Measurement of Dynamic Scapular Kinematics Using an Acromion Marker Cluster to Minimize Skin Movement Artifact

Summary

This report presents details of how to adopt the acromion marker cluster method of obtaining scapular kinematics when using a passive marker motion capture device. As has been described in the literature, this method provides a robust, non-invasive, three-dimensional, dynamic and valid measurement of scapular kinematics, minimizing skin movement artifact.

Abstract

The measurement of dynamic scapular kinematics is complex due to the sliding nature of the scapula beneath the skin surface. The aim of the study was to clearly describe the acromion marker cluster (AMC) method of determining scapular kinematics when using a passive marker motion capture system, with consideration for the sources of error which could affect the validity and reliability of measurements. The AMC method involves placing a cluster of markers over the posterior acromion, and through calibration of anatomical landmarks with respect to the marker cluster it is possible to obtain valid measurements of scapular kinematics. The reliability of the method was examined between two days in a group of 15 healthy individuals (aged 19-38 years, eight males) as they performed arm elevation, to 120°, and lowering in the frontal, scapular and sagittal planes. Results showed that between-day reliability was good for upward scapular rotation (Coefficient of Multiple Correlation; CMC = 0.92) and posterior tilt (CMC = 0.70) but fair for internal rotation (CMC = 0.53) during the arm elevation phase. The waveform error was lower for upward rotation (2.7° to 4.4°) and posterior tilt (1.3° to 2.8°), compared to internal rotation (5.4° to 7.3°). The reliability during the lowering phase was comparable to results observed during the elevation phase. If the protocol outlined in this study is adhered to, the AMC provides a reliable measurement of upward rotation and posterior tilt during the elevation and lowering phases of arm movement.

Introduction

Objective, quantitative measurement of scapular kinematics can provide an assessment of abnormal movement patterns associated with shoulder dysfunction¹, such as reduced upward rotation and posterior tilt during arm elevation observed in shoulder impingement^2-8. Measurement of scapular kinematics, however, is difficult due to the bone’s deep position and gliding nature beneath the skin surface¹. Typical kinematic measurement techniques of attaching reflective markers over anatomical landmarks do not adequately track the scapula as it glides beneath the skin surface⁹. Various methods have been adopted throughout the literature to overcome these difficulties, including; imaging (X-ray or magnetic resonance)^10-14, goniometers^15,16, bone pins^17-22, manual palpation^23,24, and the acromion method^3,5,19,25. Each method, however, has its limitations which include: exposure to radiation, projection errors in the case of two-dimensional image based analysis, require repeated subjective interpretation of the location of the scapula, are static in nature or are highly invasive (e.g. bone pins).

A solution to overcome some of these difficulties is to employ the acromion method where an electromagnetic sensor is attached to the flat portion of the acromion²⁵, a flat portion of bone which extends anteriorly at the most lateral part of the scapula leading from the spine of the scapula. The principle idea behind using the acromion method is to reduce skin movement artifact, as the acromion has been shown to have the least amount of skin movement artifact compared to other sites on the scapula²⁶. The acromion method is non-invasive and provides dynamic three-dimensional measurement of scapular kinematics. Validation studies have shown the acromion method to be valid up to 120° during the arm elevation phase when using electromagnetic sensors^17,27. When using marker based motion capture devices a series of markers arranged in a cluster, the acromion marker cluster (AMC), is required and has been shown to be valid when using an active-marker motion capture system²⁸ and whilst using a passive-marker motion capture system during arm elevation and arm lowering²⁹.

The use of the AMC with a passive marker motion capture device for measuring scapular kinematics has been used to assess changes in scapular kinematics following an intervention to address shoulder impingement³⁰. The valid use of this method, however, depends on the ability to accurately apply the cluster of markers, the position of which has been shown to affect results³¹, calibrate anatomical landmarks³² and ensuring arm movements are within a valid range of motion (i.e. below 120° arm elevation)²⁹. It has also been suggested the reapplication of the marker cluster, when using an active marker based motion capture system, was found to be the source of increased error for scapular posterior tilt²⁸. It is, therefore, important to establish the between-day reliability of the acromion method to ensure it provides a stable measure of scapular kinematics. Ensuring that measurements are reliable will enable changes in scapular kinematics, due to an intervention, for example, to be measured and examined. The methods used to measure scapular kinematics have been described elsewhere^29,33; the aim of the present study was to provide a step-by-step guide and reference tool for applying these methods using a passive-marker motion capture system, with consideration to the potential sources of error, and to examine the reliability of the measurement method.

