- Research article
- Open Access
- Open Peer Review
Validity and test-retest reliability of manual goniometers for measuring passive hip range of motion in femoroacetabular impingement patients.
© Nussbaumer et al; licensee BioMed Central Ltd. 2010
- Received: 1 March 2010
- Accepted: 31 August 2010
- Published: 31 August 2010
The aims of this study were to evaluate the construct validity (known group), concurrent validity (criterion based) and test-retest (intra-rater) reliability of manual goniometers to measure passive hip range of motion (ROM) in femoroacetabular impingement patients and healthy controls.
Passive hip flexion, abduction, adduction, internal and external rotation ROMs were simultaneously measured with a conventional goniometer and an electromagnetic tracking system (ETS) on two different testing sessions. A total of 15 patients and 15 sex- and age-matched healthy controls participated in the study.
The goniometer provided greater hip ROM values compared to the ETS (range 2.0-18.9 degrees; P < 0.001); good concurrent validity was only achieved for hip abduction and internal rotation, with intraclass correlation coefficients (ICC) of 0.94 and 0.88, respectively. Both devices detected lower hip abduction ROM in patients compared to controls (P < 0.01). Test-retest reliability was good with ICCs higher 0.90, except for hip adduction (0.82-0.84). Reliability estimates did not differ between the goniometer and the ETS.
The present study suggests that goniometer-based assessments considerably overestimate hip joint ROM by measuring intersegmental angles (e.g., thigh flexion on trunk for hip flexion) rather than true hip ROM. It is likely that uncontrolled pelvic rotation and tilt due to difficulties in placing the goniometer properly and in performing the anatomically correct ROM contribute to the overrating of the arc of these motions. Nevertheless, conventional manual goniometers can be used with confidence for longitudinal assessments in the clinic.
- Intraclass Correlation Coefficient
- Electromagnetic Tracking System
- Manual Goniometer
- High Intraclass Correlation Coefficient
- Thigh Flexion
Hip joint range of motion (ROM) is a basic clinical parameter for diagnosing hip diseases, such as osteoarthritis [1, 2] or femoroacetabular impingement (FAI) [3, 4], and for monitoring the efficacy of a treatment . Hip joint ROM is widely assessed using low-technology tools such as manual goniometers or inclinometers. The advantages of goniometry are the simplicity in assessing ROM, the direct measurement of joint angles without any data reduction process and the low cost of the instrument. The two-arm goniometer is still the most commonly used, economical and portable device for the evaluation of ROM , despite acknowledged limitations. Major drawbacks of goniometry are that the starting position, the center of rotation, the long axis of the limb and the true vertical and horizontal positions can only be visually estimated; moreover, conventional goniometers must be held with two hands, leaving neither hand free for stabilization of the body or the proximal part of the joint . There are also difficulties in monitoring joints that are surrounded by large amounts of soft tissue, such as the hip . In addition, manual goniometers assess joint flexibility only in two dimensions; however, as most of the hip ROM measures in clinical practice are practically in-plane movements, this limitation is minor. The validity (i.e., the degree to which a measurement actually measures what it claims to measure) and reliability (i.e., the degree to which a measurement is consistent and stable) of manual goniometers have therefore been questioned, especially for measuring hip flexion. Bohannon et al.  showed that in the hip flexion movement, as measured in a clinical setting, more than a quarter of the ROM can be attributed to pelvic tilt, leading to an immense misinterpretation of this movement due to the insensitivity of manual goniometers for secondary pelvic movement. Elson and Aspinall  proposed a new method for measuring range of hip flexion by palpating the lumbosacral junction to allow early identification of lumbar spine flexion which accompanies hip flexion.
Three-dimensional measurement tools based on electromagnetic tracking have recently been used to precisely measure shoulder [10–12] and spine [13, 14] ROM, as well as patellofemoral  and hip joint  kinematics. Electromagnetic tracking systems (ETS) enable the direct measurement of a three-dimensional position and the orientation of multiple sensors referred to a stationary source (transmitter). As ETS may well provide the reference standard to assess the ROM of the musculoskeletal system  in a clinical setting, concurrent use of ETS and simple two-dimensional measurement devices is a possible method to determine the validity of goniometers to yield plausible and useful objective ROM data [18–20].
