High pressures and asymmetrical stresses in the scoliotic disc in the absence of muscle loading
© Meir et al; licensee BioMed Central Ltd. 2007
Received: 06 October 2006
Accepted: 24 February 2007
Published: 1 December 2007
Loads acting on scoliotic spines are thought to be asymmetric and involved in progression of the scoliotic deformity; abnormal loading patterns lead to changes in bone and disc cell activity and hence to vertebral body and disc wedging. At present however there are no direct measurements of intradiscal stresses or pressures in scoliotic spines. The aim of this study was to obtain quantitative measurements of the intradiscal stress environment in scoliotic intervertebral discs and to determine if loads acting across the scoliotic spine are asymmetric. We performed in vivo measurements of stresses across the intervertebral disc in patients with scoliosis, both parallel (termed horizontal) and perpendicular (termed vertical) to the end plate, using a side mounted pressure transducer (stress profilometry)
Stress profilometry was used to measure horizontal and vertical stresses at 5 mm intervals across 25 intervertebral discs of 7 scoliotic patients during anterior reconstructive surgery. A state of hydrostatic pressure was defined by identical horizontal and vertical stresses for at least two consecutive readings. Results were compared with similar stress profiles measured during surgery across 10 discs of 4 spines with no lateral curvature and with data from the literature.
Profiles across scoliotic discs were very different from those of normal, young, healthy discs of equivalent age previously presented in the literature. Hydrostatic pressure regions were only seen in 14/25 discs, extended only over a short distance. Non-scoliotic discs of equivalent age would be expected to show large centrally placed hydrostatic nuclear regions in all discs. Mean pressures were significantly greater (0.25 MPa) than those measured in other anaesthetised patients (<0.07 MPa). A stress peak was seen in the concave annulus in 13/25 discs. Stresses in the concave annulus were greater than in the convex annulus indicating asymmetric loading in these anaesthetised, recumbent patients.
Intradiscal pressures and stresses in scoliotic discs are abnormal, asymmetrical and high in magnitude even in the absence of significant applied muscle loading. The origin of these abnormal stresses is unclear.
The aim of this study was to obtain measurements of pressures and stresses in the intervertebral discs of scoliotic patients in order to try to prove the hypothesis that asymmetrical loading was present in the scoliotic spine and hence could realistically be involved in curve progression. We were also very interested in the stress environment of the intervertebral disc in scoliosis in general. We considered that recording from discs prior to excision during anterior scoliosis reconstructive surgery involved minimal additional patient risk. However, in anaesthetised patients with additional muscle relaxation (an essential aspect of the anaesthetic procedure) no loading due to muscle activity is present. We therefore were unsure if our approach would show any meaningful results.
Previous authors have theorised about the biomechanical role of asymmetrical loading in progression of the scoliotic deformity [1–3]. Non-operative treatments such as bracing are designed to counteract these loads [4–6]. The majority of studies have focused on the musculature as the origin of this loading asymmetry. Electromyographic measurements have demonstrated differences in muscle activity between the convex and concave sides of the spine [7–9]. Muscle biopsies additionally find a significantly lower percentage of Type I fibers in the multifidus muscle on the concave side, particularly at the curve apex and also in the superficial muscles above and below the apex [10–13].
The cellular mechanisms by which abnormal loading may generate deformity has been shown previously in cell culture and in animal models. Cells of bone and disc are very responsive to mechanical stress[14, 15], with high loads inhibiting longitudinal growth [16–18]. An asymmetric load may thus lead to asymmetrical longitudinal growth and hence wedging of the vertebral bodies and intervertebral disc. Scoliotic-like deformities have also been produced in otherwise healthy animals by applying asymmetrical loads across the spine [19–23]. These loads differentially affect longitudinal bone growth. The disc remodels and becomes wedged and distorted. Thus asymmetrical loading could lead to permanent changes in vertebral bodies and discs and hence contribute to progression of the scoliotic deformity.
Most of the information on loads acting on the scoliotic spine is derived from measurements of changes in spinal morphology and from modelling[3, 24]. There have however been no direct measures of loading asymmetry. We have therefore used stress profilometry  to directly measure pressure and stress profiles across scoliotic discs during anterior reconstructive surgery. This technique involves introducing a miniature pressure transducer, side mounted on a needle, across the disc transversely. Two linear profiles of stresses are measuring with the transducer orientated parallel (termed horizontal) and perpendicular (termed vertical) to the endplate.
Materials and methods
Details of Scoliotic patients examined.
