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Altered neuromuscular control mechanisms of the trapezius muscle in fibromyalgia

  • Björn Gerdle1, 2,
  • Christer Grönlund3, 4,
  • Stefan J Karlsson3, 4,
  • Andreas Holtermann5Email author and
  • Karin Roeleveld6
BMC Musculoskeletal Disorders201011:42

https://doi.org/10.1186/1471-2474-11-42

Received: 5 November 2009

Accepted: 5 March 2010

Published: 5 March 2010

Abstract

Background

fibromyalgia is a relatively common condition with widespread pain and pressure allodynia, but unknown aetiology. For decades, the association between motor control strategies and chronic pain has been a topic for debate. One long held functional neuromuscular control mechanism is differential activation between regions within a single muscle. The aim of this study was to investigate differences in neuromuscular control, i.e. differential activation, between myalgic trapezius in fibromyalgia patients and healthy controls.

Methods

27 fibromyalgia patients and 30 healthy controls performed 3 minutes bilateral shoulder elevations with different loads (0-4 Kg) with a high-density surface electromyographical (EMG) grid placed above the upper trapezius. Differential activation was quantified by the power spectral median frequency of the difference in EMG amplitude between the cranial and caudal parts of the upper trapezius. The average duration of the differential activation was described by the inverse of the median frequency of the differential activations.

Results

the median frequency of the differential activations was significantly lower, and the average duration of the differential activations significantly longer in fibromyalgia compared with controls at the two lowest load levels (0-1 Kg) (p < 0.04), but not at the two highest load levels (2 and 4 Kg).

Conclusion

these findings illustrate a different neuromuscular control between fibromyalgia patients and healthy controls during a low load functional task, either sustaining or resulting from the chronic painful condition. The findings may have clinical relevance for rehabilitation strategies for fibromyalgia.

Background

Approximately 20% of the European population report severe chronic musculoskeletal pain [1]. Ten to twenty percent of those, that is 2-4 percent of the general population, suffer from fibromyalgia (FM). FM is characterized by a widespread pain and tenderness to pressure (allodynia), but with unknown aetiology [24]. FM has been described as a complex hyperalgesic pain syndrome, in which abnormalities of central sensory processing interact with peripheral pain generators and psycho-neuro-endocrine dysfunction [57].

FM patients often report pain and tenderness in the trapezius muscle, reflected by the numerous predefined tender points located within the muscle [8]. Moreover, the trapezius muscle in FM has shown mitochondrial disturbances in type-I muscle fibers (i.e., ragged-red fibers and moth-eaten fibers), hypotrophy of type-II fibers, reduced capillarisation [9] and altered microcirculation [10, 11].

In line with the disturbed microcirculation in muscles of FM patients, elevated levels of muscle fatigue has been reported in patients with chronic neck pain [12]. Reports of inability to relax muscle or increased muscular tension in persons with or developing trapezius myalgia [1317] have brought focus on the association between neuromuscular control mechanisms and chronic pain. Several neuromuscular control mechanisms are proposed to prevent continuing muscle activity, local circulation disturbances, fatigue, high-threshold afferent activity and pain [18]. An often discussed neuromuscular control mechanism is rotation or substitution of active single motor units [19, 20], assumed to prevent fatigue during prolonged contractions. Another related neuromuscular control mechanism suggested to prevent monotonous prolonged activation of motor units and local fatigue is reciprocal reversals of activity between regions within a single muscle, termed differential activation [2123].

Recently, Falla and colleagues observed a relatively higher increase in activity of the cranial compared to the caudal part of the upper trapezius in healthy controls compared to FM patients during a sustained contraction [24]. This finding indicates recruitment of more motor units in the cranial part of the upper trapzius with fatigue in FM patients compared to healthy controls [24]. However, it does not provide information whether patients with FM possess an altered neuromuscular control strategy involving shifts in activity between regions within a muscle (i.e. differential activations).

The aim of this study was to examine whether neuromuscular control is different in patients with FM from healthy controls with respect to differential activation within the trapezius muscle during shoulder elevations with low load. Such low load elevations are functional tasks which can reveal altered neuromuscular control mechanisms relevant for daily living activities and are therefore of ecologic validity.