Thus, the aims of this study were (i) to verify the validity of a conventional manual goniometer (i.e., the standard instrument for clinical assessments) to measure passive hip ROM against a criterion standard instrument (ETS) (concurrent validity) and to discriminate between individuals with and without FAI (known group construct validity), and (ii) to examine the test-retest (intra-rater) reliability of hip ROM goniometric and ETS assessments.
A total of 15 subjects (7 women) with a diagnosis of FAI, verified both clinically and radiologically , were evaluated (age ± SD: 35 ± 11 years; height: 171 ± 8 cm; mass: 68 ± 8 kg). Patients were recruited if they were at least 18 years of age and treated at our institution (orthopedic hospital specialized in the treatment of the musculoskeletal system; core competencies include joint-preserving hip and knee surgery for mechanical malalignment and instability such as hip dysplasia and FAI). As a healthy control group, 15 sex- and age-matched adults (employees of our institution) volunteered to participate in the study (age: 34 ± 10 years; height: 173 ± 9 cm; mass: 68 ± 13 kg). For both subject groups, exclusion criteria included contraindications for ROM measurements and concomitant lower extremity injuries. All subjects provided written informed consent prior to data collection. Ethical clearance for the study was granted from the local Ethics Committee.
Subjects were tested on two occasions, one week apart, at the same time of day and at constant room temperature to establish the test-retest reliability of the goniometer and the ETS for hip ROM assessment. Concurrent (criterion-based) validity was examined by simultaneously recording the same hip ROM movement with both devices, the ETS serving as the criterion instrument . Known group construct validity was based on hip ROM recordings on both FAI patients and healthy controls, with between-group differences serving as the construct. Unilateral passive hip ROM for flexion, abduction, adduction, internal and external rotation (3 trials per movement, randomly presented) were assessed for both hips, and the initial side measured was randomized. A single investigator (SN; human movement scientist with 1 year of experience in musculoskeletal examination), blind to participants' characteristics, conducted all ROM movements. Two other co-investigators (SS, JFG; human movement scientists with 1 and 2 years of experience in musculoskeletal examination, respectively), both assisting in half of the testing sessions, were in charge of goniometric assessments (ETS values blinded). All investigators received additional training in goniometry and were instructed for reaching agreement on the method of measuring each hip movement by experienced physiotherapists and a hip orthopaedic surgeon. Up to three subjects were measured per single day, with a break of at least one hour in between.
Prior to data collection, subjects completed a standardized warm-up consisting of ergometer cycling (5 minutes at 50 W). Then, each hip ROM movement was performed twice for further warm-up and familiarization. All assessments were performed in the supine position according to Clarkson , and sets of motion on the same plane were always measured consecutively (e.g., internal then external rotation). Hip flexion was measured with the knee fully flexed, abduction-adduction with the knee and hip fully extended and internal-external rotation with the hip and knee at 90°.
One sensor was attached to the sacrum with double-sided tape and flexible medical adhesive tape (5 × 10 cm), whilst the subject was in a standing position (Figure 2B). Subjects were then asked to lay supine with their back on foamed material (40 × 25 × 8 cm) with a cut-out, allowing the sacrum sensor to move freely. The body was stabilized by a belt around the pelvis, with the intent to constrain pelvic movements during data collection. Another sensor was attached to a moldable plastic plate with plastic screws and a Velcro band was threaded through the plate and tightly wrapped around the subject's thigh, so as to minimise the movement between the sensor and the underlying skin and to maximise coupling with the underlying skeletal features [16, 22] (Figure 2C). The optimal sensor location to meet the above criteria was on the lateral side of the thigh, at mid distance between the lateral epicondyle of the femur and the greater trochanter. A third sensor was attached to the medial aspect of the knee, 2 cm proximal to the medial epicondyle of the femur (Figure 2D). The fourth sensor was embedded within a wooden calibration pointer to digitize palpated anatomical landmarks prior to data collection.
Anatomical and global calibration trials were performed with the subject in the supine position. The three-dimensional positions of several anatomical landmarks were located by sequentially placing the tip of the pointer on each landmark. Position and orientation data were subsequently sampled from both the calibration sensor and the sensor attached to the segment. Dynamic calibration trials were performed to enable the calculation of functional hip joint centers. This required the participants to perform two hip circumductions with a ROM of approximately 30° in flexion and 30° in abduction .