Apical disc level
Disc levels recorded
T11/12, T12/L1, L1/2
T11/12, T12/L1, L1/2
T12/L1, L1/2, L2/3, L3/4
T10/11, T11/12, T12/L1
T9/10, T10/11, T11/12, T12/L1.
T11/12, T12/L1, L1/2, L2/3, L3/4
Details of non-Scoliotic Patients (Control) examined.
Disc levels recorded
Fibrillary Astrocytoma. Paraplegia 3 years.
T11/12, T12/L1, L1/2
Idiopathic. Curve present since age 3.
T3/4, T4/5, T6/7, T7/8
Discogenic back pain L 4/5
14 y low back pain. Provocative discography positive L4/5
Discogenic back pain L4/5, L5/S1
Low back and right leg pain. MRI showed mild degeneration L4/5 and 5/S1.
The pressure transducer used in the study was the same type as that used previously for pressure profile measurements [25–28]. It has been shown to give reproducible results when used in human intervertebral discs[25, 26]. The device consisted of a pressure-sensing diaphragm, side mounted 3 mm from the tip of a 10 cm long, 1.33 mm diameter blunt-ended surgical steel needle (AISI type 304, Gaeltec Ltd, Dunvegan, Isle of Skye, UK). A millimetre scale marked additionally at centimetre intervals was etched onto the needle to allow measurement of depth of penetration of the needle. A small metal bar was added to the base of the needle to enable the surgeon to orientate the transducer diaphragm. The transducer was connected to an isolated amplifier (ADInstruments, Oxford UK) which as well as amplifying the signal from the sensor also provided a 5 V excitation signal. A laptop computer running Chart software (ADInstruments, Oxford UK) interfaced with a PowerLab data acquisition system (ADInstruments, Oxford UK) was used to record and analyse the data.
The transducer was calibrated up to 1 MPa using a pressure vessel(a tube of circular cross section) with a known cross sectional area filled with water to which known loads were applied by a servocontrolled hydraulic materials testing machine (Dartec, Dartec Ltd. Stourbridge, United Kingdon). The rate of application of load during calibration was approximately 0.2 MPa/s. Over the range 0–1 MPa the voltage recorded was found to be linear with respect to pressure applied. Re-calibrations of the transducer showed that it was very stable and showed negligible drift over time. Before surgical use, the pressure transducer was sterilised using Perisafe (Antec International, Sudbury, UK) according to standard hospital protocols.
Analysis of data
The initial position of the transducer/electrode tip and of the transducer membrane in each disc was assessed from the intra-operative X-ray film. These were scaled using the known diameter and length of the pressure transducer. The disc dimensions were obtained from the same X-ray. Results are given as the position of the transducer diaphragm relative to the concave border of the disc.
Chart software (ADInstruments, Oxford, UK) was used to convert the voltages obtained into stresses/pressures in accordance with the measured calibration coefficient. The data were then exported to Microsoft Excel for further analysis.
Where appropriate, measurements are presented as means and standard deviations in n discs where n is the number of discs tested.
In this study, pressure profiles were measured in 25 scoliotic and 10 non-scoliotic discs from 7 scoliotic and 4 non-scoliotic patients over a period of one year (July 2001 – July 2002). Details of the scoliotic patients in the study are given in Table 1 and of the non-scoliotic patients in Table 2. The age range of the scoliotic patients was from 13 to 25 years (mean age 19.1 ± 5.0 years) and of the non-scoliotic patients was 15–40 yrs. The majority of scoliotics were female (6/7). In 6/7 patients there was no obvious underlying cause for the curve, classified as idiopathic; the one neuromuscular (patient 3) was severely disabled with microcephaly, epilepsy and possible Rett's syndrome. The Cobb angle of the curves varied from 44 to 78 degrees, mean 59.4 ± 10.1. There were four left and three right sided thoracolumbar curves and the apical disc was at T11/T12 or T12/L1 in 4/7 patients. Two of the non-scoliotic patients were treated for kyphosis and two for back-pain.
Patterns of stress profiles seen across scoliotic discs
The stress profiles generally showed asymmetries between the concave and convex sides of the curve for both the vertical and horizontal stresses.
In 5 cases, peaks in the convex annulus also occurred. On only 2 occasions was this higher than the maximum vertical stress in the concave annulus in the same disc.
Disc hydrostatic pressures
Hydrostatic disc pressures in the apical disc were not obviously higher overall or higher than at adjacent levels and the apical discs had more hydrostatic nuclei 6/7 (86%) compared with 10/18 non-apical discs (56%).
