determination of the swing technique characteristics and performance outcome relationship in golf...
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Determination of the swing technique characteristicsand performance outcome relationship in golf drivingfor low handicap female golfersSusan J. Brown a , Alan M. Nevill b , Stuart A. Monk c , Steve R. Otto c , W. Scott Selbie d &Eric S. Wallace ea School of Life, Sport and Social Sciences , Edinburgh Napier University , Edinburgh, UKb Research Institute of Healthcare Sciences , University of Wolverhampton , Walsall, UKc Research & Testing , R&A Rules Ltd , St. Andrews, UKd C-Motion Inc , Germantown, Maryland, USAe Sport and Exercise Sciences Research Institute , University of Ulster , Newtownabbey, UKPublished online: 11 Oct 2011.
To cite this article: Susan J. Brown , Alan M. Nevill , Stuart A. Monk , Steve R. Otto , W. Scott Selbie & Eric S. Wallace (2011)Determination of the swing technique characteristics and performance outcome relationship in golf driving for low handicapfemale golfers, Journal of Sports Sciences, 29:14, 1483-1491, DOI: 10.1080/02640414.2011.605161
To link to this article: http://dx.doi.org/10.1080/02640414.2011.605161
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Determination of the swing technique characteristics and performanceoutcome relationship in golf driving for low handicap female golfers
SUSAN J. BROWN1, ALAN M. NEVILL2, STUART A. MONK3, STEVE R. OTTO3,
W. SCOTT SELBIE4, & ERIC S. WALLACE5
1School of Life, Sport and Social Sciences, Edinburgh Napier University, Edinburgh, UK, 2Research Institute of Healthcare
Sciences, University of Wolverhampton, Walsall, UK, 3Research & Testing, R&A Rules Ltd., St. Andrews, UK,4C-Motion Inc., Germantown, Maryland, USA and 5Sport and Exercise Sciences Research Institute, University of Ulster,
Newtownabbey, UK
(Accepted 11 July 2011)
AbstractPrevious studies on the kinematics of the golf swing have mainly focused on group analysis of male golfers of a wide abilityrange. In the present study, we investigated gross body kinematics using a novel method of analysis for golf research for agroup of low handicap female golfers to provide an understanding of their swing mechanics in relation to performance. Datawere collected for the drive swings of 16 golfers using a 12-camera three-dimensional motion capture system and astereoscopic launch monitor. Analysis of covariance identified three covariates (increased pelvis–thorax differential at the topof the backswing, increased pelvis translation during the backswing, and a decrease in absolute backswing time) asdeterminants of the variance in clubhead speed (adjusted r2¼ 0.965, P5 0.05). A significant correlation was found betweenleft-hand grip strength and clubhead speed (r¼ 0.54, P5 0.05) and between handicap and clubhead speed (r¼70.612,P5 0.05). Flexibility measures showed some correlation with clubhead speed; both sitting flexibility tests gave positivecorrelations (clockwise: r¼ 0.522, P5 0.05; counterclockwise: r¼ 0.711, P5 0.01). The results suggest that there is nocommon driver swing technique for optimal performance in low handicap female golfers, and therefore consideration shouldbe given to individual swing characteristics in future studies.
Keywords: Golf, female players, pelvis, thorax, clubhead speed
Introduction
The importance of golf driving performance is widely
recognised. Many studies have investigated the key
elements of driving performance (Chu, Sell, &
Lephart, 2010), including the application of mathe-
matical models and in vivo measurements. Whilst the
majority of previous work has focused on male
golfers, more recent research has included female
golfers (see, for example, Chu et al., 2010; Egret,
Nicolle, Dujardin, Weber, & Chollet, 2006; Horan,
Evans, Morris, & Kavanagh, 2010; Zheng, Barren-
tine, Fleisig, & Andrews, 2008). All of these studies,
however, chose statistical analysis methods that
group data using the homogeneity principle of
participant selection and so there is an underlying
assumption that the group mean for each variable is a
representation of the homogeneous group. There-
fore, attention should be paid to the swing
kinematics of highly-skilled female golfers which
allows for individual technique variation in order to
establish the existence of common elements of the
swing associated with optimal performance, and
therefore to inform specific coaching.
