Abstract
The load distribution among lumbar spinal structures—still an unanswered question—has been in the focus of this hybrid experimental and simulation study. First, the overall passive resistive torque-angle characteristics of healthy subjects’ lumbar spines during flexion–extension cycles in the sagittal plane were determined experimentally by use of a custom-made trunk-bending machine. Second, a forward dynamic computer model of the human body that incorporates a detailed lumbar spine was used to (1) simulate the human–machine interaction in accordance with the experiments and (2) validate the modeled properties of the load-bearing structures. Third, the computer model was used to predict the load distribution in the experimental situation among the implemented lumbar spine structures: muscle–tendon units, ligaments, intervertebral discs, and facet joints. Nine female and 10 male volunteers were investigated. Lumbar kinematics were measured with a marker-based infrared device. The lumbar flexion resistance was measured by the trunk-bending machine through strain gauges on the axes of the machine’s torque motors. Any lumbar muscle activity was excluded by simultaneous sEMG monitoring. A mathematical model was used to describe the nonlinear flexion characteristics. The subsequent extension branch of a flexion–extension torque–angle characteristic could be significantly distinguished from its flexion branch by the zero-torque lordosis angle shifted to lower values. A side finding was that the model values of ligament and passive muscle stiffnesses, extracted from well-established literature sources, had to be distinctly reduced in order to approach our measured overall lumbar stiffness values. Even after such parameter adjustment, the computer model still predicts too stiff lumbar spines in most cases in comparison with experimental data. A review of literature data reveals a deficient documentation of anatomical and mechanical parameters of spinal ligaments. For instance, rest lengths of ligaments—a very sensitive parameter for simulations—and cross-sectional areas turned out to be documented at best incompletely. Yet by now, our model well reproduces the literature data of measured pressure values within the lumbar disc at level L4/5. Stretch of the lumbar dorsal (passive) muscle and ligament structures as an inescapable response to flexion can fully explain the pressure values in the lumbar disc. Any further external forces like gravity, or any muscle activities, further increase the compressive load on a vertebral disc. The impact of daily or sportive movements on the loads of the spinal structures other than the disc cannot be predicted ad hoc, because, for example, the load distribution itself crucially determines the structures’ current lever arms. In summary, compressive loads on the vertebral discs are not the major determinants, and very likely also not the key indicators, of the load scenario in the lumbar spine. All other structures should be considered at least equally relevant in the future. Likewise, load indicators other than disc compression are advisable to turn attention to. Further, lumbar flexion is a self-contained factor of lumbar load. It may be worthwhile, to take more consciously care of trunk flexion during daily activities, for instance, regarding long-term effects like lasting repetitive flexions or sedentary postures.
Similar content being viewed by others
References
Adams MA, Hutton WC, Stott JRR (1980) The resistance to flexion of the lumbar intervertebral joint. Spine 5(3):245–253
Alexander RM (2002) Tendon elasticity and muscle function. Comp Biochem Physiol A 133(4):1001–1011
Arjmand N, Shirazi-Adl A (2006) Sensitivity of kinematics-based model predictions to optimization criteria in static lifting tasks. Med Eng Phys 28(6):504–514
