Influence of Stress Magnitude on Water Loss and Chondrocyte Viability in Impacted Articular Cartilage

[+] Author and Article Information
Dejan Milentijevic, David L. Helfet, Peter A. Torzilli

Laboratory for Soft Tissue Research, Hospital for Special Surgery, Center for Biomedical Engineering, City University of New York, New York, NY

J Biomech Eng 125(5), 594-601 (Oct 09, 2003) (8 pages) doi:10.1115/1.1610021 History: Received June 26, 2002; Revised May 21, 2003; Online October 09, 2003
Copyright © 2003 by ASME
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Freeman, M. A. R., 1979, “The Matrix,” Adult Articular Catilage, Pitman Medical, Kent, UK, pp. 1–96.
Ateshian,  G. A., Lai,  W. M., Zhu,  W. B., and Mow,  V. C., 1994, “An Asymptotic Solution for the Contact of Two Biphasic Cartilage Layers,” J. Biomech., 27(11), pp. 1347–1360.
Ateshian,  G. A., and Wang,  H., 1995, “A Theoretical Solution for the Frictionless Rolling Contact of Cylindrical Biphasic Articular Cartilage Layers [See Comments],” J. Biomech., 28(11), pp. 1341–1355.
Soltz,  M. A., and Ateshian,  G. A., 1998, “Experimental Verification and Theoretical Prediction of Cartilage Interstitial Fluid Pressurization at an Impermeable Contact Interface in Confined Compression,” J. Biomech., 31(10), pp. 927–934.
Armstrong,  C. G., Lai,  W. M., and Mow,  V. C., 1984, “An Analysis of the Unconfined Compression of Articular Cartilage,” J. Biomech. Eng., 106(2), pp. 165–173.
Suh,  J. K., and Spilker,  R. L., 1994, “Indentation Analysis of Biphasic Articular Cartilage: Nonlinear Phenomena Under Finite Deformation,” J. Biomech. Eng., 116(1), pp. 1–9.
Mow,  V. C., Kuei,  S. C., Lai,  W. M., and Armstrong,  C. G., 1980, “Biphasic Creep and Stress Relaxation of Articular Cartilage in Compression? Theory and Experiments,” J. Biomech. Eng., 102(1), pp. 73–84.
Suh,  J. K., and Bai,  S., 1998, “Finite Element Formulation of Biphasic Poroviscoelastic Model for Articular Cartilage,” J. Biomech. Eng., 120(2), pp. 195–201.
Repo,  R. U., and Finlay,  J. B., 1977, “Survival of Articular Cartilage After Controlled Impact,” J. Bone Jt. Surg., 59(8), pp. 1068–1076.
Jeffrey,  J. E., Gregory,  D. W., and Aspden,  R. M., 1995, “Matrix Damage and Chondrocyte Viability Following a Single Impact Load on Articular Cartilage,” Arch. Biochem. Biophys., 322(1), pp. 87–96.
Torzilli,  P. A., Grigiene,  R., Borrelli,  J., and Helfet,  D. L., 1999, “Effect of Impact Load on Articular Cartilage: Cell Metabolism and Viability, and Matrix Water Content,” J. Biomech. Eng., 121(5), pp. 433–441.
Ewers,  B. J., Dvoracek-Driksna,  D., Orth,  M. W., and Haut,  R. C., 2001, “The Extent of Matrix Damage and Chondrocyte Death in Mechanically Traumatized Articular Cartilage Explants Depends on Rate of Loading,” J. Orthop. Res., 19(5), pp. 779–784.
Torzilli, P. A., Askari, E., and Jenkins, J., 1990, “Water Content and Solute Diffusion Properties of Articular Cartilage,” Biomechanics of Diarthroidial Joints, Springer-Verlag, New York, pp. 363–390.
Schinagl,  R. M., Gurskis,  D., Chen,  A. C., and Sah,  R. L., 1997, “Depth-Dependent Confined Compression Modulus of Full-Thickness Bovine Articular Cartilage,” J. Orthop. Res., 15(4), pp. 499–506.
Chen,  A. C., Bae,  W. C., Schinagl,  R. M., and Sah,  R. L., 2001, “Depth- and Strain-Dependent Mechanical and Electromechanical Properties of Full-Thickness Bovine Articular Cartilage in Confined Compression,” J. Biomech., 34(1), pp. 1–12.
Chen,  S. S., Falcovitz,  Y. H., Schneiderman,  R., Maroudas,  A., and Sah,  R. L., 2001, “Depth-Dependent Compressive Properties of Normal Aged Human Femoral Head Articular Cartilage: Relationship to Fixed Charge Density,” Osteoarthritis Cartilage, 9(6), pp. 561–569.
O’Connor,  P., Orford,  C. R., and Gardner,  D. L., 1988, “Differential Response to Compressive Loads of Zones of Canine Hyaline Articular Cartilage: Micromechanical, Light and Electron Microscopic Studies,” Ann. Rheum. Dis., 47(5), pp. 414–420.