Egret et al. (2006) studied swing kinematics of
male and female golfers and found significant
differences between groups for shoulder and hip
angles and knee flexion at the top of the backswing.
Their findings suggest that greater magnitude of
rotation is seen in female golfers, but they found no
significant differences in clubhead speed between
males and females, possibly as a consequence of the
range of abilities and subsequent use of group mean
data to conduct the analysis. Zheng et al. (2008)
studied group data from male and female profes-
sional golfers and also found significant differences
in shoulder and pelvis orientation at the top of the
backswing, as well as differences in pelvis orientation
Correspondence: S. J. Brown, School of Life, Sport and Social Sciences, Edinburgh Napier University, Edinburgh EH11 4BN, UK.
E-mail: [email protected]
Journal of Sports Sciences, November 2011; 29(14): 1483–1491
ISSN 0264-0414 print/ISSN 1466-447X online � 2011 Taylor & Francis
http://dx.doi.org/10.1080/02640414.2011.605161
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at ball impact. They concluded that the LPGA
(Ladies Professional Golf Association) players pro-
duced greater changes in pelvic and shoulder
orientations from the top of the backswing to ball
impact, but had less of an uncoiling effect at ball
impact than their male counterparts.
Horan et al. (2010) conducted the only study to
date using the Cardan thorax alignment rotation
method during the golf swing of males and females,
but found no significant differences between the
sexes in their calculation of pelvis–thorax separation.
There was, however, a difference between the sexes
in the overall position of the upper body at the top of
the backswing due to an increase in thorax and pelvis
sway in males, but no difference for axial rotation of
either segment. Furthermore, the magnitudes of
thorax and pelvis axial rotation were significantly
different at ball contact, with females generating
higher values. Peak clubhead speeds were also
significantly different between the sexes. The analysis
method used here was also based around group data
for the male and female golfers. Although it would
appear that no difference exists in the way that male
and female golfers separate their pelvis and thorax,
this may be the result of taking mean data from each
sex, which masks the individual variation in both
sexes.
Furthermore, even in published golf studies of only
male participants, there appears to be some dispute
regarding the impact of this hip/pelvis–thorax inter-
segment interaction and its effect on clubhead speed,
but the use of pelvis and thorax segments to identify
differences between golfers of varying ability as well as
differences between the sexes remains popular
(Cheetham, Martin, Mottram, & St. Laurent, 2001;
Cole & Grimshaw, 2009; Egret et al., 2006; Horan
et al., 2010; Myers et al., 2008; Zheng et al., 2008).
Methodological issues may have contributed to this
ambiguity between studies (Wheat, Vernon, &
Milner, 2007) and the group profiling of golfers for
analysis by means of either ability or gender is also
common, but variations exist in how this profiling is
achieved. However, the pelvis–thorax separation
previously reported in male golfers as playing an
important role in accelerating the clubhead towards
the ball may apply to some although not necessarily
all golfers. A greater change in length of muscle and
tendon tissues (elastic deformation) would result in
greater strain energy being available, but the premise
that all golfers could utilise this principle is based on
the assumption that they are all equally capable of
either achieving an appropriate level of deformation,
or that their tissues possess the same elastic proper-
ties. Crucially, however, there is evidence of in-
creased musculotendinous stiffness in males
compared with females (Blackburn, Padua, Wein-
hold, & Guskiewicz, 2006; Blackburn, Riemann,
Padua, & Guskiewicz, 2004; Gajdosik, Giuliani, &
Bohannon, 1990), resulting in an increased avail-
ability of strain energy in males compared with
females. Anatomical differences in structure between
the sexes and indeed between players of either
sex may therefore account for different swing
characteristics, particularly in terms of elastic energy
utilisation.
While no golf-specific studies have considered the
selection of movement recruitment strategies be-
tween the sexes, individual athletes may find unique
solutions to a given motor task, suggesting there may
not be a common optimal technique for everyone
(Bartlett, Wheat, & Robins, 2007). The theoretical
control mechanisms behind any differences in
technique within the golf swing are beyond the scope
of this paper, but it is important in the evolution of
the field to establish whether there is a common
technique for optimal performance of female golfers.