Battie M, Videman T, Gibbons L, Fisher L, Manninen H, Gill K (1995) 1995 Volvo award in clinical sciences. determinants of lumbar disc degeneration a study relating lifetime exposures and magnetic resonance imaging findings in identical twins. Spine 20(24):2601–12
Battie MC, Videman T, Kaprio J, Gibbons LE, Gill K, Manninen H, Saarela J, Peltonen L (2009) The twin spine study: contributions to a changing view of disc degeneration. Spine J 9(1):47–59
Beaubien BP, Freeman AL, Buttermann GR (2016) Morphologic and biomechanical comparison of spinous processes and ligaments from scoliotic and kyphotic patients. J Biomech 49:216–221
Best R, Bartlett R, Morriss C (1993) A three-dimensional analysis of javelin throwing technique. J Sports Sci 11(4):315–328
Biewener AA, Blickhan R (1988) Kangaroo rat locomotion: design for elastic storage or acceleration? J Exp Biol 140:243–255
Biewener A, Blickhan R, Perry A, Heglund N, Taylor CR (1988) Muscle forces during locomotion in kangaroo rats: force platform and tendon buckle measurements compared. J Exp Biol 137:191–205
Botsford DJ, Esses SI, Ogilvie-Harris DJ (1994) In vivo diurnal variation in intervertebral disc volume and morphology. Spine 19(8):935–940
Chaffin DB (1969) A computerized biomechanical model: development of and use in studying gross body actions. J Biomech 2(4):429–441
Chazal J, Tanguy A, Bourges M, Gaurel G, Escande G, Guillot M, Vanneuville G (1985) Biomechanical properties of spinal ligaments and a histological study of the supraspinal ligament in traction. J Biomech 18(3):167–176
Cholewicki J, McGill SM (1996) Mechanical stability of the in vivo lumbar spine: implications for injury and chronic low back pain. Clin Biomech 11(1):1–15
Christensen KB, Günther M, Schmitt S, Siebert T (2017) Strain in shock-loaded skeletal muscle and the time scale of muscular wobbling mass dynamics. Sci Rep 7:13,266 (11pp)
Christophy M, Faruk Senan NA, Lotz JC, O’Reilly OM (2012) A musculoskeletal model for the lumbar spine. Biomech Model Mechanobiol 11(1–2):19–34
Close RI (1972) Dynamic properties of mammalian skeletal muscles. Physiol Rev 52:129–197
Damm N, Rockenfeller R, Gruber K (2019) Lumbar spinal ligament characteristics extracted from stepwise reduction experiments allow for preciser modeling than literature data. Biomech Model Mechanobiol. https://doi.org/10.1007/s10237-019-01259-6
De Luca CJ (1997) The use of surface electromyography in biomechanics. J Appl Biomech 13:135–163
Delp SL, Anderson FC, Arnold AS, Loan P, Habib A, John CT, Guendelman E, Thelen DG (2007) OpenSim: open-source software to create and analyze dynamic simulations of movement. IEEE Trans Biomed Eng BME–54(11):1940–1950
Denavit J, Hartenberg RS (2014) A kinematic notation for lower-pair mechanisms based on matrices. ASME J Appl Mech 22:215–221
Erskine RM, Jones DA, Maganaris CN, Degens H (2009) In vivo specific tension of the human quadriceps femoris muscle. Eur J Appl Physiol 106(6):827–838
Erskine RM, Jones DA, Williams AG, Stewart CE, Degens H (2010) Inter-individual variability in the adaptation of human muscle specific tension to progressive resistance training. Eur J Appl Physiol 110(6):1117–1125
Fukunaga T, Roy RR, Shellock FG, Hodgson JA, Edgerton VR (1996) Specific tension of human plantar flexors and dorsiflexors. J Appl Physiol 80(1):158–165
Gerritsen KGM, van den Bogert AJ, Nigg BM (1995) Direct dynamics simulation of the impact phase in heel-toe running. J Biomech 28(6):661–668
Ghezelbash F, Shirazi-Adl A, Arjmand N, El-Ouaaid Z, Plamondon A (2016) Subject-specific biomechanics of trunk: musculoskeletal scaling, internal loads and intradiscal pressure estimation. Biomech Model Mechanobiol 15(6):1699–1712