Maximum stress in the concave annulus
Stress change across the disc
The stress change across the disc was calculated from the first reading shown to be taken inside the anatomical disc minus the last reading taken before the transducer exited on the convex side. On some occasions, the last reading was probably out of the disc (both vertical and horizontal stresses suddenly fell to zero and these points were disregarded). In 18/24 discs, this value was positive indicating that higher stresses were found on the concave side of the curve. In only 2/7 patients was the stress positive and greater in the apical disc than adjacent discs. In 7/25 discs, stress was higher in the concave annulus than the convex without a concave stress peak being present.
Due to the low numbers of patients who both were having anterior surgery for non-scoliotic conditions and who consented to having pressure measurements performed during the time period of the study, we only have pressure profiles from 10 discs for comparison.
Table 2 shows clinical details for the two patients with back pain and two patients with kyphosis in the study.
Patterns of stress profiles
Profiles showed significant variability in this group of patients.
Patient P10 who was 26 years old showed a pressure profile with higher stresses towards the posterior annulus, a hydrostatic region and a trough of horizontal pressure in the anterior annulus. In both discs of patient 11, stresses were essentially zero throughout apart from an increase in vertical stress in both and a horizontal stress peak in the anterior annulus of the L5/S1 disc with no hydrostatic regions.
In the kyphotic patients, patient 8 who had quite a flexible curve clinically showed profiles with pressure peaks mainly in the anterior annulus with an under pressurised central region. The T11/12 and L1/2 levels showed hydrostatic nuclei. Patient 9 who was a kyphotic with a curve that was noted to be very stiff intra-operatively had very narrow discs and made introduction of the pressure probe difficult. Only a few recordings per disc (mean of 2.75) were made and so profile shape could not be accurately determined.
5/10 (50%) non-scoliotic discs showed no regions of hydrostatic pressure.
For the patients with back pain, hydrostatic regions were seen in the L4/5 disc of patient 10 (0.214 MPa). The central regions of both discs in patient 11 showed negative pressures very close to zero level (L4/5 and L5/S1, means of -0.023 and 0.040 MPa respectively) and the horizontal and vertical pressures were very close in value over these regions. In the kyphotic patients, only the T11/12 and L1/2 discs of patient 8 showed hydrostatic regions with a mean of 0.030 ± 0.022 MPa. For patient 9, there were no hydrostatic regions however in order to indicate the general size of the stresses present, the mean vertical stress was 0.327 ± 0.33 MPa and horizontal was 0.627 ± 0.46 MPa over all 4 recorded discs.
Stress peaks/stress change across non-scoliotic discs
5/6 (83%) non-scoliotic discs showed stress peaks in either the anterior or posterior annulus (data from Patient 9 was disregarded due to too few data points per disc) with the T11/12 disc of patient 8 showing both anterior and posterior peaks. Of these stress peaks, 5/7 (71%) were anterior.
Comparison of scoliotic and non-scoliotic hydrostatic pressures
Because of the small number of non-scoliotic patients in this study, with the permission of the author (Mr Yonezawa) we have also compared our results with intradiscal pressures measured in Japanese subjects with back pain prior to laser nucleotomy. In this publication, intra-discal pressure measurements were made on patients under general anaesthesia and hence are comparable to our patients in terms of levels of spinal loading due to similar levels of muscular tension. This published series has older patients than those of the present study but neither we nor Yonezawa et al. found any effect of age on intradiscal pressureWe only used data from discs that we thought had hydrostatic nuclei from Yonezawa's study. We determined this by defining a hydrostatic nucleus as one in which the vertical and horizontal pressures differed by less than 0.01 MPa. For all those patients with hydrostatic nuclei (13/18) the mean disc pressure was 0.058 ± 0.03 MPa and for those age matched to the study patients the mean disc pressure was 0.070 ± 0.030 MPa.
In our study, the mean value of hydrostatic pressure for the scoliotic patients was 0.25 ± 0.10 MPa, > 3 fold higher than that measured in Yonezawa's patients.
Summary of results
We present new data on intra-disc pressure profiles of patients with thoraco-lumbar scoliosis. The overall hypothesis we were attempting to test in this study was that abnormal, asymmetrical loading was present in the scoliotic spine and contributed to the progression of the scoliotic deformity. However, due to the surgical positioning and anaesthetised state of the scoliotic subjects we were unsure whether any physiologically significant pressure readings would be obtained since the majority of loading across the motion segment is due to body weight and muscle activity [30–32]. We would perhaps have been expected to find pressures some way between 0.05 MPa and 0.14 MPa, the "intrinsic pressure" of cadaveric discs without muscle loading [33–36]. We also expected to find higher pressures, less hydrostatic discs and qualitatively different pressure/stress profiles in the apical disc than in adjacent discs since it is the most deformed and has more pronounced biochemical changes and lower cell viability than adjacent levels. [37–39].