Methods

Subjects

Healthy controls

Female healthy controls (N = 30; age: 40 ± 5 years, weight: 62.8 ± 7.3 kg, height: 168 ± 8 cm) without ongoing acute or chronic pain were recruited through advertisements among students and staff at the University Hospital of Linköping, Sweden. None of the subjects in the control group had pain according to a rating of pain intensity in the neck and shoulder region using a 100 mm visual analogue scale (VAS; endpoints: no pain and maximum pain, respectively) or had a recurrent and/or chronic pain condition.

Fibromyalgia patients (FM)

Female patients with fibromyalgia (N = 29; age: 37 ± 5 years, weight: 69.3 ± 9.5 kg, height: 166 ± 5 cm), were recruited from the Pain and Rehabilitation Centre, University Hospital, Linköping, Sweden. It should be noted that not all of these patients were able to perform all tasks (see Results, Drop-out and activity levels at the different loads). The patients were offered participation in the study after examination of medical journals, positive response to information letter, and a phone conversation with a physician. The patients were clinically diagnosed according to the ACR criteria of 1990 for the classification of fibromyalgia (FM) [25]. The mean duration of FM was 6.6 ± 3.2 years (minimum 2 years), and the maximum pain intensity recent week was 87 ± 13 mm according to a 100 mm VAS. Corresponding ratings for minimum pain intensity recent week, and average pain intensity recent week were 25 ± 15 mm, and 50 ± 18 mm, respectively.

Basic descriptive data of the two groups of subjects (i.e., age anthropometric data, habitual pain intensity, and data from ultrasound recording) have been presented previously [26].

Ethical aspects

All subjects gave written informed consent to participate. The study conformed to the Declaration of Helsinki and the study protocol was approved by the local ethics committee at Linköping University.

Ultrasound recordings

Ultrasound measurements were taken of the thickness (mm) of the trapezius muscle and the subcutaneous soft tissue (skin and fat tissue taken together) 2 cm lateral of the midpoint between the seventh process of the cervical spine and the lateral part of the acromion process using an Acuson 128XP/10 (Siemens).

Muscle contractions

The subjects performed symmetrical bilateral shoulder elevations with different loads. The loads were applied through the attachment of different weights on a harness (Figure 1). The harness consisted of 2 belts hanging on both shoulders on the level of the acromion to allow attachment of the weights. One additional belt was placed around the torso in order to fixate the other two belts. After attaching the harness and weights, the subjects were asked to lift the weights such that the shoulders were in a horizontal plane, and to hold this position for 3 min. Weights of 0, 1, 2, and 4 kg were applied successively. The subjects were given 1-min rest between each contraction. The choice of absolute weights and not relative weights in relation to maximum performance was based on the difficulties for obtaining valid maximum voluntary contractions (MVC) in FM patients due to pain and/or psychological aspects such as fear-avoidance or kinesiophobia.
Figure 1

Experimental setup. Posterior view of a subject, electromyographical electrode device (rectangle), and weight harness. The centre of the electrode-device was placed in the middle of the line between processus spinosus of the C7 vertebra and the lateral edge of acromion. The harness was used to attach weights symmetrically on the shoulders. Subjects performed isometric shoulder elevation such that their shoulders were held in the horizontal plane.

Surface EMG acquisition

Surface electromyographic (EMG) signals were recorded using a high-density electrode-grid (modified ActiveOne, BioSemi, Amsterdam, Netherlands) consisting of 13 by 10 active electrodes, covering 6 × 4.5 cm of the skin surface. The base of the electrode-grid device was concave and semiflexible and thereby fitted well with the convex recordings area of the upper trapezius muscle. The centre of the electrode grid was placed on the skin above the right trapezius muscle in the middle of the line between the processus spinosus of the seventh cervical vertebra and the lateral edge of acromion (Figure 1). In this way, the recorded signals of all subjects were not affected by muscle-tendon transitions and similarly affected by the motor end plate region. To generate a stable pressure between electrodes and the skin, the electrode grid was held in place by two elastic straps around the shoulder and torso of the subject. The surface EMG signals were recorded from all electrodes with a common reference on the processus spinosus of the seventh cervical vertebra at 2048 Hz.