Gordon AM, Huxley AF, Julian FJ (1966) The variation in isometric tension with sarcomere length in vertebrate muscle fibers. J Physiol 184:170–192
Gracovetsky SA (1986) Determination of safe load. Br J Ind Med (Occup Environ Med) 43(2):120–133
Gracovetsky SA, Farfan HF, Lamy C (1977) Mathematical model of the lumbar spine using an optimized system to control muscles and ligaments. Orthop Clin N Am 8(1):135–153
Gracovetsky SA, Farfan HF, Lamy C (1981) The mechanism of the lumbar spine. Spine 6(3):249–262
Günther M, Ruder H (2003) Synthesis of two-dimensional human walking: a test of the \(\lambda\)-model. Biol Cybern 89(2):89–106
Günther M, Wagner H (2016) Dynamics of quiet human stance: computer simulations of a triple inverted pendulum model. Comput Methods Biomech Biomed Eng 19(8):819–834
Günther M, Schmitt S, Wank V (2007) High-frequency oscillations as a consequence of neglected serial damping in Hill-type muscle models. Biol Cybern 97(1):63–79
Haeufle DFB, Wochner I, Holzmüller D, Driess D, Günther M, Schmitt S (2020) Muscles reduce neuronal information load: quantification of control effort in biological vs robotic pointing and walking Frontiers in Robotics and AI -- Soft Robotics, (accepted)
Haeufle DFB, Günther M, Bayer A, Schmitt S (2014a) Hill-type muscle model with serial damping and eccentric force–velocity relation. J Biomech 47(6):1531–1536
Haeufle DFB, Günther M, Wunner G, Schmitt S (2014b) Quantifying control effort of biological and technical movements: an information-entropy-based approach. Phys Rev E 89(012):716. https://doi.org/10.1103/PhysRevE.89.012716
Hartenberg RS, Denavit J (1964) Kinematic synthesis of linkages. Series in mechanical engineering. McGraw-Hill, New York. https://ecommons.cornell.edu/handle/1813/58640
Hatze H (1977) A myocybernetic control model of skeletal muscle. Biol Cybern 25(2):103–119
Hatze H (1981) Myocybernetic control models of skeletal muscle: characteristics and applications. University of South Africa Press, Pretoria
Henze A (2002) Dreidimensionale biomechanische Modellierung und die Entwicklung eines Reglers zur Simulation zweibeinigen Gehens. PhD thesis, Eberhard-Karls-Universität, Tübingen, Germany
Hermens H, Freriks B, Merletti R, Stegeman D, Blok J, Rau G et al (1999) European recommendations for surface electromyography, results of the SENIAM project. Roessingh Research and Development b.v
Hill AV (1938) The heat of shortening and the dynamic constants of muscle. Proc R Soc B 126:136–195
Huijing PA, Baan GC (2008) Myofascial force transmission via extramuscular pathways occurs between antagonistic muscles. Cells Tissues Organs 188(4):400–414
Huijing PA, Baan GC, Rebel GT (1998) Non-myotendinous force transmission in rat extensor digitorum longus muscle. J Exp Biol 201(Pt 5):683–691
Jäger M, Luttmann A (1989) Biomechanical analysis and assessment of lumbar stress during load lifting using a dynamic 19-segment human model. Ergonomics 32(1):93–112
Karajan N, Röhrle O, Ehlers W, Schmitt S (2013) Linking continuous and discrete intervertebral disc models through homogenisation. Biomech Model Mechanobiol 12(3):453–466
Ker RF (2002) The implications of the adaptable fatigue quality of tendons for their construction, repair and function. Comp Biochem Physiol A 133(4):987–1000
Ker RF (2007) Mechanics of tendon, from an engineering perspective. Int J Fatigue 29(6):1001–1009
Kiefer A, Shirazi-Adl A, Parnianpour M (1997) Stability of the human spine in neutral postures. Eur Spine J 6(1):45–53
Kitazaki S, Griffin M (1997) A modal analysis of whole-body vertical vibration, using a finite element model of the human body. J Sound Vib 200(1):83–103
Legnani G, Casolo F, Righettini P, Zappa B (1996a) A homogeneous matrix approach to 3D kinematics and dynamics—I: theory. Mech Mach Theory 31(5):573–587
