DETERMINATION OF EFFICIENT METHODS OF LIFT BY COMPARINQ TRAINED AND UNTRAINED MALE AND FEMALE LIFTERS by RICHARD H. SHANNON, B. S., M. Ed, A DISSERTATION IN INDUSTRIAL ENGINEERING Submitted to the Graduate Factilty of Texas Tech University in Partial Fulfillment of the Requirements for the Degree of DOCTOR OF PHILOSOPHY Approved A Accepted December, 1978
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DETERMINATION OF EFFICIENT METHODS OF LIFT
BY COMPARINQ TRAINED AND UNTRAINED
MALE AND FEMALE LIFTERS
by
RICHARD H. SHANNON, B. S., M. Ed,
A DISSERTATION
IN
INDUSTRIAL ENGINEERING
Submitted to the Graduate Factilty of Texas Tech University in Partial Fulfillment of the Requirements for
the Degree of
DOCTOR OF PHILOSOPHY
Approved
A
Accepted
December, 1978
^3/ c —t /
ACKNOWLEDGMENTS
I would like to express my indebtedness to my committee chairman.
Dr. M, M, Ayoub. Gratitude is also extended to Dr. C. E, George
(Psychology Minor Professor), Dr. J, D, Ramsey, Dr. S. S. Panwalkar,
and Dr, M, L. Smith, for their helpful advice and constructive
criticism. Thanks also goes to S. Morrisey for his on-site help
throughout the study due to m>' absence from the caiTq)us; and to rry wife
whose secretarial assistance helped to complete this project. Finally,
it is necessary also to thank those students who participated in the
experiment as test subjects.
ii
TABLE OF CONTENTS
Page
ACKNOWLEDGMENTS ii
nST OF TABLES iv
nST OF FIGURES vii
I. INTRODUCTION 1
Purpose and Scope 2
II. REVIEW OF LITERATURE h
Biomechanics , , . , . h
Lifting Injury and Prevention 7
Sex Variable 19
Training Variable 22
III. METHOD 27
Experimental Design . . . . . 27
Training Program 32
Data Collection 3h
Biomechanical Model liC
IV. RESULTS AND DISCUSSION 50
Biomechanical Model Validation 52
Multivariate Analysis 56
Analysis of Variance 69
t-Test Comparisons 39
V. CONCLUSIONS AND RECOMMENDATIONS FOR FUTURE RESEARCH . 102
Conclusions 102
Recommendations for Future Research 106
nST OF REFERENCES 108
APPENDIX 115
A. ACCEI£RATION PATTERNS OF THE BODILY SEGMENTS 116
B. ANALYSIS OF FORCE AND ELBCTROMYOGRAM DATA 12U
iii
LIST OF TABLES
Table Page
1. Worker Descriptive Breakdown of ii8ii Injuries While
Handling Manual Materials 11
2. Task Descriptive Breakdown of h% Injuries While
Handling Manual Materials 12
3. Human Error Causes of liSIi Injuries While Handling
Manual Materials 13
ii. Acceptable Weight of Lift for Males and Females 16
5. Anthropometric Data for the Experimental Subjects . . . . 28
6. Experimental Sequence of Weight and Lift Type
by Subjects 33
7. Kolroogorov-Smirnov Test of Joint Displacement -
Time Relationship for Actual Versus Theoretical
Data During Floor-Knuckle and Knuckle-Shoulder
(Combined Group) Lifts Sh
8. Kolmogorov-Smirnov Test of Resultant Force Differences
Over Time Between Force Platform and Photography Data
for Both (Combined Group) Lifts 55
9. Correlational Matrix for the Floor-Knuckle Lift 57
10. Correlational Matrix for Knuckle-Shoulder Lift 56
11. Stepwise Regression Predicting Inertial Force in the
Y-Axis at the Hand Using Force Platform and Electromyogram
Variables as Predictors (Floor-Knuckle Lift) 60
12. Stepwise Regression Predicting Inertial Force in X-Axis
at the Hand Using Force Platform and Electromyogram
Variables as Predictors (Floor-Knuckle Lift) 60
13. Stepwise Regression Predicting Inertial Force in the
Y-Axis at the Hand Using Force Platform and Electromyogram
Variables as Predictors (Knuckle-Shoulder Lift) 61
Iii. Stepwise Regression Predicting Inertial Force in X-Axis
at the Hand Using Force Platform and Electromyogram
Variables as Predictors (Knuckle-Shoulder Lift) 61
iv
15. Stepwise Regression Predicting Inert ia l Force in Y-Axis
at the Hand Using Movement Variables as Predictors
(Floor-Knuckle Lift) 62
16. Stepwise Regression Predicting Inert ial Force in X-Axis
at the Hand Using Movement Variables as Predictors
(Floor-Knuckle Lift) 62
17. Stepwise Regression Predicting Inert ia l Force in Y-Axis
at the Hand Using Movement Variables as Predictors
(Knuckle-Shoulder Lift) 63
18. Stepwise Regression Predicting Inert ia l Force in X-Axis
at the Hand Using Movement Variables as Predictors
(Knuckle-Shoulder Lift) 63
19. Factor Matrix and Loadings for Floor-Knuckle Lift . . . 66
20. Factor Matrix and Loadings for Knuckle-Shoulder Lift . . 67
The sequence of administration first depended upon the subjects
being assigned to a sex/progranj/group (ACF) combination. The order of
weight trials were then randomly selected for each of the four subjects
within a combination. There were six possible sequences of weight,
with the four subjects being randomly assigned to one of these six
permutations. There were no repetitions within an ACF combination.
Finally, the two lift regimes of floor-knuckle (F-K) and knuckle-
shoulder (K-S) were counterbalanced within each sex/training combination,
with the sequence order of weight being the same in each regime. This
information concerning order of weight and of lift type for each subject
is presented in Table 6. As an example using Female/Control, subject 1
Experimental group, E) lifted weight in the order of iiO, 25, 10 pounds,
while subject 5 (validation group, V) was given the sequence of 25, 10,
iiO pounds. Order of lift type for subject 1 was knuckle-shoulder and
floor-knuckle, while subject 5 had the reverse arrangement.
The sequence of administration just explained is very similar to
the procedure for a split-plot design recomonended by Kirk (1968). The
time and measure treatments (B, E) in this study, however, precluded
randomization of presentation order due to their sequence being dictated
by the e:q>erimental design. The order effects over time (treatment B)
during a lift were of interest because of the stated goals of studying
coordination, rhythm and efficiency. The use of a control group was an
atteirpt to cancel out order differences between pre- and post-measures
(treatment E).
Training Program
The training program consisted of two males and two females in each
replication group lifting 10, 25 and iiO pound weights in floor to knuckle
and knuckle to shoulder lift regimes for fourteen practice periods.
During each session, subjects in the training program lifted each weight
by regime approximately six to eight times. The lighter weight was
33
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lifted more than the heavier weight. This totaled to e^proximately ii2
lifts per subject per session.
The e^qperimenter was present during all of the training sessions,
and aided in the instruction with verbal comment. The training program
relied on certain ideas from the literature (items 1-ii from Tichauer,
1973):
1, Avoid unnecessary abduction of the upper arm,
2, Keep the moments acting on the vertebral column low by
enphasizing movement toward rather than away from the body,
3, Maintain wrist and forearm alignment while moving the arm.
U, Strive for a musculo-skeletal configuration which would increase
biomechanical efficiency.