The main aims of the present study were: (1) to
establish the key parameters associated with the drive
golf swings of a group of low handicap female golfers
with a particular focus on the axial rotation move-
ment patterns of the pelvis and thorax, as well as
temporal characteristics of the swing; and (2) to
determine if there is an common optimal swing
based on these parameters for this group of highly
skilled female golfers using a method of analysis
(ANCOVA) that accounts for individual differences
in technique. It was hoped that the study would
determine whether the current coaching methods for
female golfers that are based on key features of the
male swing require modification.
Methods
Participants
Sixteen right-hand dominant Category One
(handicap� 5) female golfers (Table I) gave
informed consent to participate in the study as
approved by the university ethics review committee
and in accordance with the university policy for
human experimentation.
Procedures
The height, mass, grip strength, upper body flex-
ibility, and self-reported handicap of each participant
were determined prior to motion capture. Grip
strength dynamometry was selected because it
was deemed the single strength measure most likely
to be associated with the golf swing. Handgrip was
determined by selecting the maximum value from
three attempts with each hand using a Takei
Analogue Handgrip dynamometer (TKK-5001,
Cranlea, Birmingham, UK). Upper body flexibility
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was measured using an Acuflex1 II Trunk Rotation
Test (Novel Products, Inc., USA). Participants were
asked to perform three rotations in each direction
with the highest value selected for analysis using two
different methods in random order:
. Method 1 – according to the manufacturer’s
guidelines, with feet shoulder width apart and
knees slightly bent, participants were asked to
stand at 908 and centrally to the device, arms
length away, and then to rotate backwards
keeping the arm horizontal, reaching with their
outside fist for the sliding scale, with the final
position required to be held for 2 s. This was
repeated for the opposite arm.
. Method 2 – modified from the manufacturer’s
guidelines, the participants were asked to sit on
their heels with their back to the device, again
arms’ length away and to rotate clockwise and
counter-clockwise keeping their pelvis facing
forwards to isolate the rotation of the thorax. As
in Method 1, participants were required to keep
the extending arm horizontal and hold the final
position 2 s.
During both tasks, participants were asked to
maintain an upright body position. Both methods
were used to establish the rotation capability of each
participant in a standing position similar to that used
in the golf swing, and then the adapted method used
to determine the ability of each participant to
separate their pelvis and thorax, given that the pelvis
remained ‘fixed’ during Method 2. This would help
to determine whether the use of such a separation is
related to the maximum voluntary range of trunk
motion or technique selection. Each golfer then
performed 10 drives into a golf net situated 2.5 m
from the tee and ball position while standing on a
golf mat (Figure 1). Participants used their own
driver and wore appropriate golf shoes and minimal
fitted clothing to avoid extraneous marker move-
ment. Kinematic data were collected using 12 infra-
red cameras (ProReflexTM, Qualisys Medical Ltd.,
Sweden) operating at 240 Hz. The equipment was
calibrated according to the manufacturers’ instruc-
tions, with the camera system showing a maximum
calibration residual of 1.5 mm for each camera.
Qualisys Track ManagerTM (QTM, Version
1.8.224, Qualisys Medical Ltd., Sweden) was used
to reconstruct the three-dimensional coordinates of
each of ten 19-mm spherical reflective markers
placed on the following sites: left and right shoulder
acromion processes, left and right anterio-superior
iliac spine (ASIS), left and right posterior-superior
iliac spine (PSIS), thorax tracking markers placed on
C7, T10, L4, and suprasternal notch. Reflective tape
was also placed 0.6 m downwards from the butt of
the shaft of the club and on the toe of the clubhead.
Markers were also placed on the following sites to
allow events within the golf swing to be identified:
left and right lateral shoulders, two upper arm
tracking markers on each arm, left and right, medial
and lateral epicondyles of each elbow, left and right
medial wrist markers placed on the superior aspect of
the styloid process, left and right lateral wrist markers
Table I. Participant information and variable data.
Variable mean+ s
Correlation with
clubhead speed
Age (years) 24.8+ 7.3 N.A.
Height (m) 1.68+ 0.06 N.A.
Mass (kg) 65.94+ 6.23 N.A.
Club shaft length (m) 1.11+ 0.03 N.A.