Rieppo, J., Laasanen, M. S., Korhonen, R. K., and Toyras, J., 2001, “Depth-Dependent Mechanical Properties of Bovine Patellar Cartilage,” Proceedings 47th Annual Meeting of the Orthopaedic Research Society, San Francisco, CA, p. 440.
Maroudas,  A., Muir,  H., and Wingham,  J., 1969, “The Correlation of Fixed Negative Charge With Glycosaminoglycan Content of Human Articular Cartilage,” Biochem. Biophys Acta,177(3), pp. 492–500.
Brocklehurst,  R., Bayliss,  M. T., Maroudas,  A., Coysh,  H. L., Freeman,  M. A., Revell,  P. A., and Ali,  S. Y., 1984, “The Composition of Normal and Osteoarthritic Articular Cartilage From Human Knee Joints. With Special Reference to Unicompartmental Replacement and Osteotomy of the Knee,” J. Bone Jt. Surg., Am. Vol., 66(1), pp. 95–106.
Lai,  W. M., Mow,  V. C., and Roth,  V., 1981, “Effects of Nonlinear Strain-Dependent Permeability and Rate of Compression on the Stress Behavior of Articular Cartilage,” J. Biomech. Eng., 103(2), pp. 61–66.
Buschmann,  M. D., Soulhat,  J., Shirazi-Adl,  A., Jurvelin,  J. S., and Hunziker,  E. B., 1998, “Confined Compression of Articular Cartilage: Linearity in Ramp and Sinusoidal Tests and the Importance of Interdigitation and Incomplete Confinement,” J. Biomech., 31(2), pp. 171–178.
Guilak,  F., Jones,  W. R., Ting-Beall,  H. P., and Lee,  G. M., 1999, “The Deformation Behavior and Mechanical Properties of Chondrocytes in Articular Cartilage,” Osteoarthritis Cartilage, 7(1), pp. 59–70.
Bush,  P. G., and Hall,  A. C., 2001, “The Osmotic Sensitivity of Isolated and In Situ Bovine Articular Chondrocytes,” J. Orthop. Res., 19(5), pp. 768–778.
Kobayashi,  S., Yonekubo,  S., and Kurogouchi,  Y., 1996, “Cryoscanning Electron Microscopy of Loaded Articular Cartilage With Special Reference to the Surface Amorphous Layer,” J. Anat., 188(Pt 2), pp. 311–322.
Basser,  P. J., Schneiderman,  R., Bank,  R. A., Wachtel,  E., and Maroudas,  A., 1998, “Mechanical Properties of the Collagen Network in Human Articular Cartilage as Measured by Osmotic Stress Technique,” Arch. Biochem. Biophys., 351(2), pp. 207–219.
Wang,  C. C., Hung,  C. T., and Mow,  V. C., 2001, “An Analysis of the Effects of Depth-Dependent Aggregate Modulus on Articular Cartilage Stress-Relaxation Behavior in Compression,” J. Biomech., 34(1), pp. 75–84.
Silyn-Roberts,  H., and Broom,  N. D., 1990, “Fracture Behavior of Cartilage-on-Bone in Response to Repeated Impact Loading,” Connect. Tissue Res., 24(2), pp. 143–156.
Afoke,  N. Y., Byers,  P. D., and Hutton,  W. C., 1987, “Contact Pressures in the Human Hip Joint,” J. Bone Jt. Surg., Br. Vol., 69(4), pp. 536–541.
Hodge,  W. A., Carlson,  K. L., Fijan,  R. S., Burgess,  R. G., Riley,  P. O., Harris,  W. H., and Mann,  R. W., 1989, “Contact Pressures From an Instrumented Hip Endoprosthesis,” J. Bone Jt. Surg., Am. Vol., 71(9), pp. 1378–1386.
Urban,  J. P., 1994, “The Chondrocyte: A Cell Under Pressure,” Br. J. Rheumatol., 33(10), pp. 901–908.
Takahashi,  K., Kubo,  T., Arai,  Y., Kitajima,  I., Takigawa,  M., Imanishi,  J., and Hirasawa,  Y., 1998, “Hydrostatic Pressure Induces Expression of Interleukin 6 and Tumour Necrosis Factor Alpha Mrnas in a Chondrocyte-Like Cell Line,” Ann. Rheum. Dis., 57(4), pp. 231–236.
Hall,  A. C., 1999, “Differential Effects of Hydrostatic Pressure on Cation Transport Pathways of Isolated Articular Chondrocytes,” J. Cell Physiol., 178(2), pp. 197–204.
Radin,  E. L., Paul,  I. L., and Lowy,  M., 1970, “A Comparison of the Dynamic Force Transmitting Properties of Subchondral Bone and Articular Cartilage,” J. Bone Jt. Surg., Am. Vol., 52(3), pp. 444–456.
Oloyede,  A., Flachsmann,  R., and Broom,  N. D., 1992, “The Dramatic Influence of Loading Velocity on the Compressive Response of Articular Cartilage,” Connect. Tissue Res., 27pp. (4) 211–224.