5. Repetitive trial and error motion should result in an individ
ual's adaptation toward efficiency, economy and optimization (Ayoub,
1971),
6, A lifting method similar to the one recomontended by the National
Safety Council (197ii) was enqphasized. This technique relies on balance,
initial thrust and keeping the load close to the body,
7. Coordination between and rhythm within body segments were
stressed in order to increase motion efficiency (Komarek, 1 9 6 8 ) ,
8, The performance of loosening and stretching exercises prior to
each training and experimental session was thought to be necessary in
order to avoid injury and to increase body awareness (Galton, 1 9 7 8 ) ,
3y en5)hasizing these rules repeatedly, it was expected that each
trained subject would optimize his performance by minimizing unnecessary
movements. The goal of the program was to improve technique rather than
to have aniscular development. There was never any atten5)t to stress,
fatigue or motivate the subject to complete more work tdian he or she
wanted to do or was capable of doing. The trained lift when compared to
the untrained one was meant to be purposeful, accurate and rational, and
therefore, the more efficient.
Data Collection
Data collection entailed the use of stroboscopic photography, force
platform and electromyogram (EMG) methodologies. The equipment consisted
35
of a still camera, lights and a rotating disc with equally spaced
apertures for photography; a force plate and Beckman Offner T^e "R"
dynagraph for force recordings; Sanborn integrating preamplifier (Model
350-3700) and Beckman miniature surface electrodes (5" diameter) for
EMJJ and weights and barbell. The data from these lifts were collected
by two people throughout the experiment, one taking pictures and the
other handling the dynagraph and preamplifier.
Lights were taped to the skin at the centers of the hip, knee,
ankle, shoulder, elbow and wrist joints, as well as a light attachment
at the center of the weight. Exact location of these centers were
described by Plagenhoef (1971), He indicated that these positions can
be found by using the skin crease that results from bending the joint.
A still camera, whose lens was placed inside of a box with a
rotating disc of equally spaced openings (.125 second apart), was
manually operated during the experiment. This box rested on a table
with the camera centered at the middle of the subject's body. The
camera's shutter speed was placed on "B" to keep the lens open during
the lifts in order to double expose equally spaced strobe light movements
onto the negatives, Kodak Tri-I pan black and white film was used be
cause of its sensitivity. The lens' aperture opening was set at "F 11",
A series of pictures had previously been taken under experimental con
ditions and varying aperture openings in order to determine this "F"
setting. The resulting negatives of the experimental lifts provided
angular displacement-time data from the lighted movements of the joints
and weight. With this information computations of velocity, acceleration
and force profiles were accomplished using El-Bassoussi's biomechanical
model (197ii), which is described in the next subsection of this chapter,
Electromyograms in arbitrary units were collected on two muscles -
middle deltoid and rectus femoris. The deltoid is a thick triangular
muscle which covers the shoulder joint. This muscle arises from the
clavicle, acromion process, and the spine of the scapula, and is inserted
into the lateral side of the body of the humerus (Kimber and Gray, 1956),
There are three muscles in this group - anterior, middle, posterior. The
main function of this muscle group is that of shoulder abduction (Kelley,
36
1971). The rectus femoris is one of four muscles conqprising the
quadriceps femoris. The rectus muscle arises by two tendons, one from
the anterior inferior iliac spine and the other from a groove above the
brim of the acetabulum (Kimber and Gray, 1956), The function of this
muscle is to extend the knee and flex the hip (Kelley, 1971),
These two groups of muscles have been analyzed by various
researchers, Shinno (1968) determined from his studies that the
quadriceps femoris was the prime mover to extend the knee; and that in
the semi-flexed position, the stability of the knee depended mainly
upon this muscle's power, Desipres (197ii) studied the effect of saddle
height and load on muscle activity during road riding on a treadmill.
The results indicated that quadriceps femoris activity intensified with
increasing incline slope, Leggett and Waterland (1973) studied anterior
and posterior deltoid muscle action during skilled gymnastic movements,
while s\q>ported by the hands. From previous research, they hypothesized
that skilled subjects would use only those muscles necessary to task
performance, and that all parts of the deltoid would be active during
abduction, flexion, and extension. Their findings indicated that only
the posterior deltoid showed activity at all times, Hobart and Vorro
(197ii) analyzed posterior and anterior deltoid electrical activity during
the acquisition of an underhanded ball toss task with the arm extended
and the hand pronated. Commencement and peaking of activity for both
muscles coincided very closely with the beginning of arm and shoulder
movement.
During the experiment, two pairs of miniature electromyographic
surface electrodes (Beckman, ig" diameter) were attached to the right
side of each muscle so as to measure its activity. Both probes were
placed approximately in the center of the muscle (horizontal and
vertical), one and one half inches apart, with one directly above the
other. The skin of the subjects was throughly cleansed with alcohol
prior to placement of the electrodes in order to lower skin resistance.
The ground was placed on the clavicle,
A dye marker was used to initially mark the position where the
electrodes were to be placed, A paper tracing of these markings was
37
made using the shoulder and knee joints as reference points. During
the second measurement session (post-training), these tracings were
copied onto the subject's skin for electrode placement. In this way,
electrode attachment was standardized for both observational periods.
The Sanborn integrating preamplifier. Model 350-3700, was used in
the area sxiramation mode. This meant that the integrated output voltage
curve for each lift represented only the positive input signals. The
measurement of muscular activity over time was directly related to the
area under the curve. The data were read directly from the graph paper
in arbitrary units for each incremental time period.
Prior to collecting electromyographic data, the preamplifier was
calibrated to ensure that sensitivity and reading output were the same.
Switches and controls were standardized throughout the experiment:
sensitivity (1 volt-second), attenuator (X 10), and gr^h paper speed
(1 cn\/sec). Two channels were used, one for the medial deltoid and the
other for the rectus femoris.
After completion of each measurement session, the subject was told
to sit down and relax. Another set of readings in an unstressed con
dition (legs on chair, hands in lap) were collected. These unstressed
curves represented measurement error; such as heart rate, muscular
tension and equipment noise. During data analysis, the unstressed
muscular baselines were subtracted from the stressed muscular outputs.
A Beckman Offner Type "R" dynagraph and force platform were used
to record force changes at the feet in arbitrary units over time in
three reference planes - sagittal or frontal (forward/backward), coronal
or lateral (left/right), and transverse or vertical (up/down). Prior to
data collection, the "experimental position" was marked on the platform,
which then functioned as a reference throughout the session. This
position was found by:
1, locating the intersection of the force platform's center and
the subject's mid-sagittal and coronal planes,
2. having the subject stand erect in a balanced position with
feet comfortably apart.
The three channels on the dynagraph were then zeroed and the paper speed
set at 1 cnj/sec.
38
Data output was in terms of shifting force (+ and -) across a
zero baseline. This baseline was either the initial or final positions,
respectively, for the knuckle-shoulder or floor-knuckle lifts. In this
way, the "experimental position" plus weight became the reference base
line. The amount of peak variations above and below the line within
each of the five time intervals were converted from arbitrary units to
pounds of force. These conversion estimates had been previously
determined using static weights to calibrate the force platform in
each of the three planes. The study of peak forces from the platform
were previously used by other researchers at Kansas State University
(Desai, 1976; Parker, 1976; Perkins and Konz, 197ii), The positive
and negative changes in each reference plane on the recording paper
represented force changes in specific directions. These directions
are listed below:
positive negative
Frontal backward forward
Lateral right left
Vertical downward upward
Various experiments at Kansas State University have used the same
force platform to determine the effects of weight and distance from
center of platform (Desai, 1976); height of movement, angle of bodily
rotation and box volume (Parker, 1976); height of lift, weight of box
and box distance from center of gravity of the subject (Perkins and
Konz, 197ii), Six types of data were recorded continuously on this
platform during a lift: forces in the frontal, vertical and lateral
axes, and torques about these axes. The platform is zeroed for body
weight with the subject standing motionless in the middle. The results
of these investigations can be summarized as follows (Desai 1 - 3>
Parker ii, Perkins et al, 5 - 8 ) ;
1, Vertical forces for the three weight conditions (5, 10, 15 kg)
were significantly different in the floor to knuckle lift.
