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The impact of work configuration, target angle
and hand force direction on upper extremity
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Article in Ergonomics · January 2010
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The impact of work configuration, target angle and hand force direction on
upper extremity muscle activity during sub-maximal overhead work
Jaclyn N. Chopp a; Steven L. Fischer a; Clark R. Dickerson a
a
Department of Kinesiology, University of Waterloo, 200 University Avenue W, Waterloo, Canada
Online publication date: 12 January 2010
To cite this Article Chopp, Jaclyn N., Fischer, Steven L. and Dickerson, Clark R.(2010) 'The impact of work configuration,
target angle and hand force direction on upper extremity muscle activity during sub-maximal overhead work',
Ergonomics, 53: 1, 83 — 91
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Ergonomics
Vol. 53, No. 1, January 2010, 83–91
The impact of work configuration, target angle and hand force direction on upper extremity
muscle activity during sub-maximal overhead work
Jaclyn N. Chopp, Steven L. Fischer and Clark R. Dickerson*
Department of Kinesiology, University of Waterloo, 200 University Avenue W, Waterloo, ON N2L 3G1, Canada
Downloaded By: [Canadian Research Knowledge Network] At: 20:26 18 January 2010
(Received 28 July 2008; final version received 5 September 2009)
Overhead work has established links to upper extremity discomfort and disorders. As many jobs incorporate
working overhead, this study aimed to identify working conditions requiring relatively lower muscular shoulder
load. Eleven upper extremity muscles were monitored with electromyography during laboratory simulations of
overhead work tasks. Tasks were defined with three criteria: work configuration (fixed, stature-specific); target angle
(7158, 08, 158, 308 from vertical); direction of applied hand force (pulling backwards, pushing forwards,
downwards, sideways, upwards). Normalised electromyographic activity was greater for fixed configurations,
particularly when pulling in a backward direction (total activity ¼ 108.3% maximum voluntary exertion (MVE))
compared to pushing down or forward (total activity ranging from 10.5 to 17.3%MVE). Further, pulling backwards
at angles of –158 and 08 showed the highest muscular demand (p 5 0.05). These results suggest that, if possible,
positioning overhead work in front of the body with exertions directed forwards will result in the lowest upper
extremity muscle demand.
Statement of Relevance: Overhead work pervades occupational settings and is associated with risk of upper extremity
musculoskeletal disorders. The muscular intensity associated with performing overhead work was assessed in
several combinations of work placement and hand force direction. These findings should have utility for designing
overhead work tasks that reduce muscular exposure.
Keywords: electromyography; overhead work; work design; muscle demand
1. Introduction
Upper extremity discomfort resulting from working
overhead is a common concern in the modern workplace (Bernard 1997). As it may not be possible to
modify or design all jobs to eliminate overhead
working components, it may be beneficial to identify
preferable work designs that minimise shoulder muscular demands. This may in turn decrease shoulder
discomfort and risk of pathology. Over the past 10
years, an annual average of 5700 shoulder-related
injury claims were reported to the Workplace Safety
and Insurance Board of Ontario (2006). Furthermore,
Silverstein et al. (1998) examined the incidence of
work-related upper extremity disorders in the US state
of Washington from 1987 to 1995 and found that
shoulder disorders constituted 43.2% of lost time
claims per year, with a mean of 6146 claims per year.
This highlights the need for more shoulder-focused
workplace design.
Overhead work is strongly associated with the
development of upper extremity discomfort and disorders (Bernard 1997, Punnett et al. 2000, Grieve and
Dickerson 2008). Specifically, past research indicates
*Corresponding author. Email: cdickers@uwaterloo.ca
ISSN 0014-0139 print/ISSN 1366-5847 online
Ó 2010 Taylor & Francis
DOI: 10.1080/00140130903323232
http://www.informaworld.com
that awkward postures, that is, deviation from a
neutral posture in extension, flexion and abduction
greater than 458, require a high level of muscle activity
(Herberts et al. 1984). Furthermore, Punnett et al.