Rather surprisingly, the readings obtained in the scoliotic discs were much higher in magnitude than we expected. The mean pressure reading in those discs with a hydrostatic nucleus (14/25) was 0.25 ± 0.10 MPa which was on average >3 fold greater than in the available control data (Figure 11).
Despite the lack of muscle activity, our results also showed evidence of asymmetrical loading in the scoliotic spine. Stresses were higher in the concave than in the convex annulus in 18/25 discs (Figure 9). We did not however find increased hydrostatic pressure (Figure 6) or peak stress levels (Figure 8) in the apical disc compared with its neighbours and in all but one disc, stress change was lowest in the apical disc compared with adjacent levels.
A number of scoliotic and non-scoliotic discs in this study had non-hydrostatic regions, 44% of scoliotic and 50% of non-scoliotic. For the nuclear matrix to behave in a non-hydrostatic manner it must be abnormal in composition or relatively dehydrated. This would be most likely due to glycosaminoglycan loss or potentially, mechanical loss of fluid due to chronic high loading. With regards to the non-scoliotic discs, the back pain patients would be expected to have degenerate discs with glycosaminoglycan loss. Patient 11 was known to have severe degeneration on MRI imaging and hence showed disc pressures close to zero and non-hydrostatic discs. Patient 10 was younger and had less severe degeneration consistent with higher pressures and a hydrostatic disc. For the kyphotic patients, patient 8 was a severely disabled, paraplegic from T4 distally due to invasion of the spinal cord by tumour. She had flexible kyphosis clinically and the T12/L1 level was non-hydrostatic presumably due to secondary degenerative change at that level. Patient 9 had a very stiff curve and almost complete loss of disc height at all levels and severely dehydrated discs. With regards to the scoliotic discs however, non-hydrostatic discs are less easily explainable. Glycosaminoglycan loss in not know to be severe in the scoliotic disc and although the disc structure is abnormal, it is not classically degenerate [40–42].
The pressures we measured in discs with hydrostatic regions in the scoliotic patients were considerably higher than those measured in patients with kyphosis and with chronic low back pain, which were on average low and of similar magnitude to that reported by Yonezawa. In addition, the mean intradiscal pressures measured in scoliotic patients (0.25 MPa; Fig 11) were also higher than pressures measured in healthy awake volunteers in similar postures, 0.12 MPa in the L4/5 disc of a healthy orthopaedic surgeon and a mean of 0.15 MPa in a group of 22–29 y old Japanese volunteers with no disc degeneration. These pressures indicate overloading of the scoliotic disc and hence if present chronically could cause relative dehydration and also lead to the non-hydrostatic behaviour seen in some discs.
The finding of high pressures and stresses in recumbent, anaesthetised scoliotic patients with minimal loading due to muscle activity was unexpected and its origins are unclear.
The internal mechanical environment of the intervertebral disc is complex. The factors influencing disc pressure/stress at any point in the disc will arise from both intrinsic factors, viz. disc swelling pressure and matrix organisation and extrinsic factors including muscle action, body weight and ligamentous tethering. Swelling pressure arises from the balance between tissue composition, particularly glycosaminoglycan concentration, and the opposing tension imposed by the collagen network and while changes in glycosaminoglycan concentrations have been reported across scoliotic discs[37, 45], these would tend to rather affect the swelling pressure profile than increase swelling pressure levels.
With regard to externally imposed forces, body weight and muscle forces, though altered in scoliotic patients, should play no role in these anaesthetized recumbent patients. The patients in this study were also all well supported inferiorly by an evacuated bean-bag which should have reduced externally imposed loading to a minimum. However, the surgical positioning of a patient with a curved, axially rotated spine might increase torsion in the deformed segments of the spine. The 7 surgical patients were all in the lateral position and in vitro tests show that imposition of rotation, flexion or extension in axially loaded spines can lead to a pressure rise in the disc [47, 48].
Ligamentous tethering or changes in annulus organisationcould be another factor pre-stressing the disc and causing higher pressures however we feel that this is unlikely to explain the magnitude of change seen. Recent studies of the lumbar fascia have shown that it can transmit loads and has contractile properties and hence is an intriguing candidate for the origin of these forces[50, 51]. Further studies of this structure in scoliosis would therefore be of interest.