Surface EMG analysis - Quantification of differential activation

The differential activation analysis was previously described [23]. The essence of the analysis was to examine the temporal changes of the difference in myoelectric activity between two regions within a muscle. While the EMG signals were recorded using a 2-D high-density EMG grid, a large part of the processing (most of step II below) was undertaken in order to reduce the data to signals originating from the caudal and cranial regions of the trapezius muscle. Multiple channels covering a large area were recorded to get a better estimate of the activation of the two muscle parts [27]. In short, the procedure involved;
  1. I.

    Pre-processing: Prior to analysis, poor quality signals were omitted. The remaining signals were high-pass filtered at 10 Hz, and bipolar spatial filtering in the fiber direction (medial-lateral) was carried out.

     
  2. II.

    Muscle activity in the cranial - caudal direction: Muscle activity in the caudal - cranial direction (perpendicular to fibre orientation) was calculated by averaging the muscle activity recorded by electrodes of the grid along the fibre orientation (medial - lateral), providing 10 activity signals in the cranial caudal direction. The muscle activity level of the EMG signals was described using the root-mean-square (RMS), calculated in 0.5 s non-overlapping time-windows. In order to compare the activity between regions within the muscle, the muscle activity signals were de-trended and normalized to their maximum (Figure 2A and 2C).

     
Figure 2

Examples of a normalized muscle activity from a high-density EMG recording (caudal - cranial, channel 1 to 10, 5 mm's apart) from one healthy control (A) and one patient with fibromyalgia (C) performing a 1 kg weight of isometric shoulder elevation. The activity difference (B and D) in normalized activity between caudal and cranial regions segments (see A right) were used to calculate the power spectral median frequency.

  1. III.

    Activity difference: The difference in the normalized muscle activity between the cranial (average of the three most superior electrode positions) and the caudal (average of the three most inferior electrode positions) regions of the upper trapezius was calculated (see Figure 2A).

     
  2. IV.

    Median frequency and average duration of the differential activations: Differential activation was quantified using the power spectral median frequency of the activity difference signal. The inverse of the median frequency of the differential activations was calculated to quantify the average duration of the differential activations.

     

Statistics

All statistical analyses were performed using MATLAB (The Mathworks, Nattick, USA; version 2007b). For variables and indices mean value with one standard deviation (± 1 SD) are generally reported. For multiple comparisons between the two groups, two-way analysis of variance (ANOVA) was performed. Pair-wise comparisons were performed using Student's t-test. A probability of ≤ 0.05 (two-tailed) was used as criteria for significance in all tests.

Results

Anthropometric data including muscle dimensions (also reported in [26])

FM patients were significantly younger (p = 0.017) and heavier (p = 0.005) than control subjects. The average thickness of the trapezius muscle was similar in FM and controls, being 11.7 ± 2.4 mm over the examination area of the trapezius in FM and 11.6 ± 2.4 mm in CON (p = 0.937). The thickness of the superjacent tissues (skin and subcutaneous tissue) was somewhat thicker in FM than in controls (6.6 ± 1.6 mm over the examination area in FM versus 5.2 ± 2.5 mm in controls; p = 0.028).

Drop-outs and activity levels at the different load levels

All control subjects (N = 30) were able to perform the contractions at the four load levels (0, 1, 2 and 4 kg) with a duration of 3 min, and were thus included in the subsequent analyses. In the FM group (N = 29), 2 (6.9%), 2 (6.9%), 4 (13.8%), and 8 (27.6%) patients were not able to perform the tasks during 3 min with the 4 different external loads, respectively, and were therefore excluded in the subsequent analyses for these load levels.

For all loads, the muscle activity levels averaged over all bipolar electrode leads was lower in FM than in controls (p < 0.001). More specific, the activity levels at the 4 different load levels (0, 1, 2 and 4 kg) in controls was respectively 0.87 ± 0.37, 1.04 ± 0.50, 1.14 ± 0.51 and 1.38 ± 0.58 mV and in FM 0.54 ± 0.24, 0.57 ± 0.32, 0.68 ± 0.33 and 0.82 ± 0.41 mV.