Protocol

NOTE: The use of human participants was approved by the Faculty of Health Sciences Ethics Committee at the University of Southampton. All participants signed consent forms before data collection commenced. For the data presented in this study kinematics were recorded using a passive marker motion capture system consisting of 12 cameras; six 4-megapixel cameras and six 16-megapixel cameras operating at sampling frequency of 120 Hz.

1. Participant Preparation

1. Ask subjects to remove their upper body clothing or to wear a sports bra, vest, or strapless top. It is important that clothing does not interfere with the movement of the markers or occlude markers from the view of the cameras.
2. Construct an acromion marker cluster consisting of an ‘L’ shaped piece of plastic 70 mm in length along each aspect. Attach three retroreflective markers to the AMC, one on the end of each end of each aspect and one where each aspect meet (Figure 1).
3. Attach the acromion marker cluster (AMC) onto the posterior portion of the acromion where the acromion meets the scapular spine, using double sided adhesive tape. One aspect of the plate should follow the spine of the scapula pointing medially, the other should point anterior to the scapular plane (Figure 1).
4. Attach a cluster marker set to the upper arm using straps (Figure 2).
5. Attach retroreflective markers to the following anatomical landmarks at recommended by the International Society of Biomechanics³³ (Figures 1 & 2): Sternal notch (IJ; Deepest joint of the sternal notch), Xiphoid process (PX; Most caudal point on the sternum), C7 (Spinous process of the C7 vertebra), T8 (Spinous process of the T8 vertebra), Sternoclavicular joint (SC; Most ventral point on the sternoclavicular joint), Radial styloid (Most caudal point on the radial styloid), and Ulnar styloid (Most caudal point on the ulnar styloid).

Figure 1: Position of the acromion marker cluster, C7 and T8 anatomical markers. This figure has been modified from Warner, M. B., Chappell, P. H. & Stokes, M. J. Measuring scapular kinematics during arm lowering using the acromion marker cluster. Hum. Mov. Sci. 31, 386-396, doi:http://dx.doi.org/10.1016/j.humov.2011.07.004 (2012).

Figure 2: Marker locations for the sternal notch (IJ), xiphoid process (PX), sternoclavicular (SC), upper arm cluster, ulnar styloid (US), radial styloid (RS).

2. Participant Calibration

NOTE: Locations of the scapula’s anatomical landmarks need to be determined with respect to the acromion marker cluster. Calibration of the landmarks is required for each participant.

1. Construct a calibration wand consisting of four reflective markers placed into a ‘T’ formation (Figure 3). Measure the distance from the tip of the calibration wand to the first wand marker.
2. Palpate and locate the following anatomical landmarks as recommended by the International Society of Biomechanics³³. Place the tip of the calibration wand on the landmark (Figure 3). Capture three seconds of data with the motion capture system ensuring the markers on the wand, the AMC and upper arm cluster are all visible to the cameras.
   1. Acromioclavicular joint (AC) — Place a hand on the clavicle, then move laterally until the point where the clavicle reaches the acromion. Place the tip of the wand at the joint between the clavicle and acromion.
   2. Acromion angle (AA) — Palpate along the spine of the scapula to the most lateral point. Place the tip of the wand on the dorsal aspect of the acromion at the most lateral point (Figure 3).
   3. Medial spine of the scapula (TS) — Palpate along the spine of the scapula to the most medial point. Place the tip of the wand at the point where the spine meets the medial border of the scapula.
   4. Inferior angle of the scapula (AI) — Palpate inferiorly along the medial border of the scapula. Place the tip of the wand on the most caudal point of the scapula.
   5. Medial epicondyle (EM) — With the participant’s elbow in 90° of flexion pointing forward, with their thumb pointing upwards, place a hand on the medial side of the elbow to locate the medial epicondyle. Place the tip of the wand on the most caudal point of the medial epicondyle.
   6. Lateral epicondyles (EL) — With the participant’s elbow in 90° of flexion pointing forward, with their thumb pointing upwards, place a hand on the lateral side of the elbow to locate the lateral epicondyle. Place the tip of the wand on the most caudal point of the lateral epicondyle.
3. To determine the glenohumeral joint center, ask the participant to perform a circumduction movement with their upper arm with the elbow fully extended, from zero degrees arm elevation to approximately 40° arm elevation. They must perform this movement whilst aiming to minimize protraction/retraction and elevation/depression of the shoulder complex; the investigator can provide assistance if necessary. Record this movement for approximately 30 sec.

