., Zhang, X.Z.,

    doi

  5. [1963]

    Journal of Basic Engineering 85, 528–533

    A Critical Analysis of Crack Propagation Laws. Journal of Basic Engineering 85, 528–533. https://doi.org/10.1115/1.3656900 Park, S., Hung, C.T., Ateshian, G.A., 2004a. Mechanical response of bovine articular cartilage under dynamic unconfined compression loading at physiologic...

    doi

  6. [1970]

    J Biomech 3, 111–124

    Mechanical characterization of skin—Finite deformations. J Biomech 3, 111–124. https://doi.org/https://doi.org/10.1016/0021- 9290(70)90055-2 Weightman, B.,

    doi

  7. [1972]

    Annals of the rheumatic diseases 31, 457–464

    Light microscopy of Indian ink preparations of fibrillated cartilage. Annals of the rheumatic diseases 31, 457–464. https://doi.org/10.1136/ard.31.6.457 Morrison, J.B., 1970a. The mechanics of muscle function in locomotion. Journal of Biomechanics 3, 431–451. https://doi.org/h...

    doi

  8. [1973]

    Journal of biomechanics 6, 79–92

    Biomechanical analysis of knee flexion and extension. Journal of biomechanics 6, 79–92. https://doi.org/10.1016/0021-9290(73)90040-7 Torzilli, P.A., Allen, S.N.,

    doi

  9. [1976]

    Journal of Biomechanics 9, 193–200

    Tensile fatigue of human articular cartilage. Journal of Biomechanics 9, 193–200. https://doi.org/https://doi.org/10.1016/0021-9290(76)90004-X Xu, J.H., Li, Y.K., Liu, T., Wang, D., Sun, F.Y., Hu, P., Wang, L., Chen, J.Y., Wang, X. Bin, Yao, B.W., Fu, J.J.,

    doi

  10. [1977]

    Acta Orthopaedica 48, 511–516

    Load bearing characteristics of the patello- femoral joint. Acta Orthopaedica 48, 511–516. https://doi.org/10.3109/17453677708989740 McCormack, T., Mansour, J.M.,

    doi

  11. [1986]

    Proceedings of the National Academy of Sciences of the United States of America 83, 2879–2883

    Contact pressures in the human hip joint measured in vivo. Proceedings of the National Academy of Sciences of the United States of America 83, 2879–2883. https://doi.org/10.1073/pnas.83.9.2879 Hosseini, S.M., Wilson, W., Ito, K., Van Donkelaar, C.C.,

    doi

  12. [1990]

    Journal of Orthopaedic Research 8, 86–93

    The effect of shear fatigue on bovine articular cartilage. Journal of Orthopaedic Research 8, 86–93. https://doi.org/10.1002/jor.1100080111 Smidt, G.L.,

    doi

  13. [1992]

    Biomaterials 13, 67–97

    Cartilage and diarthrodial joints as paradigms for hierarchical materials and structures. Biomaterials 13, 67–97. https://doi.org/10.1016/0142-9612(92)90001-5 Neu, C.P., Hull, M.L., Walton, J.H.,

    doi

  14. [1998]

    Journal of biomechanics 31, 55–61

    Reduction in tensile strength of cartilage precedes surface damage under repeated compressive loading in vitro. Journal of biomechanics 31, 55–61. https://doi.org/10.1016/s0021-9290(97)00103-6 McEvily Jr, A.J., Illg, W.,

    doi

  15. [2001]

    https://doi.org/10.1053/joca.2000.0417 Edelsten, L., Jeffrey, J.E., Burgin, L

    How severe must repetitive loading be to kill chondrocytes in articular cartilage? Osteoarthritis and Cartilage 9, 499–507. https://doi.org/10.1053/joca.2000.0417 Edelsten, L., Jeffrey, J.E., Burgin, L. V., Aspden, R.M.,

  16. [2003]

    Clinical Biomechanics 18, 960–968

    Propagation of surface fissures in articular cartilage in response to cyclic loading in vitro. Clinical Biomechanics 18, 960–968. https://doi.org/10.1016/j.clinbiomech.2003.07.001 Lakes, R.S.,

    2003 doi

  17. [2010]