2, Vertical force increased as weight lifted increased,
3, Bend lift was recommended because the distance between body
and load were minimized.
39
ii. Forces and torques decreased with height of movement, and
increased with box volume and angle of bodily rotation.
5. The change in box weight from 11 to 22 pounds caused a
minimal increase in vertical peak force from iiii,9 to ii8.1 pounds.
6. Height of lift and initial height position were in^ortant
variables in the experiment.
7. For lifts in the sagittal plane, peak vertical force was
more important than frontal or lateral forces.
8. Peak forces occurred in the ,5 second before and after grasp-
the load.
In another experiment force platform and oxygen consuirqption were
used to analyze the walking gait in terms of patterns and magnitudes
of force (Ismail, 1968), Five measures were used - frontal, lateral,
and vertical forces; coD5)osite force (square root of the summation of
the three forces squared); and total force (sum of three forces). The
t-test was used to compare the force patterns of the different ages
and body builds, while correlational procedures were en^loyed in
determining the best predictors of energy cost using force variable
data. The following conclusions were observed;
1. Age and weight variables influenced the magnitude of the forces.
2. Total force, followed by vertical and composite, were the best
discriminators between subjects.
3. Oxygen consumption was predicted by force platform and bodily
physique data.
The last topic of discussion in this section is the experimental
procedure. Prior to "Uie placing of electrodes, the subject was allowed
a familiarization or warm-up period of 15 minutes, which involved
calisthenics and lifting each weight (10, 25, iiO lbs.) three times in
each height regime. This meant a total of eighteen lifts. This warm-up
phase was an experimental attenqpt to avoid subject differences between
trials. Each individual was then connected with electrodes and posi
tioned on the force platform. Following this, the equipment was
calibrated and checked.
During the experiment, each person performed three lifts with each
weight in each regime. There was a total of 18 lifts per subject. The
iiO
first lift was a practice one, while data were collected on the second
and third lifts. The sequence of weight lifted by one subject was
randomly selected, and maintained across both regimes. At each weight
level, both lifts were observed prior to proceeding to the next experi
mental weight condition.
When the observations involved the floor to knuckle lift, each
person was told to crouch to a comfortable position with the barbell
weight on the floor. On the word "Go", the subject proceeded to lift
the weight to a knuckle height. He or she then halted, relaxed and let
the experimenter take the weight. The load was placed on the floor.
After a time lapse of one minute, this procedure began again.
When the knuckle to shoulder was the observed regime, the weight
was handed to the individual at knuckle height. On the word "Go",
the subject lifted the weight to a shoulder position. He or she then
halted, and waited for the experimenter to take the weight. After one
minute, the procedure began again. In this way, 18 lifts encompassing
three weight conditions and two regimes were cow5)leted with rest
periods between trials.
Biomechanical Model
A model is a representation of an object or system. This repre
sentation should reasonably explain, measure, or predict reality with
some degree of accuracy i^ile still being sin^ler than the imitated
system (Ayoub, Dryden, McDaniel, 197ii). The model to be discussed is
one that determines inertial forces and linear accelerations at
various segments of the body during a dynamic motion task, such as
lifting weight. The model's rationale and equations, as used in the
present paper, were previously developed by El-Bassoussi (197ii),
In order to sin?)lify the dynamic analysis of the data, the
following assumptions were made;
1. The human body is composed of rigid links,
2. These links are joined at articulation points or joints.
3. The lower arm and hand, because they remain aligned during
motion, were considered as one link in the analysis. The same was true
la of the arm during the floor-knuckle lift and leg during knuckle-
shoulder lift, since the upper and lower portions of these appendages
moved similarly.
ii. The density and geometrical shape of a segment remained
uniform throughout the lift,
5. Rotation occurred only about the sagittal plane.
6, Segmental motion was considered circular and the radius of
rotation was constant.
7. Displacement between the joints and their connecting links
was negligible.
8, The ankle remained fixed in one position throughout a lift.
The first step in determining the linear accelerations and
inertial forces was to analyze the film negatives which were collected
during the experiment. The negatives were presented as slides on a
wall by means of a projector, A white piece of paper was affixed to
the wall. The projection of the lighted joints were then traced onto
the paper. Every other light per joint was marked to represent .25
second time intervals. These marks were then joined, which produced a
stick drawing of the body moving over time. Angular displacements were
found by measuring the angles between each joint's segments. In all,
each floor-knuckle lift had six angular displacements (0, .25, .5, .75,
1.0, 1,25 seconds) for each of the following joints - ankle, knee, hip
and shoulder. The knuckle-shoulder lift collected data on the ankle,
hip, shoulder and elbow joints.
The use of a fixed total time of motion was determined by measur
ing all of the times in both lifts, A value was selected (1.25 sees.)
which included 75% of all the data. The 25% of the data that deviated
from the set limitation were not that much above the 1,25 second value
to significantly change the results. In addition, most of the remain
ing 75% of the total data terminated motion within the final time
interval of 1,00 to 1,25 seconds. The total time used in the analysis
of each segment, therefore, was the total difference between start and
end of motion or 1,25 seconds,
El-Bassoussi's (197ii) handling of the total time parameter is in
general agreement with the strategy used in this study. Although his
ii2
investigation was concerned with continuous data from a motion camera
and the present report studied discrete time intervals, data analyses
in both cases appear to be similar. He used the Slote and Stone (1963)
equations to study the leg lift (similar to floor-knuckle and knuckle-
shoulder lifts combined) only during the following average ranges:
Knee joint - from 0% to 80% of total lift time
Hip joint - from 0% to 85% of total lift time
Shoulder joint - from 5% to 100% of total lift time
Elbow joint - from 15% to 92% of total lift time
Wrist joint - from 12% to 88% of total lift time
Velocity and acceleration were zero, therefore, on either side of these
average ranges for a particular articulation. The present study selected
five fixed time intervals (0 - .25, .26 - .50, .51 - .75, .76 - 1,00,
1.01 - 1.25 seconds) in order to avoid some of the problems associated
with the analysis of continuous data and to facilitate data handling.
The displacement - time relationship of Slote-Stone (1963) was used
in the next phase of the calculations. Instanteous angular displacement
during forearm flexion is seen in this equation as being of equal
increments of total displacement in radians. These increments of
displacement are determined from the relationship between the incre
mental time period to total time of movement. Angiilar velocity and
angular acceleration are the first and second derivatives with respect
to time of the angular displacement equation. Angular velocity is
described as increasing from zero to a maximum and then decreasing to
zero. Angular acceleration, on the other hand, is seen in two periods
of zero to maximum to zero. These periods are called acceleration and
deceleration, El-Bassoussi (197ii), by coD?>aring his observed experi
mental displacements with the predicted angles, demonstrated that the
Slote-Stone space-time relationship was valid for the determination of
angular displacement. These equations are as follows:
Angular Displacement (time i) - ^ ( ^ ^ - sin ^ ) 27r T T
Angular Velocity (time i) - ^ ^ ( 1 - cos ^ ^ i ) T T
ii3
Angular Acceleration (time i) - ^ ^^"^ sin ^ ^ i 2
T^ T
where; Dmax » maximum angular displacement,radians
T « total displacement time, seconds
t. » incremental time, seconds
Since lifting tasks are circular, instantaneous acceleration can
be divided into two components, normal and tangential. The normal
component's vector is parallel to the segment's frame but is directed
toward the center of rotation. The value of the normal component is
equal to the product of the radius of curvature and the angular
velocity. The tangential component's vector is tangent to and in the
direction of the rotational axis. Its value is equal to the product
of the radius of curvatiire and the angular acceleration. In addition,
each component of instantaneous acceleration can be separated into the
horizontal and vertical planes. Figure 2 depicts the separation of
the angular acceleration for the lower leg during the floor-knuckle
lift into these six components and planes. Signs for the direction of
these accelerations have the following pattern: y-axis is positive up
and negative down; x-axis is positive backward and negative forward.