As well as differences in pressure levels, there were also profound qualitative differences between the pressure profiles measured in the study scoliotic discs during surgery (Figure 4 and 5) and those found in previous measurements made in non-scoliotic discs of comparable age or in healthy animal discs [28, 52]. In non-degenerate discs, a hydrostatic region of constant pressure, 'the functional nucleus' is found across most of the disc apart from the first few millimetres of the outer annulus where stresses fall steeply. No such profile was seen in the scoliotic discs despite their young age. Many of the profiles measured had characteristics previously seen only in degenerate or asymmetrically loaded discs[53, 54]such as annular stress concentrations or non-hydrostatic nuclei. The non-scoliotic but pathological discs in this study also showed stress peaks and evidence of stress gradients in the sagittal plane (Figure 10).
Stress peaks and asymmetrical loading
The origin of disc stress peaks has been discussed previously in the literature[25, 27] in non-scoliotic discs. In cadaveric discs, annular stress peaks seen in degenerate discs are thought to be due to depressurisation of the nucleus and increasing compressive loading of the annulus. Flexion or extension of discs often caused stress peaks to develop. Interestingly, some mildly degenerate discs developed annular stress peaks after depressurisation resulting from fluid loss after creep loading (1200 N over 3 hrs); this fluid loss also exacerbated the effects of flexion/extension. In the study scoliotic discs, although depressurisation was not seen in the hydrostatic region, the abnormal profiles suggest that the annulus was relatively dehydrated thus possibly leading to the stress peaks seen. If these pressures are present in daily life, these discs may be subjected to increased levels of creep loading on a daily basis in addition to the scoliotic lateral flexion and rotation deformity. Other extrinsic influences such as imposed torsion during positioning could also lead to the stress peaks observed, since combined flexion and torsion is reported to produce high stresses in the outer regions of postero-lateral annulus[53, 54] possibly induced by resistance of the annulus fibres to torque. If the stress profile is indeed affected by resistance of the annulus fibres to torsion or to other imposed deformations because of the abnormal lamellar organisation in scoliotic discs[40, 56], results on tests from non-scoliotic discs however may not predict how stresses will be altered in scoliosis.
In 18/24 discs, higher stresses were found on the concave side of the curve compared to the convex indicating asymmetrical loading. This is obviously not explainable by asymmetrical muscle loading since the spinal muscles were relaxed in these patients. The simple presence of concave annular stress peaks, due to the possible previously mentioned factors, could lead to a stress gradient across the disc. However, even in some discs without a defined stress peak, asymmetrical loading was present.
This study has found that stresses in scoliotic discs are abnormal. Scoliotic discs in recumbent anaesthetised, muscle relaxed patients have higher nuclear hydrostatic pressures than those measured in non-scoliotic discs in this study and reported in the literature. In 18/24 discs from patients, a stress gradient from concave to convex sides of the disc was measured, with some very high differential stresses (c. 1.0 MPa, Figure 9), indicating asymmetrical loading. In addition, the stress profiles seen in the scoliotic discs were very different to normal discs, showing similarities found in previous studies of degenerate discs [25–27].
Without the presence of muscle activity, these findings are very surprising and intriguing. Previous studies have implied that asymmetrical muscle loading is the origin of asymmetrical loading which via changes in cellular activity and hence asymmetrical growth causes a "vicous cycle" of progression in an otherwise physiologically normal spine[57, 58]. The results shown indicate the presence of abnormal and asymmetric stresses in the scoliotic disc but in this case not due directly to muscle action. If they arise from remodelling of disc and ligaments or are due to alterations in thoracolumbar fascial mechanics they are likely to be carried through to normal daily postures. This could influence cellular behaviour and growth and hence generate progression of the scoliotic deformity.
This study was supported by Fondation Yves Cotrel and by the Arthritis Research Campaign (U0511).