Legnani G, Casolo F, Righettini P, Zappa B (1996b) A homogeneous matrix approach to 3D kinematics and dynamics—II. Applications to chains of rigid bodies and serial manipulators. Mech Mach Theory 31(5):589–605
Lewandowski A (1982) Issues in model validation. Technical report, International Institute for Applied Systems Analysis (IIASA), Laxenburg, Austria: RR-82-037 (Reprint from ’Angewandte Systemanalyse’ 3(1): 2–11 (1982) Verlag TÜV Rheinland GmbH. Köln, Germany)
Liu G, Fekete G, Yang H, Ma J, Sun D, Mei Q, Gu Y (2019) Comparative 3-dimensional kinematic analysis of snatch technique between top-elite and sub-elite male weightlifters in 69-kg category. Heliyon 4(7):e00,658
Ma S, Zahalak GI (1991) A distribution-moment model of energetics in skeletal muscle. J Biomech 24(1):21–35
McGill SM, Norman RW (1985) Dynamically and statically determined low back moments during lifting. J Biomech 18(12):877–885
McGill S, Norman R (1986) Partitioning of the L4–L5 dynamic moment into disc, ligamentous, and muscular components during lifting. Spine 11(7):666–678
McGill SM, Norman RW (1987) Effects of an anatomically detailed erector spinae model on L4/L5 disc compression and shear. J Biomech 20(6):591–600
McGill S, Seguin J, Bennett G (1994) Passive stiffness of the lumbar torso in flexion, extension, lateral bending, and axial rotation. effect of belt wearing and breath holding. Spine (Phila Pa 1976) 19(6):696–704
McMahon TA (1984) Muscles, reflexes, and locomotion. Princeton University Press, Princeton
Miller CJ, Davidson LA (2013) The interplay between cell signalling and mechanics in developmental processes. Nat Rev Genet 14:733–744
Mohammadi Y, Arjmand N, Shirazi-Adl A (2015) Comparison of trunk muscle forces, spinal loads and stability estimated by one stability- and three EMG-assisted optimization approaches. Med Eng Phys 37(8):792–800
Mork PJ, Westgaard RH (2009) Back posture and low back muscle activity in female computer workers: a field study. Clin Biomech (Bristol, Avon) 24(2):169–175
Mörl F, Blickhan R (2006) Three-dimensional relation of skin markers to lumbar vertebrae of healthy subjects in different postures measured by open mri. Eur Spine J 15(6):742–751
Mörl F, Bradl I (2013) Lumbar posture and muscular activity while sitting during office work. J Electromyogr Kinesiol 23(2):362–368
Mörl F, Siebert T, Schmitt S, Blickhan R, Günther M (2012) Electro-mechanical delay in Hill-type muscle models. J Mech Med Biol 12(5):85–102
Mörl F, Anders C, Graßme R (2010) An easy and robust method for ecg artifact elimination of semg signals. In: ISEK
Nachemson AL (1960) Lumbar intradiscal pressure. Experimental studies on post-mortem material. Acta Orthop Scand 31(Suppl. 43):1–104
Nachemson AL (1963) The influence of spinal movements on the lumbar intradiscal pressure and on the tensile stresses in the annulus fibrosus. Acta Orthop Scand 33(1–4):183–207
Nachemson AL (1965) The effect of forward leaning on lumbar intradiscal pressure. Acta Orthop Scand 35(1–4):314–328
Nachemson AL (1966) The load on lumbar disks in different positions of the body. Clin Orthop Relat Res 45:107–122
Nachemson AL, Elfström GOSTA (1970) Intravital dynamic pressure measurements in lumbar discs: a study of common movements, maneuvers and exercise. Scand J Rehabil Med 1(Suppl 1):1–40
Nachemson AL, Morris JM (1964) In vivo measurements of intradiscal pressure. Discometry, a method for the determination of pressure in the lower lumbar discs. J Bone Joint Surg 46–A(5):1077–1092
Niven JE, Anderson JC, Laughlin SB (2007) Fly photoreceptors demonstrate energy-information trade-offs in neural coding. PLoS Biol 5(4):e116
Panjabi MM, White AA III (2001) Biomechanics in the musculoskeletal system. Churchill Livingstone, London
Panjabi MM, Goel VK, Takata K (1982) Physiologic strains in the lumbar spinal ligaments an in vitro biomechanical study 1981 volvo award in biomechanics. Spine (Phila Pa 1976) 7(3):192–203