Handicap (strokes) 1.75+ 2.35 r¼70.612,
P50.05
Grip strength, left hand
(kg � f71)
32.94+ 5.26 r¼ 0.54,
P50.05
Grip strength, right
hand (kg � f71)
35.25+ 5.93 Not significant,
P40.05
Standing flexibility,
clockwise (m)
0.39+ 0.2 Not significant,
P40.05
Standing flexibility,
counter-clockwise
(m)
0.42+ 0.2 Not significant,
P40.05
Sitting flexibility,
clockwise (m)
0.62+ 0.15 r¼ 0.522,
P50.05
Sitting flexibility,
counter-clockwise
(m)
0.58+ 0.13 r¼ 0.711,
P50.01
Clubhead speed
(m � s71)
39.48+ 2.48 N.A.
Ball speed (m � s71) 55.7+ 3.93 N.A.
Backswing time (s) 1.00+ 0.17* N.A.
Downswing time (s) 0.32+ 0.05 N.A.
*P50.05 within the ANCOVA model.
Figure 1. Plan of capture area with reference to the global
coordinate system (XG, YG, ZG).
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placed on a 7.5 cm wand extending out laterally
from the ulnar styloid process, and one lower arm
tracking marker placed on the forearm of each arm.
Thigh and shank markers were also used to stabilise
the optimisation used to calculate model pose and
were located at the following sites: left and right,
medial and lateral condyles of each knee, two upper
leg tracking markers placed non-linearly on the thigh
of each leg, left and right, medial and lateral malleoli,
two lower leg tracking markers placed non-linearly
on the shank of each leg, left and right calcaneus.
A proprietary stereoscopic launch monitor, posi-
tioned to capture images of the clubhead, was
used to measure clubhead speed at impact. The
launch monitor was also used to measure ball speed,
launch angle, and backspin rate within 0.03 s post-
impact. The accuracy in each parameter (clubhead
speed+0.5 m � s71; ball speed+0.05 m � s71;
launch angle+0.18; spin rate+50 rpm) was deter-
mined via comparison with other proprietary equip-
ment (N. F. Betzler, S. A. Monk, E. S. Wallace, & S.
R. Otto, unpublished).
The participants were asked to warm up and
familiarise themselves with the experimental set-up
before motion capture by hitting balls, with their own
drivers, into the net along a target line taped to
the floor parallel to the laboratory ‘‘XG’’ axis. All
participants used a premium three-piece construc-
tion ball commonly used by male/female professional
and low handicap golfers in competitive play. The
participants placed the ball on a wooden tee set at
their preferred height. Once a participant stated that
she was comfortable within the testing environment,
data capture began with a static calibration file of the
participant standing in the anatomical position for
use in generating the subject model using Vi-
sual3DTM software (C-Motion Inc., USA). This
allowed a transformation of the position vectors
between the segment and laboratory coordinate
systems (Cappozzo, Della Croce, Leardini, & Chiari,
2005).
Data processing
The 10 drives plus the static calibration file for each
participant were processed by identifying the location
of each marker using QTMTM software after setting
the tracking maximum residual error to 3 mm. Data
from all files were then exported into Visual3DTM for
further processing and analysis. A model was
generated for each participant using medial and
lateral markers at the proximal and distal ends of
each segment to establish a local right-handed
orthogonal coordinate system originating at the
proximal end of the segment, and oriented with the
z-axis aligned with the proximal and distal axis, and
the y-axis directed anteriorly. The thorax segment
was derived from the location of the ASIS markers
and left and right acromion markers in the anatomi-
cal position, and the pelvis derived from ASIS and
PSIS markers. The position and orientation (pose) of
the thorax segment during the hitting trials was
estimated using tracking markers placed on C7, T10,
and L4. To compensate for soft tissue artefact-
related movement, the pose was estimated using a
global optimisation algorithm (Lu & O’Connor,
1999), which considered measurement error distri-
butions and was solved using a Quasi-Newton
optimisation algorithm. The following constraints
were imposed at the joints:
. pelvis segment – 6 degrees of freedom (relative
to laboratory)
. thorax and thigh segments – 3 degrees of
freedom (no translation relative to pelvis)
. shank segments – 3 degrees of freedom (no
translation relative to thighs).