(2000) identified an association between shoulder
flexion and abduction greater than 908 (for 410% of
the work cycle) and shoulder disorder development.
Sporrong et al. (1998) earlier noted this association for
overhead precision tasks. Additionally, humeral
elevation above 608 is known to decrease the
subacromial space, potentially leading to development
of supraspinatus and biceps tendon impingement
(Flatow et al. 1994, McFarland et al. 1999, Bey et al.
2007). Several risk factors may contribute to upper
extremity discomfort, including task repetition, high
hand force, awkward postures, direct pressure,
vibration and prolonged constrained postures (Rempel
et al. 1992). Although these risk factors may exist in
the absence of elevated arm posture, their presence, in
addition to working overhead, may place the upper
extremity at elevated risk. Specifically, prolonged
activity in overhead working postures creates strain
and fatigue on shoulder muscles (Herberts and
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84
J.N. Chopp et al.
Kadefors 1976). A strong relationship also exists
between muscle fatigue and increased ratings of
discomfort (Oberg et al. 1994). Furthermore, postural
discomfort is known to occur when the arms are
required to work overhead (Wiker et al. 1989). It
follows that workers performing jobs with overhead
components are at an increased risk of developing
shoulder disorders (Svendsen et al. 2004, Miranda
et al. 2005).
Despite the strong association between overhead
work and musculoskeletal disorders, it is sometimes
difficult to avoid these postures in practice. However,
in industrial tasks that require arm elevation above
shoulder height, flexibility in the location of the
task with regard to the body and the required hand
force direction may exist. Increased muscular demand
as documented through electromyography has been
linked to shoulder pain and discomfort (Wiker
et al. 1989). Thus, if muscle activity required to
produce the same target force is decreased at a specific
work configuration or with a specific direction of
force application, then that condition lowers muscular
demand and can be considered more optimal in terms
of lowering injury risk.
Working configurations, target angles and hand
force directions have all been examined individually in
the literature; however, limited research examines how
these factors interact. Extensive research exists to
relate specific arm angles, working heights and upper
extremity discomfort (Flatow et al. 1994, Sporrong
et al. 1998, McFarland et al. 1999, Palmerud et al.
2000, Punnett et al. 2000, Anton et al. 2001, Garg et al.
2002, Svendsen et al. 2004, Okunribido and Haslegrave
2008). Further, existing research generally suggests
eliminating certain types of overhead work by recommending specific arm angles and postures to avoid; for
example, arm flexion or abduction over 908 (Bernard
1997, Punnett et al. 2000). However, few studies have
evaluated the implications of different hand force
directions (a notable exception is Haslegrave et al.
1997) in conjunction with work height. During
sustained work, postures or force application directions that require low-level muscle activation may be
less likely to trigger the development of a musculoskeletal disorder than those that require higher activations. Higher muscle activation may also accelerate
fatigue development, which is associated with an
increased probability of postural discomfort (Wiker
et al. 1990).
The aim of this research is to quantify shoulder
muscle activity for several overhead working configurations, target angles and hand force directions to
determine how differences in overhead work conditions influence specific muscle activation. The results
from this research will help in establishing which
working postures minimise muscle activity, encourage
safer job design and assist with injury prevention in
jobs that require overhead work. The goal is to
determine which of the set of overhead working
conditions minimises shoulder muscular load.
2. Method
2.1. Participants
In total, 14 right-hand dominant, university-aged
male students (aged 22 + 2 years) participated in the
study. Male participants were selected for ease of
comparison with earlier published results and subject
availability. Participants had a mean height and mass
of 1.85 + 0.08 m and 85.6 + 7.5 kg respectively.
Participants were excluded from participation if they
self-reported any upper extremity disorders within
the past year. The research protocol was approved
by the university ethics review board.