The combinations of the x and y planes for the normal and tangential
components form the linear accelerations for each of these axes. As
an exaii5>le using Figure 2, both of these equations for the lower leg
are:
Linear Acceleration,
X Axis • rad M a n g ace)sin(angle)+(ang vel) cos(angle) J
Linear Acceleration,
Y Axis » rad]](ang ace) cos (angle)-(ang vel) sin(angle)J
where; rad « radius of curvature, cm
angle » transformed angular displacement, radians
ang vel • angular velocity, crr/sec 2
ang ace « angular acceleration, cn\/sec
The angles used in the above equation are transformed from the
angular displacement values ( i ) . These transformations measxire the
HIP /Z
hh
CG ARM (combined upper and lower arm )
CG ARM/WEIGHT
Angular Displacement
Segment Center of Gravity
Rotational Direction
Tangential Component of Angular Acceleration
Normal Conponent of Angular Acceleration
X Axis Components of Angular Acceleration
Y Axis Components of Angular Acceleration
ANKLE
FIGURE 2. Floor to knuckle lift containing angular displacements, directions of rotation, centers of gravity for each segment, translational acceleration for the lower leg.
ii5
angles between the horizontal axis and the next highest segment. These
values in radians are determined as follows;
angle, ankle • Z.
angle, knee ' Z^ - angle, ankle
angle, hip » Z - angle, knee
angle, shoulder « 180 - Z, - angle, hip
In order to determine radius of curvature, two measures are used -
segment length and distance to center of gravity. Center of gravity
values are determined from percentages of segment length. These
percentiles are taken from data published by El-Bassoussi (197ii).
Center of gravity lengths are:
lower leg (LL); r^ - R^ (.567)
upper leg (UL); r^ - R^ (.567)
trunk (TR); r^ = R^ (.396)
arm (A); r^ « R^ (,530)
amv^wt (W); t " i. * wrist to weight distance
where; r = distance from articulation to center of gravity
R « segment length, distance between both joints.
As mentioned previously, linear acceleration is found by combining
tangential (T) and normal (N) components in either x or y planes.
Using a shortened version of the linear acceleration equation depicted
previously, the con5)utations for each of the segments are:
X axis accelerations -
LL (r) or LL (R) - r^ or R^ (T • N)
UL (r) or UL (R) - r^ or R^t- (T + N)]
TR (r) or TR (R) » r^ or R^ (T + N)
A (r) - r, (T • N)
W (r) - r^ (T • N)
ii6
Y axis accelerations -
LL (r) or LL (R) » r^ or R^ (T -
UL (r) or UL (R) » r^ or R^ (T -
TR (r) or TR (R) - r or R (T -
A (r) - r^ C -(T -
W (r) = r^ [-(T -
N)
N)
N)
N)
N)
] 3
where; T « tangential component; T in X plane = (ang ace) sin (angle);
and T in Y plane = (ang ace) cos (angle)
N « normal conqponent; N in X plane » (ang vel) cos (angle);
and N in Y plane • (ang vel)^ sin (angle)
Since linear acceleration of a particular segment is due to its
rotation about all preceding joints, these acceleration values are:
LL = LL (r)
UL = LL (R) + UL (r)
TR » LL (R) • UL (R) •• TR (r)
A » LL (R) • UL (R) • TR (R) • A (r)
W « LL (R) • UL (R) • TR (R) • W (r)
The final computations were those of inertial force at each of the
links in the x or y planes. Important to these calculations is the
determination of segment weight from data published by Plagenhoef (1971),
These values are percentages of total body weight by segment and are as
follows:
hands
forearm
upper arm
lower leg
upper leg
trunk
Males
1,3
3.8
6,6
9.0
21.0
38.1
Females
1.0
3.1
6,0
10.5
23.0
ii6.6
At each link, inertial force is found directly from its weight.
In the case of the hand holding the load, the additional value of either
10, 25 or iiO pounds would be added to the weight of the hand as follows:
SHOULDER
CG UPPER ARM
CG TRUNK
HIP L Z
(combined upper and lower leg)
CG LEG
ANKLE
CG LOWER ARM
ii7
CG LOWER ARM/WEIGHT
SYMBOLOGY:
' Angular Displacement
CG = Segment Center of Gravity
• Rotational Direction
FIGURE 3: Knuckle to shoulder lift containing angular displacements, directions of rotation, centers of gravity for each segment.
The final mriltivariate technique to be discussed is factor
analysis. Gattell (1966) outlined a conceptual model for factor
analysis that involved alternating the emphasis of the investigation
between three dimensions: people, conditions, and time. According
to Cattail's model the methodology used in the present research can
be called the "P" technique. As seen from the data box, the testing
conditions are treated as variables, the time segments as cases and
people as constants. In this approach, the resultant factors are
clusters of variables as they covary over time.
Separate analyses were performed on both lift regimes. The
principal axis method was conducted using the EMD package, BMD 08 M,
at the Texas Tech Coit?)uter Center (Dixon, 197U). This method operates
to maximize the amount of variance shared commonly among the factors.
Factoring was halted when the Eigenvalue slipped below 1,0, Accord
ingly, two factors explaining 58^ of the variance and three factors
with 53% communality resulted, respectively, for the floor to knuckle
and knuckle to shoulder lifts,
Varimax rotation was performed so that each variable loaded
mainly on only one factor. In this way, factorial interpretation is
as sin jle as possible. Tables 19 and 20 contain the results of the
statistical rotation with the variable loadings outlined by factor and
group. In the floor-knuckle lifts, factor I was represented by move
ment in the X axis, while factor II was defined by changes in the y
axis. Factor III in the knuckle-shoulder regime stood for x axis
movement. Trunk/upper arm/leg and lower arm/hand movements in the
y axis, respectively, defined factors IV and V,
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Some principles concerning the properties of factor loadings
will now be presented. A factor loading is similar to a correlation
coefficient. The square of the loading indicates the amount of
variance explained by a variable on a factor. The sum of the squares
in any column gives the total amount of variance by a factor, while
the average of these squared loadings depicts the proportion of total
variance. The sum of squared loadings in a row (h2) shows the pro
portion of variance by a variable on all of the factors. The higher
the h2, the more common variance a variable shares with the other
variables (Nunnally, 1967),
The remaining step, prior to utilizing the factor-variables in
the forthcoming analyses, is to conpare the factor structure in both
the experimental and validation sanqples. Nunnally (1967) claimed that
the proper method of factor comparison is to use factor scores from two
different analyses. This can be accon^lished if the same people are
involved in both factor structures. Since this was the case, the factor
scores for each person in two data sets were correlated and the com
parability of the factors were judged by the size of the relationships.