Data processing was performed using software written in the Matlab programming language (Mathworks Inc., Natick, USA). Functional hip joint centers, estimated using a functional approach, and digitized anatomical landmarks (medial and lateral epicondyle) were used to define the local coordinate systems of pelvis and thigh, which were then linked to the segment's individual receiver by means of coordinate transformations. For hip flexion, abduction and adduction, the sensor on the lateral aspect of the thigh was chosen as the relevant sensor to which the thigh coordinate system was related. As this sensor yielded considerably lower ROM for internal and external rotation compared to goniometry (-50% approximately), and also compared to the sensor on the medial aspect of the knee, the latter sensor served as the reference for these two motion patterns . In general, the definitions of the local coordinate system for the pelvis and thigh segment followed the recommendations of the International Society of Biomechanics . Once the orientations of the local coordinate systems for each segment were known, joint angles could be calculated using the floating axis method developed by Grood and Suntay . The following sign convention was adopted: flexion, abduction and internal rotation were positive, while movements in the opposite directions (extension, adduction and external rotation) were represented by negative values. Figure 3 (bottom) shows typical ROM traces for flexion of the involved and uninvolved hips in a FAI patient. ROM was consistently calculated as the highest value over a 1-s interval. For each movement, the mean of the three trials was used.
Data were first checked for normality and for homogeneity of variance. Paired Student t-tests were then used to detect any systematic bias between goniometer and ETS (concurrent validity) and test sessions (test-retest reliability). The Mann-Whitney U test was used to examine differences in ROM values between FAI patients and healthy controls (known group construct validity). For FAI patients, only the involved side was considered. For controls, the mean of the right and left hips was consistently used as no significant side-to-side difference was observed. Concurrent validity between the two systems was analyzed using intraclass correlation coefficients (ICC) (2,1) with their 95% confidence intervals, and Bland-Altman plots. This was done by plotting the difference between goniometer and ETS measures against their means and calculating the systematic bias ± random error, i.e., 95% limits of agreement (LOA) . As proportional bias - i.e., a significant association between the difference of the two methods and the mean values - was observed for hip flexion and internal rotation by performing the Passing-Bablok regression analysis , LOA were also calculated according to the procedure proposed by Ludbrook . This was done by constructing modified LOA lines running parallel to the predicted differences line of best fit, which can be used as an approximation of hyperbolic limits with increasing sample size . Relative reliability, the degree to which individuals maintain their position in a sample with repeated measurements, was assessed using ICC (2,1) . Absolute reliability, the degree to which repeated measurements vary for individuals, was analyzed using the coefficients of variation (CV), standard errors of measurement (SEM), and Bland-Altman plots (95% LOA) . As a general rule, an ICC value over 0.75 was considered good . In order to avoid statistical significance that might have occurred by chance, a corrected alpha level of P ≤ 0.01 was accepted as significant (Bonferroni correction).
Passive hip ROM in patients with FAI and healthy subjects using goniometer and ETS
103.8 ± 15.7
112.1 ± 11.3
84.5 ± 14.7
93.5 ± 7.8
30.4 ± 7.3
39.3 ± 7.4a
28.5 ± 6.7
37.3 ± 8.0a
23.2 ± 4.0
26.8 ± 5.7
21.5 ± 4.1
21.9 ± 3.0
Internal rotation (°)
26.0 ± 11.3
34.3 ± 10.1
24.2 ± 9.5
29.1 ± 8.5
External rotation (°)
36.3 ± 9.8
44.7 ± 4.8
29.6 ± 8.0
35.2 ± 4.2
Concurrent validity of the goniometer with the ETS for hip ROM measurement in patients with FAI and healthy subjects
-0.049 to 0.800
-18.92 ± 12.57b
0.721 to 0.978
-1.95 ± 4.70b
0.020 to 0.790
-3.32 ± 6.99b
0.495 to 0.956
-3.50 ± 7.95b
-0.087 to 0.844
-8.15 ± 8.49b
Test-retest reliability of the goniometer and ETS for hip ROM measurement in patients with FAI and healthy subjects
0.72 ± 11.15
0.27 ± 8.42
0.14 ± 6.67
-0.08 ± 5.72
-0.54 ± 6.60
1.07 ± 4.01
-0.24 ± 6.89
1.32 ± 7.90
0.02 ± 7.16
0.25 ± 5.14
This study examined whether manual goniometers (i) are sensitive enough to discriminate between individuals with and without FAI (construct validity), (ii) measure the anatomical correct hip joint ROM (concurrent validity) and (iii) produce consistent results (test-retest reliability). The major findings of this study were that goniometric measurements of passive hip motion provided greater ROM data than the criterion instrument ETS. Interestingly, the agreement between the two devices was high for hip abduction and internal rotation, but low for flexion, adduction, and external rotation. The finding that goniometers are particularly valid for measuring hip abduction was also confirmed by the comparison between FAI patients and healthy controls. Moreover, it was demonstrated that goniometric evaluation of passive hip joint angles was reliable between days, with similar reliability scores compared to the ETS. Manual goniometers can therefore be used with confidence during longitudinal assessments, which rely on repeated measurements over time.