Prevalence of differential activation

Figure 2 illustrates a typical example of differential muscle activation between the cranial and caudal parts of the upper trapezius muscle with an external loading of 2 Kg from a control subject and a FM patient. As shown in the figure, the frequency of differential activity between the cranial and caudal parts of the trapezius was higher in the control subject (Figure 2A and 2B) compared to the FM patient (Figure 2C and 2D). Accordingly, the median frequency of the differential activation between the cranial and caudal regions of the trapezius was higher in a typical control subject (Figure 3A) than in a typical FM patient (Figure 3B) with an external loading of 2 Kg.
Figure 3

Examples of the power spectral density (Psd) of the differential activity signal between the cranial and caudal parts of the trapezius and its corresponding median frequency (MDF), for a healthy control (A) and a patient with fibromyalgia (B).

Frequency of differential activation

The median frequency of differential activation at the two lowest load levels at the shoulders (i.e., 0 and 1 kg) was significantly lower in FM compared with the healthy controls (p < 0.04, Table 1, Figure 4). However, the frequency of differential activation was not significantly different between controls and FM at the two higher load levels (i.e., 2 and 4 Kg) (p > 0.28, Table 1, Figure 4). The median frequency of differential activation decreased with increasing loading of the neck-shoulder region in controls, but was invariant of the external loading in FM (Table 1).
Figure 4

Mean values and 95% confidence intervals for median frequency of the differential activations for healthy controls and patients with fibromyalgia at different weights. Furthest to the right is shown the difference between the two groups.

Table 1

Median frequency and duration of differential activation in fibromyalgia (FM) and healthy controls (CON); mean values ± 1 standard deviation (SD) and minimum and maximum values.

Group

CON

 

FM

 

Statistics

Variable and load

Mean ± SD

Min-Max

Mean ± SD

Min-Max

p-value

Frequency ( s -1 )

     

0 kg

0.43 ± 0.08

0.24-0.56

0.37 ± 0.11

0.14-0.53

0.028*

1 kg

0.42 ± 0.10

0.23-0.57

0.35 ± 0.12

0.12-0.60

0.033*

2 kg

0.37 ± 0.11

0.11-0.51

0.34 ± 0.12

0.14-0.53

0.303

4 kg

0.39 ± 0.11

0.14-0.56

0.36 ± 0.12

0.14-0.60

0.280

Duration (sec)

     

0 kg

1.21 ± 0.26

0.89-2.08

1.51 ± 0.61

0.95-3.59

0.022*

1 kg

1.28 ± 0.36

0.88-2.23

1.67 ± 0.85

0.82-4.30

0.025*

2 kg

1.57 ± 0.83

0.98-4.60

1.71 ± 0.73

0.95-3.59

0.500

4 kg

1.42 ± 0.59

0.90-3.59

1.59 ± 0.68

0.84-3.58

0.325

Furthest to the right is the result of the statistical comparisons (p-values) between groups (CON vs. FM); * denotes significant difference.

Duration of differential activation

The average duration of differential activation at the two lowest load levels at the shoulders (i.e., 0 and 1 kg) was significantly lower in FM compared with the healthy controls (p < 0.03, Table 1). However, the average duration of differential activation was not significantly different between controls and FM at the two higher load levels (i.e., 2 and 4 Kg) (p > 0.32, Table 1). The average duration of differential activation did not vary with modifying external loading of the neck-shoulder region in neither controls nor FM (Table 1).

Discussion

The main finding of this study was the lower median frequency of the differential activations, and thus a longer average duration of differential activation between the trapezius regions in fibromyalgia patients compared with healthy controls during static shoulder elevation with none or very low weights. These results will be discussed in the light of mechanisms behind trapezius myalgia in general, and FM in specific.

The neuromuscular control of patients with musculoskeletal pain has received clinical interest for more than a century [28]. For example based on clinical observations that patients with myalgia have tender muscles, it has often been assumed that a vicious circle of pain and hyperactivity exists in chronic pain [29]. Because the healthy controls seem to be able to utilize a redundancy of motor unit populations more frequently through shifting active motor unit populations than patients with fibromyalgia, this finding fits with the Cinderella hypothesis [30].