Figure 3: Calibration wand used to locate anatomical bony landmark with respect the acromion marker cluster (AMC).

3. Experiment Protocol

1. Ask participant to perform arm elevation from zero to 120° arm elevation, and then lower their arm back down to rest by their side in the sagittal, frontal and scapular plane. The scapular plane is approximately 40° anterior to the frontal plane.

4. Post-processing of Kinematic Data

NOTE: The following steps detail the procedure needed to calculate scapular kinematics during the dynamic movement trials. These steps have been described and explored extensively within the literature^21,33,34 and the purpose of the following section is to provide a synthesis and step-by-step guide to implementing the modeling steps required to obtain scapular kinematics. The application of these steps is conducted in relevant kinematic modeling software. The software contains commands to enable the creation of local coordinate systems, the conversion of coordinates from a global to local coordinate system, the conversion of coordinates from local to global coordinate systems and the calculation of Euler angle rotations. These steps will allow the scapula, humerus and thorax to be defined as rigid bodies. Subsequently rotation of the scapula with respect the thorax, and the humerus with respect thorax can then be determined.

1. Using the coordinates of markers on the AMC, define an arbitrary local coordinate system for the AMC (Figure 4a). For each scapular anatomical landmark calibration trial, determine the location of the tip of the wand, which represents the location of the anatomical landmark, with respect the local coordinate system on the AMC using the following steps.
   NOTE: Kinematic modeling software contain commands to enable the creation of local coordinate systems and conversion of coordinates from a global to a local coordinates, see Figure 4 for example commands.
   1. Use the markers on the wand to create a local coordinate system for the wand (Figure 4a) using the following command in the kinematic modeling software: AMC= [AMCO,AMCA-AMCO,AMCO-AMCM,xyz] where AMCO, AMCA and AMCM are the labels given to the markers on the AMC.
   2. Using the kinematic modeling software, calculate the location of the tip of the wand in the global coordinate system. In the example provided this is 83 mm from the marker 1 (M1) along the X axis of the wand (Figure 4b); use the command: Wand = [M1,M1-M2,M3-M4,xyz] and Wandtip = M1+{83,0,0}*ATTITUDE(Wand) where M1, M2, M3 and M4 are the labels given to the markers on the wand.
   3. Determine the location of the tip of the wand with respect to the local coordinate system of the AMC ($%AA) (Figure 4c) using the modeling commands: $%AA = WandTip/AMC and PARAM($%AA).
   4. Repeat steps 4.1.1 to 4.1.3 for each scapular anatomical landmark.
   5. Determine the location of the medial and lateral epicondyles with respect to the humerus marker cluster, instead of the AMC, using the using the above steps.
2. Use the dynamic calibration trial to calculate the location of the glenohumeral joint center with respect to the scapula. Calculate the position of the glenohumeral joint center, with respect to the scapula, as the pivot point of the helical axis between the humerus and scapula. For more details on this technique refer to Veeger³⁵.
3. Calculate the elbow joint center (ELJC) as the mid-distance between the lateral (EL) and medial epicondyles (EM) of the humerus; ELJC = (EM + EL) / 2.
4. During the dynamic trials, use the known position of the anatomical landmarks with respect to the AMC to determine the location of the anatomical landmarks within the global coordinate system (Figure 5).
   NOTE: Modeling software contain commands to enable conversion of coordinates from local coordinate systems to global coordinate systems, see Figure 5 for example commands.
   1. Refer to Figure 5a that shows the location of the acromion angle landmark with respect to the AMC ($%AA) as described in point 4.1.
   2. Convert the location of $%AA virtual marker to the global coordinate system for each time point during the dynamic trial to create the acromion angle (AA) landmark (Figure 5b) using the following kinematic modeling command: AA = $%AA*AMC and OUTPUT(AA).
   3. Repeat steps 4.4.2 for each anatomical landmark.
5. Define a local coordinate system for the thorax and scapula by calculating the unit vectors between the relevant markers to represent each axis for a given rigid body using the following kinematic modeling command: Scapula = [AA,TS-AA,AA-AI,zxy]. Thorax = [IJ,MUTHX-MLTHX,IJ-C7,yzx], where MUTHX is the mid-point between the IJ and C7 landmark and MLTHX is the mid-point between the PX and T8 landmarks.
   NOTE: The axes definition are based on International Society of Biomechanics’ (ISB) recommendations³³ (Table 1 and Figure 6).
   1. Using a similar method, define a local coordinate system for the humerus using ‘Option 2’ as recommended by the ISB³³.
      NOTE: Option 2 requires a sufficient plane formed by the gleohumeral joint center, elbow joint center and the ulna styloid, i.e. a degree of elbow flexion is required. If the participant approaches full elbow extension, the humeral axes may become unstable and therefore ‘Option 1’ should be used (Table 1). See Wu et al. (2005) for further details.
6. Determine the orientation of the scapula relative to the thorax for each time point during the dynamic trial using the Euler angle decomposition method with a rotation sequence of internal rotation (Y), upward rotation (X’) and posterior tilt (Z’’)³³ using the following kinematic modeling command: ScapularKin = - (Figure 7).
7. Determine the orientation of the humerus with respect to the thorax during the dynamic trial using a non-cardan rotation sequence of Y (plane of elevation), X’ (elevation) and Y’’ (axial rotation)³⁶ using relevant kinematic modeling software.
   NOTE: A macro is available to download from the manufacturer in order to determine non-cardan rotation sequences within the kinematic modeling software used in this manuscript.