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Schematic diagram of the impact test system
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Wet weight loss (top) and percent wet weight loss (bottom) as a function of maximum strain. The amount of water loss increased nonlinearly with increasing matrix strain (mean ±95% confidence interval). Water loss in control (unloaded) explants is also shown (mean±sd).
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Cell viability in explants which were impacted with peak stresses of 0, 15, 30, and 60 MPa. Cell death (red stain) initiated at the articular surface (top of figure) and increased in depth (percent thickness and absolute) with increasing stress magnitude. Viable cells are shown in green.
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Depth of cell death from the articular surface in explants impacted with peak stresses from 10 to 60 MPa. The amount of cell death increased from the surface with increasing peak stress. Percent cell death: solid line ±95% CI, • data points; absolute depth: dashed line ±95% CI, data points not shown.
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Depth of cell death from the articular surface in explants as a function of the maximum strain. The amount of cell death increased from the surface with increasing strain. Percent cell death: solid line ±95% CI, • data points; absolute depth: dashed line ±95% CI, data points not shown.
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Effect of explant orientation on water loss in explants impacted with 30 MPa at 350 MPa/s. A greater amount of water was lost from the articular surface loaded explants as compared to the deep-zone loaded explants (p<0.01). Both impacted groups lost a significant amount of water compared to the unloaded group (p<0.001).
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Effect of maximum strain and explant orientation on wet weight loss in explants impacted with 30 MPa at 350 MPa/s. Water loss from the articular surface (solid line, ▴ data points) increased nonlinearly with strain, while water loss from the deep zone (dashed line, • data points) was constant (independent of strain). Water loss in control (unloaded) explants is also shown (▪ mean±sd).
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Photograph of impact test system showing the impactor (air cylinder, load cell, load platen) mounted within the rigid frame. Insert: the solid, nonporous load platen is mounted to a piezoelectric load cell. Matrix compression is measured by the LVDT as it contacts the flat plate above the load cell.
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Schematic drawings of the different confined compression configurations used to measure water displacement (arrows indicate direction of water flow). 3a) Articular Surface Loading (ASL): The explant is positioned in the confining chamber with its articular surface against the porous filter. 3b) Deep Zone Loading (DZL): The cut-surface (deep zone) is placed against the porous filter. 3c) Paired Loading: Two explants are positioned with their surfaces facing each other, with one having its cut-surface against the nonporous load platen and one against the porous filter.
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Typical stress-strain response for an impacted explant, in this case to a peak stress of 45 MPa at a 350 MPa/s stress rate. There was always an initial toe region (section A) followed by a linear region (section B). The dynamic impact modulus (DIM) was calculated from the slope of the linear region. Some specimens exhibited a nonlinear response for strains above ∼20% (section C). After reaching the peak stress, the explant was rapidly unloaded (section D) and did not appear to immediately return to its initial thickness (section E).
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Wet weight loss (top) and percent wet weight loss (bottom) as a function of applied stress. The amount of water loss increased linearly with increasing peak stress (mean ±95% confidence interval). Water loss in control (unloaded) explants is also shown (mean±sd).



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