Already in 1922, Forbes [31] noted that subpopulations of motor units within a muscle may shift on being active (differential activation) and therefore rotate on the loading of the muscle fibers. Shifts in activity between motor unit subpopulations in anatomical complex muscles during monotonous contractions are therefore considered to prevent local muscle fatigue and muscle fiber overexertion [32]. Accordingly, subjects with larger spatial changes in distribution of intra-muscular activity within the upper trapezius are observed to be able to sustain a static contraction for longer duration than subjects with minor spatial changes [33]. The ability to shift activity between regions within the upper trapezius may be a preventive mechanism for avoiding reflexive mediated muscle hyperactivity from acute painful condition further enhancing pain and a chronic condition [34]. Therefore, a longer duration of differential activation of activity within the upper trapezius may be an underlying neuromuscular control mechanism associated with increased risk for acute and chronic musculoskeletal symptoms. In a previous study [23], the duration of differential activation was observed to be positively associated with fatigue prevention. However, this was observed at the biceps brachii during a 30 min contraction in healthy individuals, and may therefore not be translated to this study of the trapezius muscle in FM and healthy controls during a 3 min contraction.

On the other hand, the reduced differential activation in fibromyalgia patients may also be a result of the chronic painful condition; e.g in CNS (central sensitizing processes, alterations in function of neuromatrix of pain in the brain or in descending inhibition) [3538] and/or in muscle [911]. This is supported by the finding that myoelectrical manifestations of fatigue in fibromyalgia patients are central of origin [39]. Prospective investigations of the relation between neuromuscular control strategies and chronic pain are very few [17], and future prospective investigations between neuromuscular control strategies and chronic pain are recommended for elucidating the relation between neuromuscular control and chronic myalgia.

The lower EMG amplitudes in FM can eventually partly be due to the somewhat thicker subcutaneous tissue. Although a thicker subcutaneous layer can affect EMG amplitude and the spatial distribution, it is not likely to affect temporal fluctuations in EMG amplitude and differential activation as investigated in the present study. In addition, the ultrasound investigation did not reveal any significant difference in thickness of the trapezius muscle between the two groups. In order to definitely determine the level of muscle activity, an MVC is needed. However, the validity of MVC in FM can be questioned due to factors such as pain, increase in pain with increasing contraction level, anxiety and different aspects of fear and fear behaviour. However, the observation of a difference in differential activations between FM patients and health controls at very low force levels (0-1 Kg), but not higher force levels (2-4 Kg), supports that a generally higher maximal strength of controls compared with FM patients [24] is not the primary cause to the findings of this study.

The previously documented changes in intra-muscular activity within the upper trapezius of healthy subjects with injection of hypertonic saline suggest that local elicitation of nociceptive afferents generates a reorganization of activity within the upper trapezius [40]. The ability of independent selective voluntary activation of regions within the trapezius muscle with biofeedback guidance [41] illustrates that differential activation between regions of the upper trapezius may be a voluntary neuromuscular strategy.

Conclusions

For the first time, a different neuromuscular control mechanism involving degree of shifts between regions (differential activation) within a single muscle is observed between fibromyalgia patients and healthy controls. The lower frequency of differential activation between regions within the upper trapezius of FM patients than controls indicates that this may be a neuromuscular control strategy either sustaining or being a result of the chronic painful condition. The findings may have clinical relevance for rehabilitation strategies for fibromyalgia.

Declarations

Acknowledgements

This study was supported by the Swedish Research Council (K2005-27X-15316-01A; and 621-2007-3959), and the Swedish Council for Working Life and Social Research and the Swedish Rheumatism Association. There are no conflicts of interest.

Authors’ Affiliations

(1)
Rehabilitation Medicine, Department of Clinical and Experimental Medicine, Linköping University
(2)
Pain and rehabilitation Centre, University Hospital
(3)
Biomedical Engineering & Informatics, University Hospital
(4)
Centre for Biomedical Engineering and Physics, Umeå University
(5)
National Research Centre for the Working Environment
(6)
Human Movement Science Programme, Dragvoll, Norwegian University of Science and Technology

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  42. Pre-publication history

    1. The pre-publication history for this paper can be accessed here:http://www.biomedcentral.com/1471-2474/11/42/prepub

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© Gerdle et al; licensee BioMed Central Ltd. 2010

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.

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