MUTHX = mid-point between IJ and C7. MLTHX = mid-point between PX and T8. GH = glenohumeral joint center. ELJC = elbow joint center.

Mathematical operators:

^ = cross product of two vectors

|| = absolute value of a vector

Table 1: Local coordinate system for each rigid segment.

5. Data Reduction and Analysis

NOTE: The following data reduction and analysis steps are performed in numerical modeling software (such as MATLAB) that allows manipulation of data matrices. The kinematic data is divided into the elevation and lowering phases of humeral movement, time normalized for each phase of movement, then scapular kinematics are expressed relative to humeral elevation angle.

1. Determine the elevation and lowering phase of the humeral elevation as described below (Figure 8). These phases are determined from the angular velocity of the humeral elevation angle (Figure 8). See ElevationLoweringPhases.m function file.
   1. Determine the start of humeral elevation when the angular velocity of the humerus exceeds a threshold 2% of the maximal humeral angular velocity.
   2. Determine the end of the elevation phase as the point at which the humeral angular velocity falls below 2% of the maximal humeral angular velocity, or when humeral elevation exceeds 120°.
   3. Determine the start of the humeral lowering phase when the angular velocity falls below 2% of the minimum angular velocity, or the point at which humeral elevation falls below 120°.
   4. Determine the end of the lowering phase when the angular velocity exceeds 2% of the minimum angular velocity.
2. Normalize the data by interpolating the kinematic data in each phase of movement to 101 data points (Figure 9). See Time_normalisation.m function file.
3. Express scapular kinematics in relation to humeral elevation by plotting the arm angle (degrees) vs. upward rotation (degrees) (Figure 10). See PlotScapHumRhythm.m function file.

Results

Fifteen participants who had no known history of shoulder, neck or arm injuries were recruited onto the study (Table 2). To assess intra-rater (between-day) reliability, participants attended two data collection sessions separated by at least 24 hours and a maximum of 7 days. During each data collection session, the same investigator performed the protocol for attaching reflective markers, the acromion marker cluster and anatomical landmark calibrations, as detailed above. The reliability of the kinematic waveform obtained from dynamic trials was assessed using coefficient of multiple correlation (CMC)³⁷. Waveform measurement error was used to assess the amount of error between days (σ^b)³⁸.

	Age (years)	Weight (kg)	Height (m)	Body mass index (kg/m²)
Group (n=15)	24.9 ± 4.4	65.8 ± 11.7	1.7­± 0.1	22.6 ± 2.3
	19 – 38	48 – 86	1.5 – 1.9	18.3 – 36.5
Males (n=8)	25.1 ± 1.5	73.4 ± 9.9	1.8 ± 0.06	23.2 ± 2.4
	23 – 27	62 – 86	1.7 – 1.9	19.8 – 26.4
Females (n=7)	24.6 ± 1.5	57 ± 6.3	1.6 ± 0.06	21.9 ± 2.2
	23 – 27	48 – 68.5	154 – 170	18.3 – 24.2

Table 2. Participant demographics, mean ± standard deviation (SD) and range.

The intra-rater (between-day) reliability produced high CMC (>0.92) for upward rotation and posterior tilt (>0.69) during humeral elevation and lowering in all planes of arm movement. Internal rotation demonstrated lower CMC values (0.44 to 0.76) during all planes of arm elevation and lowering (Table 3). This was also reflected in the waveform measurement error with generally lower error values for upward rotation (σ^b = 2.7° to 4.4°) and posterior tilt (σ^b = 1.3° to 2.8°), indicating good reliability, compared to internal rotation (σ^b = 3.9° to 7.3°) (Table 3). There did not appear to be any bias between days, with similar waveform patterns obtained for upward rotation, posterior tilt and internal rotation during both the elevation and lowering phases (Figure 10).