Panjabi MM, Oxland T, Takata K, Goel V, Duranceau J, Krag M (1993) Articular facets of the human spine. Quantitative three-dimensional anatomy. Spine 18(10):1298–1310
Panjabi MM, Crisco JJ, Lydon C, Dvorak J (1998) The mechanical properties of human alar and transverse ligaments at slow and fast extension rates. Clin Biomech 13(2):112–120
Parkinson RJ, Beach TAC, Callaghan JP (2004) The time-varying response of the in vivo lumbar spine to dynamic repetitive flexion. Clin Biomech (Bristol, Avon) 19(4):330–336
Polly DW, Kilkelly FX, McHale KA, Asplund LM, Mulligan M, Chang AS (1996) Measurement of lumbar lordosis: evaluation of intraobserver, interobserver, and technique variability. Spine 21(13):1530–1535
Powell PL, Roy RR, Kanim P, Bello MA, Edgerton VR (1984) Predictability of skeletal muscle tension from architectural determinations in guinea pig hindlimbs. J Appl Physiol 57(6):1715–1721
Reconditi M (2006) Recent improvements in small angle X-ray diffraction for the study of muscle physiology. Rep Prog Phys 69(10):2709–2759
Robertson DJ, Von Forell GA, Alsup J, Bowden AE (2013) Thoracolumbar spinal ligaments exhibit negative and transverse pre-strain. J Mech Behav Biomed Mater 23:44–52
Rockenfeller R, Günther M (2017) Hill equation and Hatze’s muscle activation dynamics complement each other: enhanced pharmacological and physiological interpretability of modelled activity-pCa curves. J Theor Biol 431:11–24
Rockenfeller R, Günther M (2018) Inter-filament spacing mediates calcium binding to troponin: a simple geometric-mechanistic model explains the shift of force-length maxima with muscle activation. J Theor Biol 454:240–252
Rockenfeller R, Günther M, Schmitt S, Götz T (2015) Comparative sensitivity analysis of muscle activation dynamics. Comput Math Methods Med 585409:16
Rupp TK, Ehlers W, Karajan N, Günther M, Schmitt S (2015) A forward dynamics simulation of human lumbar spine flexion predicting the load sharing of intervertebral discs, ligaments, and muscles. Biomech Model Mechanobiol 14(5):1081–1105
Schmidt H, Galbusera F, Rohlmann A, Shirazi-Adl A (2013) What have we learned from finite element model studies of lumbar intervertebral discs in the past four decades? J Biomech 46(14):2342–2355
Schultz AB, Haderspeck K, Warwick DN, Portillo D (1983) Use of lumbar trunk muscles in isometric performance of mechanically complex standing tasks. J Orthop Res 1(1):77–91
Schultz AB, Haderspeck-Grib K, Sinkora G, Warwick DN (1985) Quantitative studies of the flexion-relaxation phenomenon in back muscles. J Orthop Res 3(2):189–197
Scott SH, Winter DA (1993) Biomechanical model of the human foot: kinematics and kinetics during the stance phase of walking. J Biomech 26(9):1091–1104
Seyfarth A, Blickhan R, van Leeuwen JL (2000) Optimum take-off techniques and muscle design for long jump. J Exp Biol 203:741–750
Seyfarth A, Günther M, Blickhan R (2001) Stable operation of an elastic three-segment leg. Biol Cybern 84(5):365–382. https://doi.org/10.1007/PL00007982
Shah S, Jayson MI, Hampson WG (1977) Low tension studies of collagen fibres from ligaments of the human spine. Ann Rheum Dis 36(2):139–145
Shampine LF, Gordon MK (1975) Computer solution of ordinary differential equations: the initial value problem. W.H. Freeman & Co., San Francisco
Shirazi-Adl A, Sadouk S, Parnianpour M, Pop D, El-Rich M (2002) Muscle force evaluation and the role of posture in human lumbar spine under compression. Eur Spine J 11(6):519–526
Siebert T, Till O, Blickhan R (2014) Work partitioning of transversally loaded muscle: experimentation and simulation. Comput Methods Biomech Biomed Eng 17(3):217–229
Siebert T, Stutzig N, Rode C (2018) A hill-type muscle model expansion accounting for effects of varying transverse muscle load. J Biomech 66:57–62