The assessment of construct validity was performed by comparing hip ROM between FAI and healthy hips (known group validity). Considering the advanced number of FAI patients in our clinic and the quickly increasing interest for this pathology worldwide , information regarding limitation of hip ROM is needed. Due to significantly lower hip abduction ROM in the FAI group as measured with both devices, the current results demonstrated strong construct validity of manual goniometers for hip abduction assessment. The finding of lower abduction ROM in FAI patients is also supported by the literature [4, 33, 34]. For the other motion patterns, tendencies of lower ROMs in the FAI group were observed. However, the small sample size and heterogeneity in patient characteristics limit the interpretation of the present construct validity results. Comparisons to previous studies dealing with hip ROM differences between FAI and healthy hips are difficult because either no information about the measurement technique was provided [35–37] or a CT-based computer-assisted technique, ignoring cartilaginous structures, soft tissue contractures or masses for the calculation of ROM was applied . Clohisy et al.  found no ROM differences between FAI and non-symptomatic hips, whereas Philippon et al.  reported significantly reduced ROM in injured hips for all directions. Although limited internal rotation in 90° of flexion seems to be the key symptom during clinical examination [4, 35, 39, 40], the extent of restricted internal rotation still has to be ascertained as the results of this study did not reveal such a significant reduction of internal rotation in the FAI group compared to healthy controls. One possible explanation for this finding could be that in medical routine assessments, hip ROM examination is stopped before the passive limit is reached because of the groin pain that accompanies internal rotation due to sharing forces at the labrum. It is also possible that some subjects in the control group had abnormal bony anatomy, as the estimated prevalence of FAI ranges between 10 and 15% . Adequately powered studies are needed to verify which ROM movements (together with hip abduction) should be included in physical examination as an indicator of FAI.
Although all hip ROM values measured by the goniometer were significantly greater compared to the ETS, concurrent validity of manual goniometers was particularly good for hip abduction, with high ICC, and low systematic bias and random error. Subjects were positioned supine with the contralateral leg hanging down on the edge of the massage table during hip abduction assessments. Thus, the pelvis was not only stabilized by the belt, but also by the abducted contralateral limb, regardless of any other movements. In this configuration, excessive rotation of the pelvis around a vertical axis was prevented, which was not the case for hip adduction. Considering that the sacrum sensor was assumed to be rigidly attached to the pelvis and therefore representative of the pelvic coordinate system, most of the differences between the goniometer and the ETS can be attributed to this phenomenon. For motion patterns others than hip abduction, it is plausible that the difference between the goniometer and the ETS was largely due to pelvic rotation when the passive limit of motion was reached. Although the co-investigators performing the goniometer assessments tried to minimize this source of error by stabilizing the subject manually, they could not adequately correct for this misalignment. The obtained results for hip flexion are in agreement with Elson and Aspinall , who found a mean value of 85° for true hip flexion. In the same way, Bohannon et al.  stated that a large portion of the hip flexion movement is assumed to be the consequence of pelvic rotation, resulting in pure hip flexion of only 90°. Independent of the arc of motion, pelvic tilt always occurred within the first 10° of hip flexion, indicating that the thigh and pelvis move in synergy with one another. Hence, for what we usually call hip flexion, the ROM generally evaluated is thigh flexion on the trunk, which is a combination of "true" hip flexion and pelvis tilt.