Figure 4. A) Local coordinate system of the acromion marker cluster (AMC) as determined by the three markers on the AMC (AMCO, AMCA, AMCM). B) Local coordinate system of the wand using the four markers attached to the wand (M1, M2, M3, and M4). The tip of the wand is subsequently calculated as a point 83 mm from the M1 marker along the X axis of the wand. C) The location of the tip of the wand, which represents the location of the anatomical landmark within the global coordinate system, is determined with respect to the local coordinate system of the AMC. Example kinematic modeling commands are given for each step. This figure has been modified from Warner, M. B., Chappell, P. H. & Stokes, M. J. Measuring scapular kinematics during arm lowering using the acromion marker cluster. Hum. Mov. Sci. 31, 386-396, doi:http://dx.doi.org/10.1016/j.humov.2011.07.004 (2012).

Figure 5. A) The location of the acromion angle landmark with respect to the local coordinate system of the acromion marker cluster. B) The conversion of the acromion angle (AA) landmark from the local to the global coordinate system (black axes).

Figure 6. Local coordinate system of the scapula defined by the locations of the acromion angle (AA), medial spine of the scapula (TS) and the inferior angle (AI) following International Society of Biomechanics Recommendations. Example kinematic modeling commands are provided. This figure has been modified from Warner, M. B., Chappell, P. H. & Stokes, M. J. Measuring scapular kinematics during arm lowering using the acromion marker cluster. Hum. Mov. Sci. 31, 386-396, doi:http://dx.doi.org/10.1016/j.humov.2011.07.004 (2012).

Figure 7. Euler angle rotations of the scapula around each axis, with respect to the thorax, following a rotation sequence of internal rotation (Y), upward rotation (X’) and posterior tilt (Z”). This figure has been modified from Warner, M. B., Chappell, P. H. & Stokes, M. J. Measuring scapular kinematics during arm lowering using the acromion marker cluster. Hum. Mov. Sci. 31, 386-396, doi:http://dx.doi.org/10.1016/j.humov.2011.07.004 (2012).

Figure 8. A) Humeral elevation and lowering with the start and end of each phase denoted by the green dotted lines. B) Humeral angular velocity used to determine the start and end of each phase. The uppermost red dashed line represents the threshold used to determine the start and end of the elevation phase. The lowermost red dashed line represents the threshold used to determine the start and end of the lowering phase. Green dotted lines represent the points at which the angular velocity exceeded the thresholds.

Figure 9. Scapular upward rotation during arm elevation that has been interpolated over 101 data points to normalize with respect to time.

Figure 10. Kinematic waveforms of the scapula for day one (black) and day two (grey). Scapular rotations during sagittal plane arm movement shown are; upward rotation during the elevation (A) and lowering phase (B), posterior tilt during the elevation (C) and lowering phase (D) and internal rotation during the elevation (E) and lowering phase (F). Dashed lines represent ±1 standard deviation.

Scapular rotation	Phase of arm movement	Sagittal plane		Scapular plane		Frontal plane
		CMC	Waveform error	CMC	Waveform error	CMC	Waveform error
Internal rotation	Elevation	0.44 ± 0.3	7.3° ± 1.6	0.50 ± 0.2	6.7° ± 0.8	0.44 ± 0.3	3.9° ± 1.5
Upward rotation		0.93 ± 0.1	3.1° ± 1.6	0.94 ± 0.1	3.4° ± 1.0	0.93 ± 0.1	2.7° ± 1.5
Posterior tilt		0.69 ± 0.2	2.3° ± 0.9	0.78 ± 0.2	1.4° ± 0.5	0.82 ± 0.2	1.3° ± 0.3
Internal rotation	Lowering	0.53 ± 0.3	7.0° ± 1.4	0.45 ± 0.2	7.2° ± 1.1	0.76 ± 0.2	5.4° ± 2.9
Upward rotation		0.94 ± 0.0	4.4° ± 1.0	0.92 ± 0.1	4.3° ± 1.1	0.94 ± 0.1	3.9° ± 1.7
Posterior tilt		0.70 ± 0.2	2.5° ± 1.4	0.77 ± 0.2	1.8° ± 0.9	0.87 ± 0.1	2.8° ± 0.8

CMC = Coefficient of multiple correlation.