Thorpe SKS, Li Y, Crompton RH, Alexander RM (1998) Stresses in human leg muscles in running and jumping determined by force plate analysis and from published magnetic resonance images. J Exp Biol 201(Pt 1):63–70
van Soest A, Bobbert M (1993) The contribution of muscle properties in the control of explosive movements. Biol Cybern 69(3):195–204
Videman T, Battie MC, Gibbons LE, Manninen H, Gill K, Fisher LD, Koskenvuo M (1997) Lifetime exercise and disk degeneration: an mri study of monozygotic twins. Med Sci Sports Exerc 29(10):1350–6
Weis-Fogh T, Alexander RM (1977) The sustained power output obtainable from striated muscle. In: Pedley TJ (ed) Scale effects in animal locomotion. Academic Press, London, pp 511–526
White AA III, Panjabi MM (1990) Clinical biomechanics of the spine, 2nd edn. Lippincott Williams & Wilkins, Philadelphia
Wilke HJ, Neef P, Caimi M, Hoogland T, Claes LE (1999) New in vivo measurements of pressures in the intervertebral disc in daily life. Spine 24(8):755–762
Wilke HJ, Neef P, Hinz B, Seidel H, Claes LE (2001) Intradiscal pressure together with anthropometric data: a data set for the validation of models. Clin Biomech 16(Suppl. 1):S111–S126
Yahia L, Audet J, Drouin G (1991) Rheological properties of the human lumbar spine ligaments. J Biomed Eng 13(5):399–406
Acknowledgements
This work was funded by the German Social Accident Insurance (DGUV, Glinkastraße 40, 10117 Berlin, Germany) project FP-0390 titled ‘Direct and indirect effects of mechanical creep of passive structures on the load sharing in the human spine and on risk of working tasks’. Michael Günther was supported by “Deutsche Gesetzliche Unfallversicherung” (DGUV) project “Wirbelsäulenmodell passive Strukturen” and “Deutsche Forschungsgemeinschaft” (DFG, German Research Foundation) project SCHM2392/5-2, all granted to Syn Schmitt. Additionally, this work was funded by “Deutsche Forschungsgemeinschaft” (DFG, German Research Foundation) under Germanys’ Excellence Strategy—EXC 2075–390740016. We like to thank the unknown reviewer for the appreciative and motivating review. Further thanks to the editorial board for down-to-earth handling of the manuscript.
Author information
Authors and Affiliations
Corresponding author
Ethics declarations
Conflict of interest
The authors declare that they have no conflicts of interest.
Additional information
Publisher's Note
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Appendix
Appendix
1.1 The implemented point-to-plane contact elements (PPCEs)
There are six PPCEs at the HAUT body. Two are located at the HAUT’s right side and model the trunk of the subjects, which lie on their right sides in the experiment, being supported by the mobile table part of the machine. In these two PPCEs, their plane is fixed to the table, with their normal vector pointing upwards (to HAUT), while the contact points are fixed on HAUT: at shoulder height and width, each one 4 cm dorsally and ventrally, respectively.
Four further PPCEs are introduced to model the fastening of the subject’s trunk to the shoulder cushion roll by the fixation belt, both on their part fixed to the mobile table (Fig. 1b). The belt is for pulling the trunk back to the roll in case the trunk would tilt away from the roll down to the surface of the mobile table. The roll–shoulder interaction is implemented by two of these PPCEs which are fixed to the HAUT’s backside: their plane in common is located 5 cm dorsally from the HAUT’s centre of mass (COM) and its normal vector points dorsally. The belt fastening is simply implemented by the another PPCEs with a second plane in common. This plane is likewise fixed on the HAUT’s backside, however, located 6 cm dorsally from HAUT’s COM, and its normal vector points ventrally.