- Stokes IA: Analysis of symmetry of vertebral body loading consequent to lateral spinal curvature. Spine. 1997, 22: 2495-2503. 10.1097/00007632-199711010-00006.View ArticleGoogle Scholar
- GC R: The aetiology of idiopathic scoliosis. 1990, CRC PressGoogle Scholar
- Villemure I, Aubin CE, Dansereau J, Labelle H: Simulation of progressive deformities in adolescent idiopathic scoliosis using a biomechanical model integrating vertebral growth modulation. J Biomech Eng. 2002, 124: 784-790. 10.1115/1.1516198.View ArticleGoogle Scholar
- Andriacchi TP, Schultz AB, Belytschko TB, Dewald R: Milwaukee brace correction of idiopathic scoliosis. A biomechanical analysis and a restrospective study. J Bone Joint Surg Am. 1976, 58: 806-815.View ArticleGoogle Scholar
- Perie D, Aubin CE, Petit Y, Beausejour M, Dansereau J, Labelle H: Boston brace correction in idiopathic scoliosis: a biomechanical study. Spine. 2003, 28: 1672-1677. 10.1097/00007632-200308010-00008.PubMedGoogle Scholar
- Wynarsky GT, Schultz AB: Optimization of skeletal configuration: studies of scoliosis correction biomechanics. J Biomech. 1991, 24: 721-732. 10.1016/0021-9290(91)90336-L.View ArticleGoogle Scholar
- Alexander MA, Season EH: Idiopathic scoliosis: an electromyographic study. Arch Phys Med Rehabil. 1978, 59: 314-315.PubMedGoogle Scholar
- Avikainen VJ, Rezasoltani A, Kauhanen HA: Asymmetry of paraspinal EMG-time characteristics in idiopathic scoliosis. J Spinal Disord. 1999, 12: 61-67. 10.1097/00002517-199902000-00010.View ArticleGoogle Scholar
- Zetterberg C, Bjork R, Ortengren R, Andersson GB: Electromyography of the paravertebral muscles in idiopathic scoliosis. Measurements of amplitude and spectral changes under load. Acta Orthop Scand. 1984, 55: 304-309.View ArticleGoogle Scholar
- Ford DM, Bagnall KM, McFadden KD, Greenhill BJ, Raso VJ: Paraspinal muscle imbalance in adolescent idiopathic scoliosis. Spine. 1984, 9: 373-376. 10.1097/00007632-198405000-00008.View ArticleGoogle Scholar
- Mannion AF, Meier M, Grob D, Muntener M: Paraspinal muscle fibre type alterations associated with scoliosis: an old problem revisited with new evidence. Eur Spine J. 1998, 7: 289-293. 10.1007/s005860050077.View ArticleGoogle Scholar
- Yarom R, Robin GC: Muscle pathology in idiopathic scoliosis. Isr J Med Sci. 1979, 15: 917-924.PubMedGoogle Scholar
- Zetterberg C, Aniansson A, Grimby G: Morphology of the paravertebral muscles in adolescent idiopathic scoliosis. Spine. 1983, 8: 457-462. 10.1097/00007632-198307000-00003.View ArticleGoogle Scholar
- Lanyon LE: Control of bone architecture by functional load bearing. J Bone Miner Res. 1992, 7 Suppl 2: S369-S375.View ArticleGoogle Scholar
- Lotz JC, Hsieh AH, Walsh AL, Palmer EI, Chin JR: Mechanobiology of the intervertebral disc. Biochem Soc Trans. 2002, 30: 853-858. 10.1042/BST0300853.View ArticleGoogle Scholar
- Iatridis JC, Mente PL, Stokes IA, Aronsson DD, Alini M: Compression-induced changes in intervertebral disc properties in a rat tail model. Spine. 1999, 24: 996-1002. 10.1097/00007632-199905150-00013.View ArticleGoogle Scholar
- Ohashi N, Robling AG, Burr DB, Turner CH: The effects of dynamic axial loading on the rat growth plate. J Bone Miner Res. 2002, 17: 284-292. 10.1359/jbmr.2002.17.2.284.View ArticleGoogle Scholar
- Robling AG, Duijvelaar KM, Geevers JV, Ohashi N, Turner CH: Modulation of appositional and longitudinal bone growth in the rat ulna by applied static and dynamic force. Bone. 2001, 29: 105-113. 10.1016/S8756-3282(01)00488-4.View ArticleGoogle Scholar
- Mente PL, Stokes IA, Spence H, Aronsson DD: Progression of vertebral wedging in an asymmetrically loaded rat tail model. Spine. 1997, 22: 1292-1296. 10.1097/00007632-199706150-00003.View ArticleGoogle Scholar
- Feik SA, Storey E, Ellender G: Stress induced periosteal changes. Br J Exp Pathol. 1987, 68: 803-813.PubMedPubMed CentralGoogle Scholar
- Mente PL, Aronsson DD, Stokes IA, Iatridis JC: Mechanical modulation of growth for the correction of vertebral wedge deformities. J Orthop Res. 1999, 17: 518-524. 10.1002/jor.1100170409.View ArticleGoogle Scholar