Table 3. Intra-rater (between-days) reliability of the acromion marker cluster as determined by the coefficient of multiple correlation and waveform error.

Discussion

The choice of methodology for determining scapular kinematics is crucial, and consideration of the validity, reliability and its appropriateness for the research study should be given. Various methods have been adopted throughout the literature but each method has its limitations. The acromion marker cluster overcomes a number of these limitations, such as projection errors from 2D imaging or requiring repeated interpretation of the location of the scapula by providing non-invasive dynamic kinematic measurement of the scapula. However, the AMC method is still susceptible to skin movement artifact, particularly at higher arm elevation angles and brings into question the validity of the method at these higher arm positions. A previous study that assessed the validity of the method outlined in the present study, has shown that at arm elevation above 120 degrees the measurement error becomes too large and the method is no longer valid²⁹. However, the study also demonstrated that when the arm returns to a position below 120 degrees following arm high arm elevation the acromion marker cluster method remains valid²⁹. It is possible to reduce the errors at higher arm elevation angles by performing the calibration of the anatomical landmarks with the arm elevated³². However, this increases the error at lower arm elevation angles. Therefore, it is important to consider the aims of the study for which scapular kinematics are being determined and decide the optimal arm elevation position with which to calibrate the anatomical landmarks.

In order for any measurement technique to be considered a viable tool it is important to establish its reliability. The data presented in the present paper have shown that the acromion marker cluster can be classified as having excellent to good between-day reliability for scapular upward rotation and posterior tilt respectively. These finding were observed when examining the entire kinematic waveform during the elevation and lowering phases, demonstrating that the acromion marker cluster is a reliable method of measurement during both phases of arm movement. In a previous studies, the repositioning of the acromion marker cluster had been shown to adversely affect reliability^27,28, particularly the reliability of scapular posterior tilt when comparing different investigators.²⁸ The results from the present study, however, demonstrate that posterior tilt was a reliable measurement between days. Differences in methodology between the study of van Andel (2008) and the present study which include the type of motion capture system (active marker vs. passive marker), and the design and attachment site of the acromion marker cluster may account for the differences observed. In addition, it is known that the positioning of the acromion marker cluster onto different areas of the acromion affects the accuracy of the measurement³¹. Although the present study demonstrated good between day reliability, care must be taken when attaching the acromion marker cluster to the participant to ensure valid and reliable results are obtained.

Although good and excellent reliability was observed for upward rotation and posterior tilt, internal rotation of the scapula demonstrated poor to fair reliability when examining the entire kinematic waveform. This is in agreement with previous studies that have also found lower CMC results for internal rotation (0.82) and greater error (4.3°) when compared to upward rotation and posterior tilt (CMC = 0.94 and 0.85, error = 3.3° and 3.4° respectively)^39,40. Internal rotation is, therefore, the least reliable of the scapular rotations. The reason why internal rotation has poorer reliability may be due to the lower range of motion (~5°) observed compared to other scapular rotations. The reported errors in the kinematic waveforms range from 3.9° to 7.3° meaning that the errors are in some cases larger than the motion taking place. In addition, within participant variability is inherently large^3,18,41. The poor reliability may, therefore, not be as a result of the measurement technique, but rather the inherent individual variability coupled with a small range of motion. Caution should be taken when examining repeated measurements of internal scapular rotations.

The aim of measuring scapular kinematics is to quantify scapular dyskinesis, which is often observed clinically in patients with shoulder impingement¹, and subsequently assess the changes in scapular kinematics following treatment interventions to reduce the effects of shoulder impingement³⁰. The technique described in the present study has been used to demonstrate alterations in scapular kinematics in a group of individuals with shoulder impingement following a motor control retraining exercise³⁰ and has been shown to be valid²⁹ and reliable.

Materials

List of materials used in this article

Name	Company	Catalog Number	Comments
Passive marker capture system	Vicon Motion Systems	N/A
Nexus	Vicon Motion Systems	N/A	Data capture software
Bodybuilder	Vicon Motion Systems	N/A	Modeling software
14 mm retro reflective markers	Vicon Motion Systems	VACC-V162B
6.5 mm retro reflective markers	Vicon Motion Systems	VACC-V166
Calibration wand	Vicon Motion Systems	N/A
Plastic base	N/A	N/A	Constructed 'in-house'
Matlab	Mathworks	N/A	Numerical modelling software