2.2. Equipment
Exerted hand force and muscle activation were
measured in this study. Force was quantified using a
multiaxis loadcell (Figure 1) (MC3A; AMTI,
Watertown MA, USA). Visual force feedback was
provided through a custom designed program written
with Labview software (National Instruments, Austin
Texas, USA), which provided visual feedback to the
participant on the level of force applied to the force
transducer. Feedback was displayed on three bar
graphs corresponding to the direction of force
application; forward/backward (X), upward/
downward (Y), medial (Z). Each graph had a 30 N
threshold line. Subjects were instructed to exert the
specified force level on the transducer until the
Figure 1. Diagram showing the five hand force directions:
pulling backwards and pushing upwards, downwards,
forwards and sideways (A–E). The exertion is an
open-handed push or pull with the palm of the hand
centred on the opposing face of the force transducer.
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Ergonomics
moving bar on the screen met the threshold line. Offaxis force levels were monitored and kept below 5 N or
the trial was repeated. They were given ample practice
before commencing trials and collected force values
indicated that participants were capable of staying
within +5 N for each trial. Surface electromyographic
(EMG) signals were collected using the Noraxon
T2000 telemetered system (Noraxon, Scottsdale,
Arizona, USA). Force and electromyography were
measured at 1500 Hz, synchronised through the Vicon
Nexus 1.2 software (Oxford, UK). Target angles were
confirmed using a goniometer.
EMG signals were collected from 11 different sites,
overlying muscles on the right side of the upper
extremity using bi-polar Ag-AgCl Noraxon dual surface electrodes with a fixed 2 cm inter-electrode
spacing (Noraxon). Specifically, electrodes were placed
on the biceps brachii, triceps brachii, anterior deltoid,
middle deltoid, posterior deltoid, upper trapezius,
lower trapezius, latissimus dorsi, infraspinatus and
pectoralis major (both clavicular and sternal insertions) using published placements (Cram and Kasman
1998). Prior to electrode placement, the skin overlaying
the muscle was shaved and cleansed with alcohol to
minimise impedance.
2.3.
Experimental procedures
2.3.1. Experimental protocol
Muscle specific maximal voluntary exertions (MVEs)
were performed for the 11 muscles monitored using
the protocol recommended by Cram and Kasman
(1998). Each exertion was 5 s in duration, during
which participants ramped up to their maximum (1 s),
sustained their maximum (3 s) and then ramped down
(1 s). Participants performed three repetitions of each
MVE in order to increase the reliability of the results
(Fischer et al. 2009). In addition, there was a minimum
of 2 min rest between each exertion to minimise the
likelihood of fatigue and promote recovery (Mathiassen et al. 1995).
Following instrumentation set-up and the completion of the MVE protocol, participants were seated
under the force transducer. Three overhead work
parameters were manipulated: working configuration;
target angle; hand force direction. The work configuration variable was defined by either ‘fixed’ or ‘stature
scaled’. In the fixed condition, the transducer was
placed at 120 cm from the stool; independent of the
other two variables, the height of the force transducer
remained the same for all trials. This height was chosen
as it reflects the maximum reach distance of a 5th
percentile male and thus the study findings would be
germane to the entire working population (Chaffin
85
et al. 2006). It was also low enough to constitute an
overhead work location for the range of tested
statures. In the stature scaled condition, the transducer
spatial location was anthropometrically scaled to the
participant and was placed at a distance of 70% of the
participant’s maximum overhead reach, measured
vertically from the greater trochanter to the centre of
the palm. This distance was maintained along all target
angles (Figure 2).
Within each of the two work configurations, four
target angles were examined: 158; 08; 158; 308. These
angles were defined as the angle (with a positive
angle being a clockwise rotation) between vertically
upright and a line connecting the centre of the
participant’s pelvis (the 3-D centre of the greater
trochanters) to the centre of the force transducer,
while the participant was seated (Figure 2). Thus, a
08 target angle resulted in the transducer being
located directly overhead and positive angles creating
an overhead reach in front of the body and negative
angles behind the body. Within each target angle
participants exerted 30 N of force onto the force
transducer, in each of five globally defined hand
force directions: pushing forward, sideways (medial),
downward, upward, and pulling backward (Figure 1).