- Pazzaglia UE, Andrini L, Di Nucci A: The effects of mechanical forces on bones and joints. Experimental study on the rat tail. J Bone Joint Surg Br. 1997, 79: 1024-1030. 10.1302/0301-620X.79B6.7749.View ArticleGoogle Scholar
- Wynarsky G, Schultz A: Effects of age and sex on the external induction of scoliosis in rats. Spine. 1987, 12: 974-977. 10.1097/00007632-198712000-00005.View ArticleGoogle Scholar
- Stokes IAF, Aronsson DD, Jones M: Disc and vertebral wedging in patients with progressive scoliosis. Research into Spinal Deformities 2. 1998, Amsterdam. IOS Press, 191-193.Google Scholar
- McNally DS, Adams MA: Internal intervertebral disc mechanics as revealed by stress profilometry. Spine. 1992, 17: 66-73. 10.1097/00007632-199201000-00011.View ArticleGoogle Scholar
- Adams MA, McNally DS, Dolan P: 'Stress' distributions inside intervertebral discs. The effects of age and degeneration. J Bone Joint Surg Br. 1996, 78: 965-972. 10.1302/0301-620X78B6.1287.View ArticleGoogle Scholar
- McNally DS: Biomechanics of the intervertebral disc- disc pressure measurements and significance. Lumbar Spine Disorders. Current Concepts. Edited by: Aspen RM, Porter RW. 1995, Singapore: World Scientific Publishing Co., 42-50.View ArticleGoogle Scholar
- Mitchell RA, Innes JF, McNally D: Pressure profilometry of the lumbosacral disk in dogs. Am J Vet Res. 2001, 62: 1734-1739. 10.2460/ajvr.2001.62.1734.View ArticleGoogle Scholar
- Yonezawa T, Ichimura Y, Onomura T: Intradiscal pressure measurements in patients undergoing surgery. Medical Electronics and Tissue Engineering. 1997, , 35: 249-253.Google Scholar
- Nachemson AL: Disc pressure measurements. Spine. 1981, 6: 93-97. 10.1097/00007632-198101000-00020.View ArticleGoogle Scholar
- Sato K, Kikuchi S, Yonezawa T: In vivo intradiscal pressure measurement in healthy individuals and in patients with ongoing back problems. Spine. 1999, 24: 2468-2474. 10.1097/00007632-199912010-00008.View ArticleGoogle Scholar
- Andersson GB, Ortengren R, Herberts P: Quantitative electromyographic studies of back muscle activity relatated to posture and loading. Orthop Clin North Am. 1977, 8: 85-96.PubMedGoogle Scholar
- Virgin WJ: Experimental investigations into the physical properties of the intervertebral disc. J Bone Joint Surg Br. 1951, 33-B: 607-611.View ArticleGoogle Scholar
- Nachemson A, Morris JM: In vivo measurments of intradiscal pressure. Discometry, a method for the determination of pressure in the lower lumbar discs. J Bone Joint Surg Am. 1964, 46: 1077-1092.View ArticleGoogle Scholar
- Nachemson A, Elfstrom G: Intravital dynamic pressure measurements in lumbar discs. A study of common movements, maneuvers and exercises. Scand J Rehabil Med Suppl. 1970, 1: 1-40.PubMedGoogle Scholar
- Nachemson AL, Schultz AB, Berkson MH: Mechanical properties of human lumbar spine motion segments. Influence of age, sex, disc level, and degeneration. Spine. 1979, 4: 1-8. 10.1097/00007632-197901000-00001.View ArticleGoogle Scholar
- Urban MR, Fairbank JC, Bibby SR, Urban JP: Intervertebral disc composition in neuromuscular scoliosis: changes in cell density and glycosaminoglycan concentration at the curve apex. Spine. 2001, 26: 610-617. 10.1097/00007632-200103150-00010.View ArticleGoogle Scholar
- Bibby SR, Fairbank JC, Urban MR, Urban JP: Cell viability in scoliotic discs in relation to disc deformity and nutrient levels. Spine. 2002, 27: 2220-2228. 10.1097/00007632-200210150-00007.View ArticleGoogle Scholar
- Bibby SR, Meir A, Fairbank JC, Urban JP: Cell viability and the physical environment in the scoliotic intervertebral disc. Stud Health Technol Inform. 2002, 91: 419-421.PubMedGoogle Scholar
- Roberts S, Menage J, Eisenstein SM: The cartilage end-plate and intervertebral disc in scoliosis: calcification and other sequelae. J Orthop Res. 1993, 11: 747-757. 10.1002/jor.1100110517.View ArticleGoogle Scholar
- Roberts S: Disc morphology in health and disease. Biochem Soc Trans. 2002, 30: 864-869. 10.1042/BST0300864.View ArticleGoogle Scholar