    Soft Matter 6, 5206–5212

    Viscoelastic deformation of articular cartilage during impact loading. Soft Matter 6, 5206–5212. https://doi.org/10.1039/c0sm00097c Frost, N.E., Dugdale, D.S.,

    doi

  18. [2012]

    J Biomech Eng 134, 11005

    FEBio: Finite Elements for Biomechanics. J Biomech Eng 134, 11005. https://doi.org/10.1115/1.4005694 Maier, F., Lewis, C.G., Pierce, D.M.,

    doi

  19. [2014]

    Cartilage 5, 97–106

    Effects of Freeze- Thaw Cycle with and without Proteolysis Inhibitors and Cryopreservant on the Biochemical and Biomechanical Properties of Articular Cartilage. Cartilage 5, 97–106. https://doi.org/10.1177/1947603513515998 Rattan, S., Li, L., Lau, H.K., Crosby, A.J., Kiick, K.L.,

    doi

  20. [2015]

    Materials Science and Engineering C 57, 371–377

    Ratcheting behavior of articular cartilage under cyclic unconfined compression. Materials Science and Engineering C 57, 371–377. https://doi.org/10.1016/j.msec.2015.07.061 Guterl, C.C., Hung, C.T., Ateshian, G.A.,

    2015 doi

  21. [2017]

    Journal of the Mechanical Behavior of Biomedical Materials 65, 734–742

    Cyclic loading of human articular cartilage: The transition from compaction to fatigue. Journal of the Mechanical Behavior of Biomedical Materials 65, 734–742. https://doi.org/10.1016/j.jmbbm.2016.09.040 Kerin, A.J., Coleman, A., Wisnom, M.R., Adams, M.A.,

    2016 doi

  22. [2018]

    International Journal of Fatigue 109, 60–69

    Fatigue damage in angle-ply GFRP laminates under tension-tension fatigue. International Journal of Fatigue 109, 60–69. https://doi.org/https://doi.org/10.1016/j.ijfatigue.2017.12.015 Mow, V.C., Ratcliffe, A., Robin Poole, A.,

    2017 doi

  23. [2019]

    Osteoarthritis and Cartilage 27, 810–822

    The evolving large-strain shear responses of progressively osteoarthritic human cartilage. Osteoarthritis and Cartilage 27, 810–822. https://doi.org/https://doi.org/10.1016/j.joca.2018.12.025 Matthews, L.S., Sonstegard, D.A., Henke, J.A.,

    2018 doi

  24. [2020]

    Extreme Mech Lett 34, 100601

    Interfacial fatigue fracture of tissue adhesive hydrogels. Extreme Mech Lett 34, 100601. https://doi.org/10.1016/j.eml.2019.100601 Paris, P., Erdogan, F.,

    2019

  25. [2021]

    Curr Protoc 1, e280

    Microindentation Technique to Create Localized Cartilage Microfractures. Curr Protoc 1, e280. https://doi.org/https://doi.org/10.1002/cpz1.280 Chawla, D., Thao, A.K., Eriten, M., Henak, C.R.,

    doi

  26. [2022]

    J Mech Behav Biomed Mater 136, 105467

    Effect of osmolarity and displacement rate on cartilage microfracture clusters failure into two regimes. J Mech Behav Biomed Mater 136, 105467. https://doi.org/https://doi.org/10.1016/j.jmbbm.2022.105467 Chawla, D., Han, G., Eriten, M., Henak, C.R.,

    2022

  27. [2023]

    Polymer Testing 117, 107875

    Study on the ratchetting behavior of glass fiber-reinforced epoxy composites: Experiment and theory. Polymer Testing 117, 107875. https://doi.org/https://doi.org/10.1016/j.polymertesting.2022.107875 Lyyra, T., Jurvelin, J., Pitkänen, P., Väätäinen, U., Kiviranta, I.,

    2022

  28. [3489]

    Effect of frequency on crack growth in articular cartilage

    https://doi.org/10.1039/c8sm00501j Sadeghi, H., Lawless, B.M., Espino, D.M., Shepherd, D.E.T., 2018a. Effect of frequency on crack growth in articular cartilage. J Mech Behav Biomed Mater 77, 40–46. https://doi.org/10.1016/j.jmbbm.2017.08.036 Sadeghi, H., Lawless, B.M., Espino...

    doi

Pith tools

Reviewed August 12, 2026 · model on record in the stance chip above.