Kinematic data were analysed for thorax and pelvis
rotations during the drive by considering four phases
of movement based on the following events [adapted
from Neal, Abernethy, Moran, & Parker (1990) and
Robinson (1994)]:
. Event 1: address (AD) – associated with the
frame before motion of the club began, estab-
lished from clubhead markers
. Event 2: top of the backswing (TB) – associated
with the frame before the club began moving
back towards the target, established from club-
head markers
. Event 3: left wrist un-cocking (WU) – time at
which the resultant angle from the lateral elbow
and wrist markers relative to the club shaft
began to increase
. Event 4: left-arm horizontal (LAH) – associated
with the frame at which the left forearm segment
was horizontal (relative to the ground)
. Event 5: impact (IM) – determined by the
position of the clubhead marker relative to the
ball.
The specific events were located at the frame
coinciding with these descriptions, and respective
swing phases were between these frames.
A virtual laboratory (XG, YG, ZG) was created in
Visual3DTM aligned with the tee and a target line
along a line parallel to the XG axis, the global
coordinate system (GCS) determined by the YG axis
representing the anterior-posterior direction, the XG
axis the medial-lateral direction, and the ZG axis the
vertical direction. The segment coordinate system
(SCS) was determined for each segment so as to
simulate the different axes of rotation for each
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segment, the origin of which was placed at the
proximal end of each segment using the same
reference direction as the GCS (e.g. ZT-vertical
and YT-anterior) computing the longitudinal axis
first (see Figure 2 for orientation of the SCS). Pelvis
angular position and then displacements were
derived from pelvis orientation relative to the global
coordinate system of the virtual laboratory using
Cardan sequence XYZ, the ZP value providing
segment axial rotation at and between events (Lees,
Barton, & Robinson, 2010). A zero ZP value signifies
that the segment and the target line were parallel,
with a negative value (commonly referred to as a
closed position) indicating a clockwise rotation of the
segment relative to the target line and a positive value
(open) a counter-clockwise rotation relative to this
line. Pelvis translation along the target line was also
calculated based on the pelvis origin position at and
between events. The pelvis–thorax differential was
calculated as the joint angle created by the thorax
relative to the pelvis (about the thorax ZT axis) and
extracting the Z values using Euler angles and
Cardan sequence XYZ, and finally the angular
velocity of this variable was calculated as the thorax
relative to the pelvis resolved into the thorax SCS.
Data analysis
The golf swing data were analysed using the best
three of the 10 trials (Bates, Dufek, & Davis, 1992).
Since the analysis was intended to focus on
participant maximum potential, the best three shots
rather than all 10 were selected. These three shots
were determined by consideration of the launch
characteristics, specifically ranking each shot by
clubhead speed, efficiency (ratio of ball speed to
clubhead speed), launch angle, and backspin rates.
The interdependency of these characteristics is
crucial to achieving greater driving distance; in
particular, optimum launch angle is heavily depen-
dent on backspin rates and ball speed. The highest
clubhead speed, efficiency, and launch angle were
given the highest rankings (Cochran & Stobbs, 1968)
and the backspin values closest to 2500 rpm were
ranked highest. A figure of 2500 rpm was selected as
it is close to the spin magnitude used by golf’s
governing bodies for conformance testing of golf
balls (The R&A, 2011). The sum of the rankings was
calculated and the three best trials selected. Mean
data were derived and are presented from the three
selected shots based on the events and phases
described above, but all three selected shots and
the associated kinematic variables were used in the
statistical analysis.
Analysis of covariance (ANCOVA) using backward
elimination was used (PASW Statistics v.18.0, SPSS
Inc., Chicago, IL) to investigate which variables or
covariates were likely to explain the differences in
clubhead speeds for all 48 trials (16 participants6 3
selected shots), with clubhead speed as the dependent
variable and the kinematic and temporal variables as
covariates. ANCOVA was selected because it has the
capacity to fit a fixed between-participant indicator
variable (n¼ 16) and enables the estimation of a
within-participant source of variation (3 trials) as part
of the error structure. This means that the ANCOVA
partitions two sources of variation: one between
participants and one within participants. Participant
number was therefore used as a fixed factor so that the
analysis allowed for individual differences in club-
head speeds. Clubhead speed data were assessed for
normality by plotting the calculated residuals against
the predicted values, and tests of normality were
carried out to ensure data were normally distributed.