The mean factor scores in the "pre" and "post" condition (N » 32) for
each subject in either replication (experimental and validation) and
combined group were correlated using the Spearman Rank Correlation
Coefficient (Siegel, 1956). This coefficient closely approximates
the product-moment correlation in sanples larger than 30. This test
involves ranking the subjects in both groups and squaring the sub
tracted difference (d). The correlation then is computed using the
following formula (N - 32):
, 6 (sum of squared differences)
N- - N
The results indicated a high similarity between both factor structures,
and gave support to the validity of the loadings used in the combined
saji5)le. The following correlations by factor and significance level
can be shown below:
Correlation
.751
.911
.360
.685
.915
Probability Level
,001
,001
.05
.001
.001
69
Factor
I
II
III
IV
V
In summary, the analyses so far have a good deal of predictive
and concurrent validity. Using a two group replication approach,
the correlation, regression and factor analytic results appear to
have been cross-validated. The product of these efforts were:
(1) four equations (2 axes, 2 lifts) using force platform and
electromyogram data to predict inertial forces at the hands.
(2) fo\ir equations relating bodily acceleration patterns and
inertial forces at the hands.
(3) a five-factor model or construct of motion describing two
different types of lifts.
Analysis of Variance
Five split-plot analysis of variance (SPF 22»532 and SPF 222*532)
tests of the five factors were performed on each of the replication
groups (experimental, validation, combined) in each regime. The Texas
Tech Conputer Center's SAS-76 package for ANOVA (Barr et al, 1976) was
utilized in the analyses. The dependent variables were the five factor-
variables determined from multivariate statistics in the previous sub
section. The resulting factor scores for each factor were the data
studied in the con5)utations. The factor score for each case was found
by adding the products of the loadings and standard scores on each of
the fifteen variables. The result was a score for every case on the
one factor extracted. A case was equal to a specific subject, trial
and combination of the following independent variables: sex (A),
time (B), program (C), weight (D), measure (E), group (F). In all,
there were 960 cases. A high positive factor score indicated that a
case related highly with a factor, while the reverse was true for a
high negative score (Lawlis and Chatfield, 197U).
The following three levels of testing were conducted in these
analyses:
70
(1) the effects of the independent variables upon the five factor-
variables of the experimental, validation and combined groups (Tables
21 - 25).
(2) single main effects tests to study further the significant
interactions (Table 26 - 29).
(3) Tukey tests to con^are means among levels of the significant
main or simple main effects (Tables 30 - 33).
Care was taken during these analyses to avoid both Types I and II
errors. Type II error (determination of non-significance when in fact
significant) was kept small by making the preliminary tests on each
replication (experimental, validation) at an "alpha" level of .25
(Winer, 1971). Also to be significant, a main effect or interaction
had to be beyond the "alpha" level for the combined group's ANOVA.
In other words, these levels changed as the level of testing changed
(.25 for experimental and validation, while .1 for combined). Type I
error (rejection of the null hypothesis when it is true) was partially
controlled by varying the levels of significance with the number of
observations tested. The procedure recommended by Kirk (1968) was to
assign the same error rate to the simple main-effects tests as that
given to the overall F-ratio. The various cor^arison tests among
means were treated similarly. The following equation, therefore, was
used to set the "alpha" level at the various stages of testing:
•l/number of observations • alpha. The use of replication groups and
changes in the levels of significance as the analysis progressed
should have increased experimental validity. The initial willingness
to commit a Type I vice a Type II error hopefully insured that all
avenues of possible scrutiny were included in the data pool. As the
testing advanced, the use of more stringent levels of significance
should have helped to curtail Type I error.
Tables 21 to 25 contain the ANOVA results from each factor on the
three san5)les. Each factor-variable is signified by:
Factor I - movement in x axis, floor-knuckle lift (F-K)
Factor II - movement in y axis, floor-knuckle lift
Factor III - movement in x axis, knuckle-shoulder lift (K-S)
71
Factor IV - movement of leg, trunk and upper arm segments in
y axis, knuckle-shoulder lift
Factor V - movement of lower arm and hand segments in y axis,
knuckle-shoulder lift
Pooling procedures were used in this part of the investigation. All
sources of interaction that were not of interest to the experimenter
or did not contribute significantly to the total variation became part
of the error term. The use of both replication groups to determine
the final model in the combined group analysis was very similar to the
"middle-of-the-road" position concerning pooling taken by Winer (1971)
and Kirk (1968). Also, replication interactions were pooled into the
error term (Winer, 1971).
An examination of these five Tables shows that the results contain
some F ratios of less than 1.0, This could be the result of chance but
it could also be caused by a failure to meet some of the assumptions of
the fixed-effects linear model. However, since the F distribution is
robust with respect to moderate deviations of normality and of homo
geneity of error variance, the magnitude of Type I error should not be
greatly influenced (Kirk, 1968; Winer, 1971). Failure to meet these
assumptions can affect the sensitivity and the significance level of
the test (Cochran and Cox, 1957). However, the care taken to avoid
experimental error, the large sample size and the ANOVA's function of
serving only as a screening device were strategies purposely used in
this investigation to avoid some of these pitfalls.
Tables 26 to 29 depict the next level of analyses, which were
sinqple effects tests. Those interactions deemed significant by the
first series of ANOVA's were now further scrutinized. These inter
actions were time/weight (BD) for factors I, IV, V; sex/time (AB) for
factors II, IV, Vj sex/weight (AD) for factor V; and time/program/
measure (BCE) for factors II, V, These tables are labeled as
"inconqplete" because only the pertinent information are contained in
them. The levels of significance varied with the number of observa
tions per interaction. The following probability levels were used in
these analyses:
,05 - B at a, D at a
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81
.033 - B at d, A at d
.025 - B at ce
.02 - D at b, A at b, CE at b
The error terms depicted in Tables 21 - 25 were "pooled within sub
jects" and "subjects within groups". In Tables 26 - 29, the "pooled
within subjects" error term was the same. However, the "within cell
pooled" error was a weighted average of the "pooled within subjects"
and "subjects within groups" errors.
The last levels of analysis are shown in Tables 30 to 33. Tukey
A Posteriori tests were used to conpare the differences between the
means of the time treatment and the time/weight, sex/time, sex/weight
and time/program/measure interactions. Again, the level of signifi
cance was dependent upon ,1 (level of overall combined group signifi
cance) divided by the number of observations. Since there could have
been 6, 8, 15 and 20 observations, respectively, for the AD, AB, BD
and BCE interactions, .01 was set as the best approximate level of
"alpha" in these tests. The Tukey test statistic is given by Kirk
(1968):
mean, - mean.
V MS of ce
error term cell size
The value of "q" changes with the number of means conpared, for exanple
using the .01 level:
2 comparisons (A treatment) - 3.6U
3 comparisons (D) = U.12
U comparisons (3, CE) » U.UO
The time treatment (3) variable (Table 30) accounted for most of
the variance of factors I and II in the floor-knuckle lift (F-K) and
in factor V of the knuckle-shoulder regime (K-S). These variances
(square root « correlation) are determined from equations listed in
Kirk (1968), They can be approximated by taking the square root of the
sum of squares of the "B" treatment divided by the total sum of squares.
The "eta" correlations indicated that the movement patterns for these
three factors are curvilinear and closely associated with the time
82
variable. The motion patterns of each factor shown in Table 30 had the
following deviations when the time variable was examined by interaction
in Tables 31 to 33:
(1) factor IV, male sex, no differences over the four time
coD5)arisons (Table 32),
(2) factor IV, 10 and 25 pound weights, no differences over the
four time comparisons (Table 31),
(3) factor V, UO pound weight, no difference for time comparison
between intervals 3 and U (Table 31).