Each combination (work configuration-target
angle-hand force direction) lasted 5 s and was repeated
three times; all combinations were randomised. The
completion of the protocol entailed 120 sub-maximal
exertions: two work configurations 6 four target
angles 6 five hand force directions 6 three
repetitions. Participants were given a minimum of
1 min rest between trials, with the option of more rest
at their discretion.
2.3.2. Data analysis
Raw EMG signals were band pass filtered from
10–500 Hz and differentially amplified (common-mode
rejection ratio 4100 dB at 60 Hz, input impedance
100 MO) to generate maximum signal (in the range of
the A/D board). EMG signals were A/D converted
using a 16 bit A/D card with a +3.5 V range.
Following collection, EMG signals were full wave
rectified and filtered at 6 Hz (Dickerson et al. 2008)
using a fourth order low pass Butterworth filter to
produce a linear enveloped EMG response, then
normalised to MVEs outlined in the experimental
protocol. Within-trial means in normalised
electromyography were calculated for each muscle.
Then, the sum of all mean muscle activities during
each combination was calculated to give an estimate of
total shoulder effort for each trial. The rationale for
this calculation is the assumption that lower total
muscle activity may prevent potential injury and,
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86
J.N. Chopp et al.
Figure 2. Diagram showing both the fixed (top) and stature scaled (bottom) work configurations with target angles of 308, 158,
08, –15 (left to right). In the fixed configuration condition, the height of the force transducer remains consistent at 120 cm
from the stool. In the stature-specific condition, the cube is moved vertically and horizontally to maintain the hip–hand distance
at each specified angle (note the varying vertical location of the transducer relative to the participant).
thus, total activity gives a holistic representation of
muscular effort.
A 2 6 4 6 5 repeated measures ANOVA was
used to determine the effects of work configuration
(fixed and stature-scaled), target angle (7158, 08, 158,
308) and force application direction (forward, backward, upward, downward, sideways) on total normalised EMG activity. A p-value of 0.05 was used
to determine significance. Pairwise comparisons were
examined post hoc using a Tukey with Bonferroni
adjustments to ensure a strict p value, and reduce the
risk of type 1 error. Effect size was calculated using
the method outlined by Cohen (1988). All statistical
analysis was done using JMP software (SAS Institute,
Cary, NC, USA).
3.
Results
Significant influences of the tested factors, both main
effects and interactions, were found that included all
three manipulated condition levels (work configuration, target angle and hand force direction) for both
total and individual muscle activity.
3.1.
Total muscle effects
Work configuration, target angle and hand force
direction all independently and in conjunction influenced total muscle activity. Main effects of each of the
individual factors were present in work configuration
[F (1, 506) ¼ 28.5], target angle [F (3, 506) ¼ 11.4] and
direction [F (4, 506) ¼ 289.1]. Also, two-way
interaction effects were found between work
configuration and direction [F (4, 506) ¼ 19.4] and
target angle and direction [F (12, 506) ¼ 8.7]. The twoway interaction between work configuration and target
angle and the three-way interaction between work
configuration, target angle and direction were not
found to be overall significant (Table 1). Thus,
hereafter only interaction effects between work
configuration and direction, and target angle and
direction will be discussed.
3.1.1.
Work configuration * direction interaction
A statistically significant (p 5 0.05) interaction existed
between the two work configurations (fixed, stature
scaled) and five hand force directions (backwards,
forwards, downwards, sideways, upwards). The
combination with the highest total normalised
electromyography was pulling backwards at a fixed
configuration (total muscle activity ¼ 108.3%MVE)
(Figure 3). A distinct pattern existed for work
configuration–direction combinations. The level of
activity from highest to lowest was first dictated by
direction (backward, sideways, upwards, downwards,
forwards), but within each direction (for backward,
sideways and upwards) the fixed condition had
significantly higher activity than the stature scaled.