Figure 2. Segment coordinate systems: thorax (XT, YT, ZT) and
pelvis (XP, YP, ZP). The SCS origin was placed at the proximal
end of each segment for analysis but located at the centre of mass
for clarity in the figure above.
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Pelvis displacement, translation, and pelvis–thorax
differential data were placed along with temporal data
into the analysis. Pearson product–moment correla-
tions were carried out separately for clubhead speed
relative to flexibility and grip strength since these
measures were not directly associated with any given
golf shot, unlike all other data. In all cases, statistical
significance was set at P5 0.05.
Results
Participant data are presented in Table I and include
both anthropometric and performance measures.
Clubhead speed was chosen as the performance
measure for analysis since all participants used their
own club, inferring a possible ball/club influence that
could affect analysis using ball speed data. A
significant correlation was found (r¼ 0.54,
P5 0.05) between left-hand grip strength and club-
head speed, but not between right-hand grip strength
and clubhead speed. A significant negative correla-
tion was found between handicap and clubhead
speed (r¼70.612, P5 0.05).
Flexibility measures provided in Table 1 showed
some significant correlation with clubhead speed;
both sitting flexibility tests gave significant positive
correlations (clockwise: r¼ 0.522, P5 0.05; coun-
ter-clockwise: r¼ 0.711, P5 0.01) but neither of the
standing tests was significant.
With reference to the data presented in Table II
and Figures 3 and 4, the ANCOVA identified three
covariates (increased pelvis–thorax differential at
the top of the backswing, increased pelvis translation
during the backswing, and one temporal value –
a decrease in absolute backswing time) as determi-
nants of the variance in clubhead speed (dependent
variable) between the participants (adjusted r2¼0.965, P5 0.05). Participants was used as a fixed
factor within the ANCOVA using three shots per
participant, but when this was removed and the
ANCOVA re-run, the model was less useful in
explaining the variance in performance (adjusted
r2¼ 0.734, P5 0.05), indicating a strong reliability
on participants’ own swing technique to produce
faster clubhead speeds.
Data for pelvis–thorax axial (Z) angular velocity at
wrist un-cocking was only slightly above the alpha
threshold (P¼ 0.062) in the final elimination.
Further analysis of these data using a scatter plot
and Pearson product–moment correlation confirmed
that there was a positive correlation between this
variable and clubhead speed (r¼ 0.489, P¼ 0.00);
participant 11 appeared as an outlier. This golfer
began wrist un-cocking very early and proceeded to
un-cock throughout the downswing, so the timing of
this event and therefore the negative values present in
the angular velocity data may have influenced the
results within the ANCOVA.
Figure 3 shows data presented in ascending
clubhead speed order for the timing of specific
events expressed as a percentage of downswing time.
The relative percentage times for wrist un-cocking
Table II. Displacement data for pelvis axial rotation and translation, and pelvis–thorax data for specific events and phases throughout the
swing (mean+ s).
Segment
Displacement between events
BS to TB TB to WU WU to LAH LAH TO IM
Pelvis angular displacement (ZP axis) (8) 751.49+9.56 30.46+19.56 25.17+ 18.03 43.24+ 8.47
Pelvis linear displacement (XG axis) (m) 70.05+0.06* 0.07+0.04 0.05+ 0.05 0.03+ 0.02
Differential at events (8)
TB WU LAH IM
Pelvis–thorax differential (8) 718.33+ 10.36* 724.69+12.86 723.37+11.75 711.38+ 9.91
Pelvis-thorax angular velocity (8 � s71) 741.28+ 50.42 40.44+95.40 96.96+101.94 134.12+ 79.4
Abbreviations: BS¼ start of backswing, TB¼ top of backswing, WU¼wrist un-cocking, LAH¼ left-arm horizontal, IM¼ impact.
*P5 0.05 within the ANCOVA model.