Peak acceleration and deceleration movements occurred during the
It is interesting to note that the y axis patterns in both lifts at the
arm/hands were the same, while maximum x axis motion occurred one time
interval later. Also, there appeared to be a coordinated effort between
the y axis movement of the trunk/upper arm (factor IV) and the lower
arin/hand (factor V), When the hands were accelerating (between 0 and
.50 second) in the knuckle-shoulder regime, the upper ant\/trunk demon
strated very little acceleration or was decelerating, A similar
observation previously had been discussed by Plagenhoef (1971) in his
description of a tennis racket swing. He stated that maximum deceler
ation of a body segment increased the velocity of the next segment.
Maximum deceleration of factor IV at time 2 (.26 - .50 second) coincided
very closely with the most stressful portion of lifting the weight, that
of passing the load through the horizontal plane.
83
Significant sex/time differences are noted in Table 32 for factor
II with males having higher accelerations (time 1: 0 - .25 second) and
decelerations (time 3: .51 - .75 second). Males also had lower decel
erations at the trunk/upper arms (factor IV) and higher accelerations
at the hands (factor V) during the .26 - .50 second time interval in
the y axis, knuckle-shoulder lift.
The time/weight interaction in Table 31 shows that there were
differences between the 10 and UO pound lifts (factor I, time U; factor
IV, time 2; factor V, times 1, 2, U) and the 25 and UO pound loads
(factor IV, time 2; factor V, times 1, U), Table 32 indicates that
most of the deviations in factor V were due to females lifting the UO
pound weight. The AD interaction in factor IV was not studied because
the e3q)erimental group (Table 2U) was not significant. However, the
validation and combined groups (Table 2U), UO pound weight (Table 26),
and female sex (Table 27) demonstrated differences; and therefore,
presented a strong case for studying the AD interaction in factor IV,
The results of these analyses are the same as factor V: most of the
variance were explained by females lifting the UO pound weight. The
results can be seen below:
Simple effect MS(p)
A at d^ ,62
A at d^ .29
A at d^ 17.26(.01)
D at a^ 12.8U(.01)
D at a^ .OU
A "% variance of total interaction" column was shown in Table 31,
32 and 33 to describe the amount of variance explained within an inter
action by the sum of squares of its coinponents. For exanple. Table 27
shows that B at a^ (female), 3 at a (male) and total sum of squares
are, respectively, U15.8, U55.9 and 871.7. In Table 32, factor V«s AB
interaction is depicted as having the following percentages of variance:
9
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hQ% (female) and $2% (male). This column was mainly presented in these
tables for descriptive purposes.
The tests of BCE interaction are contained in Table 33, The
following four con?)arisons were conducted, as shown in the table, in
order to evaluate training program effectiveness:
Ej^C^/E^C^ " pre/post untrained, should be insignificant
EQ^C^/E^C^ - pre of untrained/trained, should be insignificant
E C-ZE C, - post of untrained/trained, should be significant
E^C^/E^C^ - pre/post trained, should be significant
Time 2, factor II (,26 - .50 second) and time U, factor V (.76 - 1,00
second) fulfilled these criteria. Interval 3 (.51 - .75 second) in
both factors only partially met the requirements. However, when these
data were combined with the other two time frames, the results were
significant. These results indicated that training caused higher
decelerations in the y axis of both lifts. This finding would appear
to indicate that trained individuals demonstrated more efficient and
coordinated lifts because they accomplished the same task with less
effort.
Another area of interest was the investigation of the AD inter
action in the knuckle-shoulder lift. The statement that "females
lifting Uo pounds explained most of the variance in the y axis" left a
question unanswered. Is this statement true for trained females? A
series of Tukey mean comparisons were performed using .01 as the level
of significance for trainecJ/untrained female lifters over the three
weights. Using q = U.76 to compare the 10/25, 25/UO and 10/UO pound
lifts for factors IV and V, the following are the results of these tests:
10/25 25/UO lO/UO
Factor IV Trained
Untrained
Factor V
Trained
Untrained
.77
2.3U
.86
1.96
.75 U.78»
2.90
8.8l»
.03
5.89*
3.76
6.85*
89
These results indicate that most of the variance in the y axis for the
sex/weight interaction can be attributed to untrained females lifting
Uo pounds in the knuckle-shoulder lift. Differences were not noted
for untrained/trained males and trained females. This statement would
seem to en5)hasize the need for female training programs if women are
expected to lift loads approximating UO pounds,
t-Test Comparisons
Finkelman et al (1977) recommended that post-con5)arison analyses
of the independent variables on each of the dependent measures should
be limited to only those sources of variance found significant. The
next series of tests, therefore, will study the following topics which
were determined as being statistically significant from the ANOVA
investigations:
(1) male/female movements in y axis during time intervals 1 and
3 of the floor-knuckle lift (factor II).
(2) sex differences in y axis during time period 2 in the knuckle-
shoulder lift (factors IV and V).
(3) y axis decelerations of trained/untrained individuals during
time intervals 2 and 3 (factor II) and 3 and U (factor V) for the
floor-knuckle and knuckle-shoulder lifts, respectively.
The dependent variables studied will be limited to those items having a
factor loading greater than ,70. The t-test was used to compare the
male/female and untraineci/trained means on each of the segment acceler
ations. These analyses are contained in Tables 3U and 35. The level
of significance was foxmd by dividing ,01 ("alpha" during Tukey tests)
with the number of con5)arisons. The value ,001 was judged to be the
best approximate "alpha" after considering all of the tests that had to
be conducted. As mentioned previously, the probability has been varied
with the number of observations in order to minimize the occurrence of
a Type I error.
As an aid in interpretation, stick diagrams of the average move
ments of the trainecJ/untrained and male/female lifters in the floor-
knuckle and knuckle-shoulder regimes are depicted in figures U to 7.
90
The broken line in these drawings signifies either the female or
untrained person. When both lines overlap, the solid line represents
both conditions or sexes.
Trained individuals had higher decelerations in the floor-knuckle
lift (Table 3U) during time frames 2 and 3 (.26 - .75 second) due to
an initial position of bent knees and lower hip. As can be seen in
figure U, the knees and hip do the initial work, causing a domino-like
effect in the other segments. The result was a more efficient lift
with the initial thrust of legs/trunk causing the load to come closer
to the body more quickly.
The male lift in the floor-knuckle regime (Figure 5) resembled
the trained individual more than the female. Significant upward
accelerations for trunk/arms (time interval 1) and decelerations for
arms/hands (time interval 3) can be seen in Table 3U, These obser
vations can mainly be attributed to an initial position of lowered hip
and bent knees. Higher initial movements of these segments caused
higher decelerations later at the hands. Females initially relied
more on back motion with straight knees. Male and female differences
could possibly be explained by men being accustomed, even though
inexperienced, to handling weight and physically using their body more
than females.
During the knuckle-shoulder lift, the trained individual (Table
35) demonstrated more deceleration at the lower arms (.51 - ,75 second)
and lower arms/hands (,76 - 1,00 second). By visual inspection of
Figure 5, these decelerations appear to be directly related to smaller
trunk movement. Again, the trained person demonstrated a more efficient
lift by moving the elbows/arms backward in order to keep the load as
close to the body as possible. The untrained person relied more on the
back movement to lift the weight as well as to maintain balance with
the weight extended at the hands.