In contrast, the directions ‘downward’ and ‘forward’
87
F(12,506) ¼ 1.08
F(4,506) ¼ 1.02
F(3,506) ¼ 0.89
F(4,506) ¼ 1.62
F(3,506) ¼ 0.56
F(1,506) ¼ 1.09
Figure 3. Comparison of total muscle activity (11 muscles)
required to maintain 30 N of force between different work
configurations * directions of hand force interactions;
significantly different conditions (p 5 0.05) are indicated
by different letters. MVE ¼ maximum voluntary exertion.
showed no significant difference in activity between
each other for either work configuration (total
muscle activity ranged from 10.5 to 17.3%MVE for
fixed-forward to stature-downward respectively).
3.1.2.
Note: F ratios shown in bold indicate the main effects and interactions that were significant.
¼
¼
¼
¼
¼
¼
¼
¼
¼
¼
7.42
5.56
1.81
1.95
7.29
3.07
5.11
4.27
6.65
1.08
¼
¼
¼
¼
¼
¼
¼
¼
¼
¼
F(4,506) ¼ 5.59
F(4,506) ¼ 22.35
F(4,506) ¼ 2.19
F(4,506) ¼ 3.43
F(4,506) ¼ 3.86
F(4,506) ¼ 1.83
F(4,506) ¼ 21.63
F(4,506) ¼ 2.40
F(4,506) ¼ 11.58
F(4,506) ¼ 1.75
F (3,506) ¼ 4.31
F(3,506) ¼ 4.72
F(3,506) ¼ 2.58
F(3,506) ¼ 0.41
F(3,506) ¼ 1.25
F(3,506) ¼ 3.49
F(3,506) ¼ 9.27
F(3,506) ¼ 18.46
F(3,506) ¼ 2.48
F(3,506) ¼ 1.34
Anterior Deltoid
Middle Deltoid
Posterior Deltoid
Biceps
Triceps
Latissimus Dorsi
Upper Trapezius
Lower Trapezius
Infraspinatus
Pectoralis
Major (C)
Pectoralis
Major (S)
F(1,506) ¼ 4.07
F(1,506) ¼ 69.47
F(1,506) ¼ 2.18
F(1,506) ¼ 4.65
F(1,506) ¼ 2.67
F(1,506) ¼ 0.42
F(1,506) ¼ 53.87
F(1,506) ¼ 0.30
F(1,506) ¼ 12.68
F(1,506) ¼ 1.23
F(4,506) ¼ 227.93
F(4,506) ¼ 104.54
F(4,506) ¼ 3.00
F(4,506) ¼ 90.10
F(4,506) ¼ 31.31
F(4,506) ¼ 53.56
F(4,506) ¼ 156.11
F(4,506) ¼ 68.11
F(4,506) ¼ 232.61
F(4,506) ¼ 17.59
F(3,506) ¼ 0.27
F(3,506) ¼ 3.45
F(3, 506) ¼ 0.86
F(3,506) ¼ 0.73)
F(3,506) ¼ 2.87
F(3,506) ¼ 0.26
F(3,506) ¼ 3.70
F(3,506) ¼ 0.50
F(3,506) ¼ 0.63
F(3,506) ¼ 0.16
F(12,506) ¼ 1.18
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
F(12,506)
0.59
0.86
1.35
0.29
1.12
0.30
0.63
0.31
0.54
0.60
Configuration *
Angle * Direction
Angle * Direction
Configuration *
Direction
Configuration *
Angle
Direction
Angle
Configuration
Muscles
ANOVA results summary of all 11 muscles demonstrating main effects and interactions.
Table 1.