Figure 3. Time at which wrist un-cocking began (¤) and when the
left arm was horizontal (') expressed as a percentage of normalised
total downswing time on the primary y axis, and club head speed
data (~) presented on the secondary y axis. Data are presented in
ascending clubhead speed order.
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and left-arm horizontal events would suggest varia-
tion across participants, in that some initiate an early
un-cocking relative to the top of the backswing (0%)
and others delay this action until closer to the event
coinciding with their left arm being horizontal.
Figure 4 represents pelvis–thorax differential data
at events within the swing plotted against clubhead
speed for all participants. Again, the dispersion of
these data points would suggest variation across
participants, with only values at the top of the
backswing showing significance within the ANCO-
VA model.
Discussion
The main aim of the study was to establish the key
parameters associated with the drive golf swings of a
group of low handicap female golfers with a
particular focus on the axial rotation movement
patterns of the pelvis and thorax, as well as temporal
characteristics of the swing. In addition, the study
aimed to determine if there is a common optimal
swing based on these parameters for this group of
highly skilled female golfers using an ANCOVA to
consider between-participant and within-participant
variation in relation to performance. Mean clubhead
speed (39.48+ 2.48 m � s71) and mean ball speed
(55.7+ 3.93 m � s71) were both consistent with a
recent similar study of female golfers (Horan et al.,
2010). The results suggest that greater clubhead
speed was obtained by increasing the pelvis–thorax
differential at the top of the backswing in agreement
with several previous studies (Egret et al., 2006;
Myers et al., 2008; Zheng et al., 2008), and at the
same time increasing the linear displacement (trans-
lation) of the pelvis away from the target along the
laboratory XG axis (Figure 1) during the backswing
in agreement with Horan et al. (2010). It also
appears that faster clubhead speeds require a quicker
backswing, in agreement with Zheng et al. (2008).
The significant correlation found between the
sitting flexibility test and clubhead speed further
supports these findings, since increasing thorax
rotation relative to the pelvis, as seen at the top of
the backswing, would seem to give optimal set-up
position for the initiation of the downswing. In
addition, this relationship between clubhead speed
and flexibility appears to validate the idea that the
pelvis–thorax separation at the top of the backswing
is not simply a secondary phenomenon but is
influential in the generation of clubhead speed.
These variables therefore seem to indicate that the
backswing unsurprisingly plays an important role in
determining the outcome of the swing, but that the
group of golfers used here have established their own
technique during the downswing to generate the
clubhead speeds shown; there are no common
characteristics during the downswing that can
account for the differences in clubhead speeds within
the group. The results provide further evidence of
the nature of elite amateur female golfers’ swing
patterns, as well as adding weight to the limitations of
assuming that a common technique should be
adopted by all golfers for optimal performance.
The conclusions of previous studies on pelvis–
thorax separation have been based on the suggested
utilisation of greater elastic energy produced as a
result of increased pelvis–thorax separation particu-
larly at the top of the backswing. Okuda and
colleagues (Okuda, Armstrong, Tsunezumi, &
Yoshiike, 2002) describe the coiling of the trunk in
terms of generating a stretch in the muscles of the
trunk as a consequence of rotating away from the
address position, and the lower body moving in
the opposite direction to the upper body at the start
of the downswing creating the proximal-to-distal
sequence commonly associated with golf swings. In
agreement with the present study, this separation
certainly appears to be important at the top of the
backswing, but in agreement with Zheng et al.
(2008) who report that females produce less of an
uncoiling effect than males between the top of the
backswing and impact, the present study does not
support the idea that the stretch–shortening cycle is a
determinant of clubhead speed during the down-
swing phase or at ball impact in female golfers. Myers
et al. (2008) found a moderate correlation between
torso–pelvis separation rotational velocity (akin to
the present study’s consideration of pelvis–thorax
angular velocity) and ball velocity at lead-arm
parallel (equivalent to left-arm horizontal in the
present study) and 40 ms before impact in a group of
male golfers, which supports the idea of the utilisa-
tion of the stretch–shortening cycle during the
downswing. However, the lack of support for this
in the present study and evidence of decreases in
musculotendinous stiffness in females compared
with males (Blackburn et al., 2004, 2006; Gajdosik
et al., 1990) may account for the differences in
Figure 4. Mean pelvis–thorax differential and clubhead speed
values for all participants at the top of the backswing (¤, TB), left-
arm horizontal (', LAH), and impact (~, IM)
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techniques used and reported clubhead speeds, since
the strain energy derived and available from the
pelvis–horax separation may be reduced in females.