Apart from the uncontrolled pelvic tilt or rotation and neutralization of lumbar lordosis (in case of hip flexion) for goniometric hip ROM assessments, there are other possible factors leading to the disagreement between the goniometer and ETS data. It is unlikely that between-device bias was attributable to differences in the physiological mechanisms underlying hip ROM testing, because measurements were performed simultaneously with the two devices. Rather, the observed discrepancies were certainly due to visual estimation of the true anatomical reference lines (e.g., the long axis of the limb) and potential alignment of the goniometer to the position of the massage table or to the laboratory arrangements, rather than to true bony orientation. Another reason for the disagreement between the goniometer and ETS is the two-dimensional characteristics of goniometric hip ROM measurements. Cheng and Pearcy  showed that an abduction angle measured in the frontal plane and a flexion angle measured in the sagittal plane can be significantly overestimated by the presence of out-of-plane movements. In the setting of this study, both hip abduction and adduction were associated to some degree of flexion, whereas hip flexion was associated to some degree of abduction. Therefore, this kind of error may have occurred, at least to a small extent.
The results obtained in the present study suggest that the hip ROMs "read" by the goniometer are in fact intersegmental thigh-trunk angles (e.g., thigh flexion on trunk for hip flexion) rather than true hip joint ROM. This study clearly demonstrates the "harmful" effect of flexing hip while evaluating ROM if pelvic tilt or rotation is not adequately controlled. Future research is needed to find hints allowing the goniometer to measure an angle close to the real ROM and to verify if other ways of goniometric estimation (e.g., hip rotations measured in prone position) would provide similar results compared to the ETS, all the more because one of the goniometer's arms could be placed on the table, potentially adding accuracy due to standardization. Even if manual goniometers are logically preferred in the clinic to more accurate devices, such as ETS, because of the limited time available for routine medical examinations, clinicians should be aware of this misinterpretation and they should try to minimize pelvic rotation. Apart from other advantages (such as simplicity of use, low cost and time saving), the use of conventional manual goniometers for longitudinal evaluations is supported by the present test-retest reliability results, which were good and comparable to those obtained with the ETS.
The excellent absolute and relative reliability estimates for hip flexion are in agreement to those reported on persons with hip osteoarthritis [1, 2, 42–44] and healthy hip subjects [5, 45]. Results from CV analyses showed that hip flexion measurements had the lowest difference between the two test days. ROM measurements of the hip abductors showed excellent test-retest reliability, with CVs around 5% and ICC estimates exceeding 0.90. A review of the literature did not identify reliability studies with comparable good CV results. Holm et al.  and Pua et al.  both reported CVs of more than 20% for passive hip ROM measurements. Even in a study assessing intra-tester within session reliability , CV was larger compared to the present between session results. The excellent reliability estimates for hip abduction are the result of adequate stabilization of the subject's body and standardized force. Of particular interest in this study was the measurement of hip adduction ROM, as information about the test-retest reliability of this movement pattern is lacking in the literature. Those authors providing information about the repeatability of hip adduction measurements reported CVs of 23% , ICCs around 0.5 [2, 43, 46], or used the Pearson correlation coefficient, which is a questionable reliability index . Although superior, the results of this study indicate that hip adduction is the most challenging movement pattern to measure, confirmed by the low ICCs (< 0.9) and the smallest arc of motion (~20°). The ICC estimates for hip internal and external rotation (~0.9) are in agreement with those previously reported on hip osteoarthritis subjects [2, 44]. In contrast, Croft et al.  reported substantially lower levels of reliability by using six raters and six participants with hip osteoarthritis. They reported inter-tester ICC values of 0.48 and 0.43 for internal and external rotation, respectively. However, because of their small sample size, the results must be interpreted with caution. The present CV values are even slightly superior to those reported in the literature [2, 5, 44]. Nevertheless, inter-study comparisons for rotational movements are difficult because of differences in the testing positions (prone compared to supine).