Males demonstrated higher upward accelerations at the lower arms/
hands and lower movements at the upper arms/legs than females during
time frame 2 of the knuckle-shoulder lift (Table 35). The time frame
of .26 - .50 second was the period of highest decelerations (downward
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movement) of the trunk/upper arms for both sexes with the females being
higher. This point indicated that both sexes were coordinating their
movements during the most stressful part of the lift (passing weight
through horizontal). Through segment deceleration, upward motion at
the hands was helped, (Plagenhoef, 1971), ^ ^ general, males appeared
to rely more on back and arm muscles rfiile females used more leg and
downward back motion to compensate for strength differences. These
observations, which can be seen in Figure 7, demonstrated that females
and the untrained condition as well as males and trained people were
comparable^
The remaining part of this section will discuss the significant
results pertaining to electromyograms (EMG), platform forces and
inertial forces (at the hands). Since many authors have primarily
studied EMG and platform information, it was felt that this data too
should not be overlooked. Although these variables did not contribute
heavily to the factor-variable structure, they did have significant
loadings. From Tables 19 and 20, the variables with loadings of .20
and above are presented below:
II III IV V
.20
-.22 .21 - .2U
.22 .28
.22 - .53
From this information, quadriceps and deltoid muscles loaded, respec
tively, on the X axis of the floor-knuckle and knuckle-shoulder lifts.
This was as expected from the literature (Shinno, 1968; Hobart and
Vorro, 197U) since these lifts coincided closely with each muscle's
specific function. Transverse force explained most of the variance of
the platform variables within the factor structure. This too was
expected because of its importance in previous experiments (Ismail, 1968j
Perkins et al, 197U), The significant loadings of frontal force, al
though lower than transverse, had also been previously identified. How
ever, coronal force demonstrated a pattern which was observed in the
Quadriceps Vial i-nAfi LieJ. bOlU
Sagi t ta l
Coronal
Transverse
I .20
- . 3 U
.29
.78
98
correlational matrices of Tables 9 and 10, and from the factor loadings.
This was not reported by Perkins and Konz (197U), ^o found no apparent
pattern.
Stepwise regression was also performed using EMG and platform
variables as predictors and inertial forces at the hands as the
criterion variables (Tables 17 - 20), The results were highly signif
icant. This demonstrated some concurrent validity between the
different sources of data collection and analysis.
Table 36 depicts the average force and strain data over time for
both lifts. Table 37 contains t-test comparisons using averaige peaks
for the sex, condition and weight treatment levels. Some investi
gators (Perkins and Konz, 197U) have used peak forces from the platform
in their studies of load handling because they considered these values
to be related to stress and safety. Positive force values in Table 36
represented backward, right and downward vectors, while the reverse was
true for negative information. Deltoid and quadriceps SMG*s were only
studied, respectively, in the knuckle-shoulder and floor-knuckle lifts
because of a lack of common variance in the other two muscle-lift
relationships. The level of significance selected for these t-test
coriparisons in Table 37 was .01. This value was determined from
dividing .1, the initial treatment probability, by the number of
observations.
From Table 36, peak values in the floor-knuckle regime occurred
generally in the first .5 second of lift (the acceleration phase). The
deltoid, sagittal plane and inertial force (x axis) followed the same
pattern with peak strain/stress being observed in the first .5 second
of the knuckle-shoulder lift. However, peak forces in the transverse
plane and at the hands (y axis) occurred during deceleration (time
interval U), Maximum coronal force happened during the ,75 - 1.00
interval (time U) in both lifts, and may indicate a slight loss of
lateral balance toward the end of motion. Also, initial height of lift
significantly effected the amount of force shown in both axes with
floor-knuckle values being higher than knuckle-shoulder data.
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101
Trained/untrained males and trained females in Table 37 demon
strated higher forces in the sagittal and transverse planes in the
floor-knuckle (F-K) regime. All females and untrained males had
higher values in the sagittal and coronal planes in the knuckle-
shoulder (K-S) lift. These findings appear to support the results
previously stated in this investigation that:
(1) trained females and all males produced more movement during
the floor to knuckle lift,
(2) all females and untrained males relied more on leg and back
movement in the knuckle-shoulder lift to supplement either strength or
balance differences.
The effect of object weight (Table 37) in the floor-knuckle regime
was small and only significant between the 10 and UO pound lifts. On
the other hand, weight had a greater influence during knuckle-shoulder
observations with most weight conparisons being significant.
CHAPTER V
CONCLUSIONS AND RECOMMENDATIONS
FOR FUTURE RESEARCH
(Chis investigation atteirpted to expand upon the dynamic biomechan
ical model developed by El-Bassoussi (197U) for non-repetitive, short
duration lifts in the sagittal plane^ This model expansion entailed
not only using acceleration patterns and inertial forces which were
mathematically computed, but also the more precise electromyogram (EMG)
and force platform data^ The result was a biomechanical model based on
clusters of motion in two ranges of lift. These factor-variables were
then utilized to compare lifting by male/female and trained/untrained
individuals over time, weight and regime. In addition, prediction
equations were generated in order to determine inertial forces at the
hands from both the mathematically generated data from film and the
force platfonn/EMG information from the recorders.
Conclusions
The significant conclusions of this report are as follows:
1. A biomechanical model utilizing factor analysis was developed
for non-repetitive, short duration tasks in the sagittal plane. The
five-factor model for lifting in the floor-knuckle (F-K) and knuckle-
shoulder (K-S) regimes was shown to have validity by demonstrating that
there were similarities between both the correlational matrices and the
factor structures of two uncorrelated samples,
2, Slote and Stone equations were used in the development of the
present model by determining angular velocities and accelerations for
each body segment. The application of these relationships in the
present model depended upon demonstrating their validity. Validation
procedures were performed in the following three ways:
(a) Goodness-of-fit tests indicated that observed and predicted
(Slote and Stone) angular displacement distributions were similar for
all but one joint's motion. This deviation, ankle in the floor-knuckle
lift, was not considered very serious to model validity because it only
102
103
accounted for a total displacement of thirteen degrees.
(b) Goodness-of-fit tests were used to show that the resultant
forces in the x and y planes from both the force platform (sagittal/
transverse planes) and film negatives (inertial force at the hands)
were similarly distributed in both lift regimes,
(c) Regression equations demonstrated that there were signifi
cant relationships between inertial forces at the hands (film) and
forces at the feet (force platform). These equations were cross-
validated through the use of weights from one sanple to calculate the
results of the second saii?)le. The major contributor in the four
equations (x and y planes in both F-K and K-S lifts) was the force in
the transverse plane.
3, The major movement predictors of x and y inertial forces at
the hands were accelerations at the arms (F-K) and lower arms (K-S),
These results were also cross-validated using the two group comparison
methodology,
U. Movement patterns were curvilinear in both lifts with peak
accelerations and decelerations occurring within (a) the 0 - .25 and
.51 - .75 second intervals in the y axis, and (b) the .26 - .50 and
either the .51 - .76 (K-S) or .76 - 1.00 (F-K) time frames in the x
axis. Although maximum deceleration in the x axis of the knuckle-
shoulder regime was observed during time frame 3, it was not signifi
cantly different from time interval U, The highest electromyogram
strain values in both lifts coincided with peak acceleration periods
within the first ,5 second of the lift. In addition, some of the peak
forces or stresses occurred during the first one-half second of the
floor-knuckle lift and y axes, inertial forces; and transverse plane)
and knuckle-shoulder regime (sagittal plane; and x axis, inertial
force). These findings are generally in agreement with Grieve (197U)
and Perkins and Konz (197U),
5, Most of the variance, in the x and y axes of the floor-knuckle
range and in the y axis at the lower arms/hands for the knuckle-
shoulder lift, can be explained by the time treatment. These findings
loU
are due mainly to motion in factors I, II and V approximating the
Slote and Stone (1963) curvilinear relationships,
6, Coordinated movement in the knuckle-shoulder lift was shown
when maximum deceleration of the trunk/upper arms (y axis, ,26 - ,50
second) coincided with acceleration at the lower armsAands (y axis,
0 - .50 second). This point indicates that both sexes are coordinating
movement during the most stressful part of the lift (passing weight
through the horizontal). By decelerating one segment with downward
movement, upward movement at the hands is helped (Plagenhoef, 1971),
7, Males had higher accelerations (0 - .25 second) and decel
erations (.51 - .75 second) in the y axis for the floor-knuckle lift.