Each the dorsal and ventral PPCE plane on HAUT can interact with both a lower (1.5 cm above table surface) and an upper (33.5 cm above table surface) contact point locating the shoulder cushion roll. The modeled roll is fixed on the machine’s mobile table part (Fig. 1a) a distance of 18 cm away (at \(\mathcal {K}\)) from the axis \(\mathcal {S}\) of the frictionless hinge joint by which the mobile table is linked to the lever construction A-B-\(\mathcal {S}\) which is again linked by hinge A to the machine’s base table part. The latter is eventually fixed to the ground. The two possible contact points on the roll are chosen so as to enable its contacting with HAUT in the regions nearby the heights of both shoulder joints.
To sum shoulder fixation up, two PPCEs support the right shoulder region of HAUT against gravity and another four PPCEs make a ‘rail’ gap for HAUT of 1 cm width, roughly representing a subject’s trunk backside supported by the cushion roll and its front side being pulled back to the cushion roll by the fixation belt. During flexion movements (forward rotations), two PPCEs guide the HAUT body mainly by normal pressure to the trunk’s backside—partly superposed by reversible tangential stick-slip interaction. Enforced pronounced HAUT backward rotations (trunk overextension) can be enforced by the A-B-\(\mathcal {S}\) lever arm system around the machine’s motor axis \(\mathcal {A}\) pulling the HAUT shoulder region backwards by means of the fifth and sixth PPCEs.
Like the shoulder region is ‘railed’ by PPCEs, the pelvis is ‘clamped’ to the base table by another four PPCEs in accordance to the experiments (Fig. 1b). Their contact points are fixed to the base table, all located 5 cm footward of the axis \(\mathcal {A}\) and either 6 cm or 30 cm, respectively, above the base table plane. The corresponding planes fixed to the pelvis are located such that all four PPCEs are usually strained by few millimeters: in the model, the pelvis is thus viscoelastically ‘clamped’. Similar to HAUT at the shoulder cushion roll, both model’s shanks are also ‘railed’ by four further PPCEs. In the shanks, however, the ‘railing’ planes are fixed to the base table instead of the bodies, in parallel to the posterior edge of the base table where the model is lying on its left side on. The contact points are fixed to the shanks at the positions of their respective COM positions in caudal–cranial direction.
Eventually, the pelvis on its right, lying side, the right thigh, the right shank, and the right foot are supported against gravity by altogether six PPCEs of which their planes, like at the right shoulder height of HAUT, all represent the surface of the base table. From proximal to distal (numbers given as distances from the body’s respective COM), the contact points fixed to the bodies are located on the pelvis at 17.5 cm laterally below its COM and 5.8 cm cranially, on the thigh at 6 cm laterally and 13.5 cm proximally as well as 4.5 cm laterally and 25.5 cm distally, on the shank at 4.5 cm laterally and 13.5 cm proximally as well as 4.5 cm laterally and 25.5 cm distally, and on the foot 4.5 cm laterally at about the heel position.
All main parameters of the PPCEs were chosen the same: normal stiffness as \(1.5\times 10^{4}\) N m\(^{-1}\), the nonlinear normal damping factor according to Eq. (3) as \(d_{PPCE,damp}\) = 1 s m\(^{-1}\), tangential (stick) stiffness as \(2.0\times 10^{3}\) N m\(^{-1}\), the coefficients of static and kinetic (sliding, slipping) friction as \(\mu _{s}\) = 0.8 and \(\mu _{k}\) = 0.7, respectively, and the critical velocity for the slip–stick transition as \(v_{crit}\) = 1 cm s\(^{-1}\).
Rights and permissions
About this article
Cite this article
Mörl, F., Günther, M., Riede, J.M. et al. Loads distributed in vivo among vertebrae, muscles, spinal ligaments, and intervertebral discs in a passively flexed lumbar spine. Biomech Model Mechanobiol 19, 2015–2047 (2020). https://doi.org/10.1007/s10237-020-01322-7
Received:
Accepted:
Published:
Issue Date:
DOI: https://doi.org/10.1007/s10237-020-01322-7