Axial stiffness of human lumbar motion segments, force dependence
Introduction
The mechanical response of the spine to different loading situations is one of the keys to understanding, as well as predicting, its behaviour. The influence of factors like load history, exposure time, as well as total load has to be considered.
Measurements of axial deformation due to loading (Dieen and Toussaint, 1993; Kulak et al., 1975, Kulak et al., 1976) have been performed in vitro as well as in vivo in order to establish the relation between force and deformation. Stiffness, generally defined as the capability of a structure to withstand load, is one of the parameters that has been determined in a number of tests. Age, mineral content and strain rate are some of the factors that have been shown to influence stiffness (Kazarian and Graves, 1977; Koeller et al., 1986; Neumann et al., 1994). Most of the reported stiffness values have been derived during semi-static loading conditions. To understand better the dynamic properties of the functional spinal unit (FSU), it is essential to determine stiffness for physiological loads (i.e. loads that might be experienced in daily life). Typical force– deformation curves have traditionally been divided into three different regions: toe, elastic and yield. The toe region has been designated by Panjabi as the ‘Neutral zone’. In this region, even small forces can cause relatively large motions. Examination of force–deformation curves reveals that the stiffness is increasing with load (Fig. 1 shows the general form of the curve).
The large variation in reported stiffness values is to some extent explained by biological variations, but is also due to different definitions of stiffness: mean, ultimate (slope from origo to the failure point in the force– deformation curve), elastic and tangential stiffness. The functional spinal unit is composed of several tissues: ligaments, cartilage, intervertebral disc and bone structure, each structure having individual properties (Burstein and Frankel, 1968; Markolf and Morris, 1974; McNally and Arridge, 1995; Shah et al., 1977; Yoganandan et al., 1989aYoganandan et al., 1989b). The influence of each component in the overall performance of the FSU is hitherto not fully understood.Neumann et al. (1994) reported a non-linear behaviour of ligaments as did Viidik, 1968, Viidik, 1980 in studies of collagenous tissue. Isolated disc structures such as the annulus exhibit a predominantly non-linear behaviour as demonstrated by Wu and Yao (1976) and Skaggs et al. (1994). Typical force–deformation curves from intact vertebrae as well as vertebral trabecular bone show a progressively increasing stiffness (Hansson et al., 1980; Hansson et al., 1986).Linde and Hvid (1987) stated in a study of trabecular bone stiffness that ‘it is doubtful if a linear part exist at all’. They believed that for practical reasons this specific interval could be regarded as linear but it is only a matter of resolution and number of specimens to demonstrate that this part is also non-linear.
In the present study, data have been fitted to a simple non-linear model. The aim has been to determine the axial stiffness of the FSU and its relation to the applied load. In order to analyse various physiological loading conditions, a simple model is proposed that, with a reasonably good accuracy, permits prediction of spinal stiffness over a range where the maximum is about three times the minimum load. The relevance of this model is in situations where the FSU can be treated as a ‘black box’ and its internal mechanisms are not the main concern (e.g. modelling of the whole spine).
We have also tried to relate the parameters from the load-stiffness fit to the following factors:
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Age.
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Amount of bone mineral (BMC).
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Degree of disc degeneration.
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Morphometry (the geometry of the FSU).
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Position in the time–deflection curve (degree of creep).
Section snippets
Materials and methods
Six lumbar functional spinal units (FSU) obtained from four subjects were tested. Each FSU consisted of one intact disc, ligaments and two adjacent vertebrae. Data for each FSU can be found in Table 1. The degeneration of the discs was classified according to the visual four-graded scale by Friberg and Hirsch (1949).
The bone mineral in each vertebra was determined with dual photon absorptiometry (DPA) technique and expressed in g cm-1. After excision of the soft tissue except the disc and
Results
The relationship between k2 and force for all six tests can be seen in Fig. 5. A close linear relationship is suggested for each FSU. An overall fit of k2 as a function of force (r2=0.59) gives the following values: kl= 0.81 kN mm-1 and kn=2.7 kN mm-2. A relationship between k2l and BMC was also found:(significant at the 5% level, r2=0.73).
Age and degeneration had no significant influence upon stiffness. This is in agreement with findings of dynamic stiffness determined during
Discussion
The non-linear behaviour of the motion segment within the load levels studied has been reported by a number of authors (Asano et al., 1992; Brown et al., 1957; Hirsch, 1955; Hutton et al., 1979; Kasra et al., 1992; Koreska et al., 1977; Kulak et al., 1976, Kulak et al., 1975; Yoganandan et al., 1989a, Yoganandan et al., 1989b). So far, no mathematical expression accounting for the non-linearity has been generally accepted. The proposed model describes, in agreement with Panjabi’s neutral zone
Conclusions
The method of using impacts superimposed to a static load allows for evaluation of short time as well as long time viscoelastic properties and has proven useful. A non-linear behaviour of the FSU stiffness is apparent. This implies that linear Maxwell and Kelvin units are not appropriate in modelling, except in narrow force range.
Acknowledgements
The authors wish to acknowledge the support from the Swedish Council for Work Life Research and Ingabritt and Arne Lundberg’s Research Foundation. We also wish to thank Allison M. Kaigle, Ph.D., for valuable comments on the manuscript.
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