Significant upward accelerations for trunk/arms and decelerations for
arms/hands segments of the male subject could be attributed to an
initial position of a lower hip and more deeply bent knees than the
female. Lower trunk accelerations were also supported by Kumer (197U)
when he observed that female back extension occurred later in the lift
than males. Lumbar vertebrae remained fixed until a specific safe
level was reached, and then extension of the spine was allowed to begin.
8, In the knuckle-shoulder lift, males demonstrated higher upward
accelerations at the lower armsAands and lower movement at the upper
arms/legs than females during the .26 - .50 second time interval. (jMs
would seem to indicate that the men relied more on back and arm muscles,
while the women used more leg and back motion to supplement strength
differences^) Strength differences between the sexes are well supported
in the literature (Ayoub, 1978; Snook, 1978),
9, Trained individuals demonstrated more efficient and coordinated
lifts in the y axis of both lifts by having similar patterns of acceler
ation with, but significantly higher deceleration patterns from, the
untrained condition. These deviations in deceleration were observed
during the .26 - .75 second of the floor-knuckle lift and the .51 - 1.00
second of the knuckle-shoulder lift, ^ i s would appear to indicate that
trained people accorqjlished the same task with less efforU) (jhe obvious
differences between the groups are that the trained sairple had lower
hips and more bent knees in the floor-knuckle lif^ This initial thrust
105
combined with "domino-like" and coordinated movements during the lift
resulted in the weight coming closer to the body more quickl^^ iDuring
the knuckle-shoulder lift, the trained person demonstrated a more
efficient lift by moving the elbows and arms backward in order to keep
the load as close to the body as possible^) Untrained inciividuals
relied more on back movement to lift the load as well as to maintain
balance with the weight extended at the hands. The literature supports
this study's conclusions that (gaining results in more efficiency,
coordination and rhytlm) (Komarek, 1968; Waterland, 1968; Vorro and
Hobart, 197U),
10, Male movements approximated the trained condition. This
finding could possibly be explained by men being more accustomed to
physical exercise and the handling of weight. The male desire for
competition and skilled performance somewhat supports this contention
and has previously been outlined in the research literature (Deaux et al,
1975; House, 197U),
11, The weight variable had greater influence during the knuckle-
shoulder lift with most of the weight comparisons between forces being
significant. On the other hand, the effect of object weight in the
floor-knuckle regime was small and mainly only significant between 10
and Uo pounds,
12, Most of the variance in the y axis for the sex/weight inter
action (factors IV and V) can be attributed to untrained females
lifting Uo pounds in the knuckle-shoulder lift. Acceleration pattern
differences were not noted between weight conditions and all males or
trained females, ^lis statement would indicate that training programs
are necessary in the industrial environment if women are expected to
lift loads of approximately UO pounds) (Women presently are having
significantly more injuries with lighter loads (1 - 35 lbs.) and demon
strating poorer handling techniques than men (Shannon, 19782j In
addition, the recommended acceptable weight of lift for women in these
two lift regimes is roughly UO pounds for the twenty-fifth percentile
(25%) of the female population (Ayoub, 1978). This limit can be
improved, as demonstrated by the results in this study, through training
106
13. The application of a multivariate approach to analysis of
variance not only isolated specific areas for future analyses but
prevented raising the alpha error, and losing power and data information
(Finkelman, 1977). Analyses of this pooled information, using t-tests
to explore the significant interactions, allowed the investigator to go
deeply into the qualitative relationships behind the significant quan
titative numbers. The use of various sources of data besides movement
on film resulted in the investigator having other avenues for data
comparison. In all, the statistical methodology should have resulted
in a valid investigation.
Recommendations for Future Research
The methodology outlined in this paper was used to analyze non-
repetitive, short duration lifts. The same procedural steps could again
be performed in another experiment which would collect pre- and post-
measures of movement and stress in males/females and untrained/trained
individuals during repetitive lifts. Repetitive models have been
developed at Texas Tech (McDaniel, 1972; Dryden, 1973; Knipfer, 1973;
Ayoub, 1978) relating sex, strength and anthropometric characteristics
to amount of weight lifted within specific lift regimes. The same
psychophysical technique, which was applied in these research investi
gations, could again be used to study movement as measured by film and
force platform analyses. Strain measurements can be attained by
estimating metabolic energy expenditure rates. In general, the recom
mended experimental design would consist of:
(1) sex - male and female
(2) time - intervals during lift (possibly 5 periods)
(3) program - trained and untrained
(U) measure - pre- and post-training program
(5) phase - beginning and ending of session to determine differences
in fatigue due to work.
Size, strength and weight lifted would have to be controlled in this
study. The training program should strive to optimize bodily movements
rather than to develop muscular strength. Factor analysis, regression
107
analysis and analysis of variance are the recommended statistical tech
niques. Dependent variables would consist of the three force patterns
from the platform, segment accelerations and forces from photography,
and oxygen consumption measurements. Independent variables would test
differences in short duration over time within a lift (Time), long
duration over time within a session (Phase), training (Measure/Program),
and male and female (Sex).
(Aijother possible investigation would be the study of the influence
of body size upon lift techniquej Stratification based on either
height, weight or somato types can be performed. Their effects can
then be studied using a similar methodology as the one outlined in this
report.
Other possible avenues of future research can follow along the
lines of the various arguments presented against women assuming male-
oriented jobs. Some of these viewpoints may have validity, while
others, of course, may be quite prejudiced. Strength, endurance, coordi
nation, and menstrual cycle are valid issues, and therefore require
further investigation. The effects of these topics may be fiirther
influenced by the attitudes of women, which could further broaden the
gap between the sexes. In other words, relevant research of the sex
variable may require a systems or multivariate approach using various
physiological, environmental, motor, intellectual, sensory and psycho
logical variables.
In closing, the following recommendations were presented by
Hudgens and Billingsley (1978) in their review of the Human Factors
literature concerning the sex variables:
1. Increase the research performed on the sex variable.
2. Avoid the practice of small ratio of females to males because
it contributes to measurement error and often precludes analysis of the
sex variable.
3. Valid research and analysis of the sex variable, even when no
differences are found, should be reported,
U, Studies involving female subjects should, ideally, include
information as well as possible control for menstrual cycle and oral
contraception.
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APPENDIX
A. Acceleration Patterns of the Bodily Segments
B, Analysis of Force and Electromyogram Data
115
116
APPENDIX A: ACCELERAHON PATTERNS OF THE BODILY SEGMENTS
Angular displacements during both lifts were found by measuring the
angles of each joint from photographic negatives collected during the
experiiOBnU Tables A-1 and A-2 contain the means of these angles over
time by lift, sex and program. With this displacement information,
con5)utations of velocity, acceleration and force profiles were accom
plished. Table A-3 depicts the acceleration means by segment, time and
lift in the x and y axes. Figures A-1 through A-U show the discrete
data in Table A-3 in terms of continuous curves of segment motion.
These Tables and Figures are listed on the following pages as:
Joint angular displacements in degrees for the floor-
knuckle (combined group) lifts Table A-1
Joint angular displacements in degrees for the knuckle-