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Ergonomics
Target angle * direction interaction
A statistically significant (p 5 0.05) interaction existed
between the four angles (7158, 08, 158, 308) and five
hand force directions (backwards, forwards,
downwards, sideways, upwards). Pulling backwards at
angles of –158 and 08 showed the highest muscular
demand and were not significantly different from one
another (Figure 4). Further, higher muscle demand
was present when pulling backwards at the two
remaining angles than for any other hand force
direction. Within each angle, backward pulling and
sideways pushing produced higher muscle activity than
other directions. An exception to this was at a 308
target angle. At this angle, pushing upwards had
significantly higher activity (43.4%MVE) than
sideways (29.8%MVE).
3.2. Individual muscle contributions
Specific muscles contributed more toward achieving
30 N of hand force than others, with some having a
combination of significant main effects and
interactions (Table 1). Further, the activity elicited
from each muscle during work configuration–hand
force direction interactions and arm angle–hand force
direction interactions varied considerably. Specifically,
the work configuration–hand force direction
combination that resulted in the largest level of total
muscle activity was the ‘fixed configuration–backward
hand force direction’ combination. In this
88
J.N. Chopp et al.
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combination, certain muscles were far more activated
than in the combination that resulted in the lowest
level of total muscle activity (‘fixed configuration–
forward hand force direction’) (Figure 5). Anterior
deltoid, middle deltoid, biceps, lower trapezius and
infraspinatus had 90% higher activation during the
more ‘difficult’ work configuration–force combination
than the ‘easier’ combination; ‘difficult’ was defined as
the combination requiring the highest level of muscle
activity and ‘easy’ as the combination requiring the
lowest level of muscle activity. The remaining muscles
showed relatively minimal change in activity level
during different combinations.
The target angle–hand force direction combination
found to require the highest activation was ‘–158 target
angle–backward hand force direction’ and lowest
activation was ‘308 target angle–forwards hand force
direction’. Similar to the work configuration–hand
force interaction, anterior deltoid, middle deltoid,
biceps, lower trapezius and infraspinatus showed the
most variety between combinations, requiring the
highest activation compared to lowest activation,
with highest activation having 95% higher activity
(Figure 6).
4.
Discussion
Figure 4. Comparison of total muscle activity (sum of %
maximum voluntary exertion (MVE) for 11 muscles)
required to maintain 30 N of force between different target
angle * directions of hand force interactions; significant
differences between conditions (p 5 0.05) are indicated by a
difference in letters.
This research quantified shoulder muscle activity for a
variety of overhead working conditions to determine
how differences in overhead work configurations,
target angles and hand force directions influence
muscular demands. The magnitude of normalised
EMG activity was greater for the fixed height
configurations (anthropometrics not considered) and
when the target angle was –158 and when pulling
backwards (effect size ¼ 4.1–6.3). These results
highlight the utility of job modification to reduce
shoulder muscular demands during overhead work,
Figure 5. Comparison of individual muscle activity between
‘work configuration * hand force direction’ combination
requiring highest level of total muscle activity (fixed
configuration–backward hand force direction) and
combination requiring lowest level of total muscle activity
(fixed configuration–forward hand force direction) to
maintain 30 N of force. MVE ¼ maximum voluntary
exertion.
Figure 6. Comparison of individual muscle activity
between ‘target angle * hand force direction’ combination
requiring highest level of total muscle activity
(7158 target angle–backward hand force direction)
and combination requiring lowest level of total muscle
activity (308 target angle–forward hand force direction)
to maintain 30 N of force. MVE ¼ maximum
voluntary exertion.
89
Ergonomics
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particularly in cases when overhead work is not
entirely removable.
4.1. Work configuration in space
Although work configuration did not influence activity
to the same degree as hand force direction, the data
suggested a stature scaled (anthropometric) workstation can reduce muscle activity for overhead work
compared to a fixed working configuration (effect
size ¼ 0.79). This finding is particularly pronounced
with backward or sideways hand force directions
(Figure 3). The anthropometrically scaled condition
eliminated some excessive reaches and brought the task
to an equal distance from the worker (Figure 2). These
results coincide with Sood et al. (2007), who found that
an increase in muscle activity is required (for anterior
and middle deltoid) when the working height is moved
from low to high. Further research showed that
moving the task closer to the worker (moving up a
step on a ladder) reduced muscle activity (Anton et al.