- Roberts S, Evans H, Trivedi J, Menage J: Histology and pathology of the human intervertebral disc. J Bone Joint Surg Am. 2006, 88 (Suppl 2): 10-14. 10.2106/JBJS.F.00019.PubMedGoogle Scholar
- Wilke HJ, Neef P, Caimi M, Hoogland T, Claes LE: New in vivo measurements of pressures in the intervertebral disc in daily life. Spine. 1999, 24: 755-762. 10.1097/00007632-199904150-00005.View ArticleGoogle Scholar
- Sivan S, Merkher Y, Wachtel E, Ehrlich S, Maroudas A: Correlation of swelling pressure and intrafibrillar water in young and aged human intervertebral discs. J Orthop Res. 2006, 24: 1292-1298. 10.1002/jor.20144.View ArticleGoogle Scholar
- Antoniou J, Arlet V, Goswami T, Aebi M, Alini M: Elevated synthetic activity in the convex side of scoliotic intervertebral discs and endplates compared with normal tissues. Spine. 2001, 26: E198-E206. 10.1097/00007632-200105150-00002.View ArticleGoogle Scholar
- Stokes IA, Gardner-Morse M: Muscle activation strategies and symmetry of spinal loading in the lumbar spine with scoliosis. Spine. 2004, 29: 2103-2107. 10.1097/01.brs.0000141182.42544.1f.View ArticleGoogle Scholar
- Frei H, Oxland TR, Nolte LP: Thoracolumbar spine mechanics contrasted under compression and shear loading. J Orthop Res. 2002, 20: 1333-1338. 10.1016/S0736-0266(02)00058-X.View ArticleGoogle Scholar
- van Deursen DL, Snijders CJ, Kingma I, van Dieen JH: In vitro torsion-induced stress distribution changes in porcine intervertebral discs. Spine. 2001, 26: 2582-2586. 10.1097/00007632-200112010-00011.View ArticleGoogle Scholar
- Heidari B, Fitzpatrick D, Synnott K, McCormack D: Modelling of annulus fibrosus imbalance as an aetiological factor in adolescent idiopathic scoliosis. Clin Biomech (Bristol , Avon ). 2004, 19: 217-224. 10.1016/j.clinbiomech.2003.12.007.View ArticleGoogle Scholar
- Vleeming A, Pool-Goudzwaard AL, Stoeckart R, van Wingerden JP, Snijders CJ: The posterior layer of the thoracolumbar fascia. Its function in load transfer from spine to legs. Spine. 1995, 20: 753-758. 10.1097/00007632-199504000-00001.View ArticleGoogle Scholar
- Schleip R, Klingler W, Lehmann-Horn F: Active fascial contractility: Fascia may be able to contract in a smooth muscle-like manner and thereby influence musculoskeletal dynamics. Med Hypotheses. 2005, 65: 273-277. 10.1016/j.mehy.2005.03.005.View ArticleGoogle Scholar
- Ishihara H, McNally DS, Urban JP, Hall AC: Effects of hydrostatic pressure on matrix synthesis in different regions of the intervertebral disk. J Appl Physiol. 1996, 80: 839-846.View ArticleGoogle Scholar
- Edwards WT, Ordway NR, Zheng Y, McCullen G, Han Z, Yuan HA: Peak stresses observed in the posterior lateral anulus. Spine. 2001, 26: 1753-1759. 10.1097/00007632-200108150-00005.View ArticleGoogle Scholar
- Steffen T, Baramki HG, Rubin R, Antoniou J, Aebi M: Lumbar intradiscal pressure measured in the anterior and posterolateral annular regions during asymmetrical loading. Clin Biomech (Bristol , Avon ). 1998, 13: 495-505. 10.1016/S0268-0033(98)00039-4.View ArticleGoogle Scholar
- Krismer M, Haid C, Rabl W: The contribution of anulus fibers to torque resistance. Spine. 1996, 21: 2551-2557. 10.1097/00007632-199611150-00004.View ArticleGoogle Scholar
- Yu J, Fairbank JC, Roberts S, Urban JP: The elastic fiber network of the anulus fibrosus of the normal and scoliotic human intervertebral disc. Spine. 2005, 30: 1815-1820. 10.1097/01.brs.0000173899.97415.5b.View ArticleGoogle Scholar
- Stokes IA, Spence H, Aronsson DD, Kilmer N: Mechanical modulation of vertebral body growth. Implications for scoliosis progression. Spine. 1996, 21: 1162-1167. 10.1097/00007632-199605150-00007.View ArticleGoogle Scholar
- Stokes IA, Burwell RG, Dangerfield PH: Biomechanical spinal growth modulation and progressive adolescent scoliosis - a test of the 'vicious cycle' pathogenetic hypothesis: Summary of an electronic focus group debate of the IBSE. Scoliosis. 2006, 1: 16-10.1186/1748-7161-1-16.View ArticleGoogle Scholar
This article is published under license to BioMed Central Ltd. This is an Open Access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/2.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.