Certainly, the present findings did not suggest that
any of these variables associated with the stretch–
shortening cycle during the downswing consistently
played a role in explaining the variance in clubhead
speed. Further consideration of the data might
suggest that some golfers create more separation,
and some larger angular velocities, but that these
alone cannot explain the variance in clubhead speeds
in all golfers, since other equally long hitters showed
an alternative swing pattern.
The group of golfers who participated in the
present study all used their own driver, and in all
cases this was a club designed for use by male golfers,
which tend to have a greater overall mass than those
designed specifically for females. However, given the
moderate relationship of left-hand grip strength to
clubhead speed found in this study and that there
appears to be no relationship between the players’
height and shaft length selected, it is perhaps not
surprising that the inertial effects of a heavier
clubhead and longer shaft may influence the dy-
namics of the swing, particularly during the transi-
tion phase at the top of the backswing. Indeed,
Kaneko and Sato (2000) found that when the total
club mass was increased, the joint torques of the
shoulders and torso in the latter half of the down-
swing were increased, encouraging an early wrist
release. This may impact on the technique used by
the female golfers in terms of compensating for the
increase in proportional effort needed to compensate
for the inertial effects of the golf club compared with
their male counterparts while using the same
equipment. Given that left-hand grip strength was
only moderately correlated with clubhead speed
(r¼ 0.54, P5 0.05) in this group, these golfers
appear to be selecting their own strategies during
the transition and downswing phases to optimise
clubhead speeds. Consideration of the temporal
characteristics shown in Figure 3 would suggest that
the timing of the action of wrist un-cocking differs
between players, some initiating this motion at the
top of the backswing, others delaying until left-arm
horizontal. There is also evidence (Table I) that a
shorter backswing could assist in generating faster
clubhead speeds but equally this could, if it is also
faster, result in a greater inertial effect at the
transition between backswing and downswing. This
action could well be affected by the inertial para-
meters of the club during the transition phase and
would require greater strength to generate the force
required to change direction. This club–player
interaction therefore warrants further study and
may indicate some of the variation between golfers,
but also the difference in technique adopted by male
and female golfers.
Comparing groups of athletes in an attempt to
define common key variables present in elite
performers is prevalent in the biomechanical litera-
ture. While the ANCOVA provided some indication
of the determinants of clubhead speed in the group
of female golfers tested, it is evident that each golfer
may find her own solution to the problem of
optimising clubhead speeds given the influence of
the participant fixed factor in the analysis and the
variables that did not appear to be significant within
the model. Horan et al. (2010) also suggest that
swing kinematics previously reported as optimal for
male golfers may not be appropriate for females, and
Bartlett et al. (2007) support the notion of athletes
not relying on a common technique for optimal
performance even among elite performers.
In conclusion, aspects of the backswing phase of
the golf swing do appear to be critical in determining
faster clubhead speeds in this group of female golfers.
However, no characteristics were found to establish a
common optimal technique used by these golfers
during the downswing, contrary to previous studies;
some participants showed similarities to previously
presented data but others did not, regardless of
clubhead speed. Critically, it would appear that
individual techniques, whether related to movement
frequency preferences, equipment selection, anthro-
pometric characteristics, or more likely a combina-
tion of these, are prevalent within this group of low
handicap female golfers and contribute in different
ways to each player’s swing pattern. In exploring the
swing characteristics of this group of female golfers, a
valuable story is emerging: assuming that there is a
common technique that produces optimal perfor-
mance appears to be invalid for low handicap female
golfers, and therefore studies that aim to assess the
impact of such characteristics on clubhead speed
may benefit from considering the individual rather
than group data. Nonetheless, we acknowledge that
limiting the analysis to the gross movement patterns
of the pelvis and thorax may not allow consideration
of the complete energy flow through the swing, and
therefore a more detailed analysis of additional inter-
segment interactions is required. In doing so, golf
coaching strategies can be better informed resulting
in improved performance and reduced potential for
injury.
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