2001). Other research has shown that by reducing
workstation dimensions, that is, by having a half reach
instead of a full reach and lower height (elbow
compared to shoulder), muscle activity was 3.5–3
times lower, respectively (Habes and Grant 1997).
The present results support this previous research,
which encourage the use of a scaled work design or a
reduced reach distance in order to decrease muscle
demands.
4.2.
Angle of work from directly overhead
As a main effect, target angle was found to be
significant. However, results show that target angle
interacts with hand force direction, in that certain
target angles yield higher muscle activity dependent
on hand force direction. Overhead arm angle has
been previously examined by Anton et al. (2001),
Haslegrave et al. (1997) and Garg et al. (2002). The
present findings are similar to Anton et al. (2001),
when the current data are limited to only the upward
push force direction at close (08) and far (308) target
angles (Figure 4). They only examined the effects of
overhead arm angle, using an upward drilling task and
were therefore not able to show the interactions
discovered in the current study when using alternate
force application directions at each of the angles. These
interactions are important for job design to provide
additional options for modification when the task is in
a specified overhead location, but the worker is not
constrained to a single posture.
Analysis of muscle activity while reaching to a
variety of overhead target angles provided insight into
the demand on the shoulder. This quantification
provided contrasting results with those examining
other biomechanical factors. Garg et al. (2002)
examined endurance times while holding various
weights statically at varied overhead arm angles. Their
research supports job design directed at minimising
the external shoulder moment, allowing for greater
endurance times. This is accomplished by reducing the
applied force at the hand or reducing the perpendicular
distance between the shoulder and the applied hand
load. In their case, the applied hand load acted
vertically downwards due to gravity; therefore, the
lowest perpendicular distance and resulting lowest
moments occurred when the arm was either placed
parallel to the torso at the side or directly overhead
(08). Their argument has limited application, however,
as it lacks information about specific muscles.
Although the moment created by external weights is
greater when the arm is farther from an overhead
position (in the case presented here at 308), this study
found less total muscle activation was required in these
forward reaches compared to when the target was
placed directly overhead (08).
The results from this study showed the target angle
of –158 (158 backwards) required the most muscle
activity (effect size ¼ 0.49–1.08), particularly when the
hand force direction was also pulling backwards
(Figure 4). Haslegrave et al. (1997) also examined the
location of overhead tasks: 158 forward, 158
backwards, 158 medially and 158 laterally with regard
to the vertical. Although forward and either side were
not significantly different from one another, overall,
participants had the lowest force capability in the
backward direction. The results from this study
compare with those of Haslegrave et al. (1997), as it is
likely that the capacity to produce a greater force in
the rearward angle position is less due to these
findings that there is less muscle activation in reserve
to increase force output.
4.3.
Applied hand force direction
Hand force direction was the most influential factor
affecting muscle activity during the overhead working
task examined. Most individual muscles had larger
mean EMG recordings for the backward direction
than for the forward and downward directions
(Figures 5, 6). Further, pulling backwards had a higher
level of total activity than all other hand force
directions (effect size ¼ 4.1–6.3). This may be due to
some gravitational assistance in pushing both forward
and downward. Simply resting or leaning the hand
on the force transducer in these directions may have
contributed to producing the 30 N of required hand
force (thus eliciting minimal shoulder muscle
demands). Conversely, in the backward pull, the
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90
J.N. Chopp et al.
muscles would need to not only contribute to both
the 30 N force, but also act to support the arm against
gravity.
Haslegrave et al. (1997) examined isometric
strength capability for six different directions of force
exertion (push, pull, medial, lateral, up, down) and
found participants were most capable in the vertical
direction (up or down). The results from this study
showed that a downward push required the least
muscle activity. Haslegrave et al. (1997) found that
force capability decreased as pushes moved from
vertical to horizontal (sagittal plane) and then to
lateral (frontal plane). A similar pattern was found in
this study, where activity was lower for those directions
that corresponded to the greatest strength capability,
with the exception of the backwards (horizontal)
direction, which required the most activity overall.
4.4. Relationship to fatigue
Determining a combination of working conditions that
lower muscular demand may, in turn, decrease the risk
of musculoskeletal injury. In exceeding the recommended arm angles (Bernard 1997) or exerting force
in unfavourable directions (i.e. backwards), one may
increase required muscle activity and in turn increase
the probability of fatigue development (Rohmert
1973). Sood et al. (2007) stated that localised muscle
fatigue is a valid concern when determining injury risk
and, therefore, attempts should be made to minimise
muscle activity and resulting fatigue. The present
findings dovetail well with Sood et al. (2007), as
the stature scaled work placement required less
muscle activity, which would likely be less fatiguing.
Further, the current results agree with recommendations that, if overhead work is unavoidable, all
attempts should be made to keep the work as close
to shoulder height as possible to reduce the likelihood
of sustaining shoulder fatigue or discomfort (Wiker
et al. 1989).
Further, lower apparent muscular requirements for a
stature-specific working condition support the
notion of population scalability in work design, a
stance historically advocated by ergonomists
(Nussbaum 2001). Positioning the task further in front
of the body (up to 308 forward from vertical)
required lower shoulder muscle activity than directly
overhead or behind the worker in nearly all cases.
Thus, working in a target angle range of 15–308 from
directly overhead is preferred when a forward or
downward force application is used. If an upward push
is required, then working directly above the head as
close to the body as possible minimises shoulder
muscular activity, but may pose issues with
line-of-sight and neck fatigue.
4.6.
Despite attempts to minimise the likelihood of error
with the study design, there were certain limitations
that should be addressed. Total muscle activity
was used as a surrogate for shoulder muscular load
and thus combinations resulting in higher total muscle
activity were considered ‘better’ in terms of lowering
the risk of upper extremity injury. There were,
however, trials in which total muscle activity was lower
but an individual muscle or muscles showed a greater
response. This discrepancy would make it difficult to
distinguish between advantageous and potentially
dangerous combinations. Additionally, it was decided
to perform the maximal exertions according to
specific recommendations (Cram and Kasman, 1998).
This is somewhat limited as EMG measurements are
influenced by local body posture. However, to perform
maximal exertions in each posture tested was
prohibitive for both fatigue generation and time
considerations. Thus, all trial values were normalised
by the defined maximal exertions with the
understanding of this limitation.
5.
4.5. Did any overhead work combination minimise
shoulder muscular demand?
When designing an overhead work task to minimise
muscular demands, many factors are important. In
order of greatest to least influence in the present
experiment, these were: 1) force direction; 2) positioning of the work interface; 3) angular work placement.
This study identified a benefit in terms of muscular
demand associated with generating forward or downward compared to backward applied hand forces
(or horizontal and up). Consequently, adjusting the
direction of applied hand force appears to yield the
largest benefits in terms of reducing muscle activity.
Limitations
Conclusion
Certain tasks or jobs intrinsically demand overhead
work postures. Therefore, it is important to determine
if an overhead working condition exists that lowers
muscular demand. The present results indicated
that muscle demands in low-intensity overhead tasks
are lowest when: 1) the required hand force is directed
either forwards or downwards; 2) the task is scaled
to individual anthropometry; 3) the task is moved
closer. These findings delineate the muscular impact of
performing overhead work across a range of
conditions and may therefore be useful as a part of job
design decisions where shoulder muscle demand is a
concern.
Ergonomics
Acknowledgements
Support for Jaclyn Chopp and Steven Fischer during
completion of this study came from a Hallman Research
Fellowship and an NSERC doctoral award, respectively.
Additional project support came from an NSERC discovery
grant held by Dr Clark Dickerson.
Downloaded By: [Canadian Research Knowledge Network] At: 20:26 18 January 2010
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