The current study has a few limitations. Firstly, human movement analysis based on electromagnetic tracking technology is affected by instrument errors, anatomical landmark uncertainty and skin movement artifacts . These sources of error were minimized by using a functional approach for calculating the hip joint centers and by adopting a segment coordinate system approach, which reduced anatomical landmark palpation to a minimum. However, it is still unknown if the joint coordinate system solution proposed by Grood and Suntay  represents the clinical reality. Moreover, movements were primarily performed in a single plane, so that error due to inertial effects and skin deformation by direction of movement were both negligible. The authors therefore believe the ETS can be used as the criterion instrument for hip joint ROM assessment in orthopedic research, although it is acknowledged that alternative methods such as fluoroscopy or bone-pins would be more accurate. Secondly, ETS measurements were limited to a single investigator performing the movements. Future research should include more testers in order to determine inter-tester reliability. It can be supposed that this kind of reliability would also yield excellent results for both devices, as standardization of the applied force should eliminate a considerable amount of inter-tester variability [5, 48, 49]. Finally, the investigator performing the goniometer assessments was not blinded for the goniometric ROM values. This bias was minimized by prohibiting the observer to read the goniometer results until proper alignment of the device was ensured. It is therefore unlikely that this factor influenced the main results.
This study was designed to determine the validity and reliability of manual goniometers for measuring passive hip ROM. This study is unique to the literature, and thus offers new information of clinical importance. The current findings suggest that goniometer-based assessments conventionally used in orthopedic clinical practice overestimate the majority of passive hip motion patterns by measuring intersegmental angles (e.g., thigh flexion on trunk for hip flexion) rather than true hip ROM; it is indeed difficult to reproduce true hip ROM by placing the goniometer properly and performing the anatomically correct ROM. It is likely that uncontrolled pelvic rotation and tilt contribute to the overrating of the arc of these motions. Future work is needed to find hints to perform hip ROM assessments more accurately. It is concluded that, as manual goniometers yielded good test-retest reliability estimates, they would remain the first choice tool for the assessment of hip ROM in the clinic, especially when longitudinal monitoring of hip function is aimed.
The authors wish to acknowledge the subjects for their participation in the study and Ms. Kirsten Dobson for the English revision of the manuscript.
- Arokoski MH, Haara M, Helminen HJ, Arokoski JP: Physical function in men with and without hip osteoarthritis. Arch Phys Med Rehabil. 2004, 85 (4): 574-581. 10.1016/j.apmr.2003.07.011.View ArticlePubMedGoogle Scholar
- Holm I, Bolstad B, Lutken T, Ervik A, Rokkum M, Steen H: Reliability of goniometric measurements and visual estimates of hip ROM in patients with osteoarthrosis. Physiother Res Int. 2000, 5 (4): 241-248. 10.1002/pri.204.View ArticlePubMedGoogle Scholar
- Leunig M, Beaule PE, Ganz R: The concept of femoroacetabular impingement: current status and future perspectives. Clin Orthop Relat Res. 2009, 467 (3): 616-622. 10.1007/s11999-008-0646-0.View ArticlePubMedGoogle Scholar
- Tannast M, Kubiak-Langer M, Langlotz F, Puls M, Murphy SB, Siebenrock KA: Noninvasive three-dimensional assessment of femoroacetabular impingement. J Orthop Res. 2007, 25 (1): 122-131. 10.1002/jor.20309.View ArticlePubMedGoogle Scholar
- Bierma-Zeinstra SM, Bohnen AM, Ramlal R, Ridderikhoff J, Verhaar JA, Prins A: Comparison between two devices for measuring hip joint motions. Clin Rehabil. 1998, 12 (6): 497-505. 10.1191/026921598677459668.View ArticlePubMedGoogle Scholar
- Lea RD, Gerhardt JJ: Range-of-motion measurements. J Bone Joint Surg Am. 1995, 77 (5): 784-798.PubMedGoogle Scholar
- Allard P, Stokes IAF, Blanchi J-P: Three-dimensional analysis of human movement. 1994, Champaign: Human KineticsGoogle Scholar
- Bohannon RW, Gajdosik RL, LeVeau BF: Relationship of pelvic and thigh motions during unilateral and bilateral hip flexion. Phys Ther. 1985, 65 (10): 1501-1504.PubMedGoogle Scholar
- Elson RA, Aspinall GR: Measurement of hip range of flexion-extension and straight-leg raising. Clin Orthop Relat Res. 2008, 466 (2): 281-286. 10.1007/s11999-007-0073-7.View ArticlePubMedPubMed CentralGoogle Scholar
- Johnson GR, Fyfe NC, Heward M: Ranges of movement at the shoulder complex using an electromagnetic movement sensor. Ann Rheum Dis. 1991, 50 (11): 824-827. 10.1136/ard.50.11.824.View ArticlePubMedPubMed CentralGoogle Scholar
- Jordan K, Dziedzic K, Jones PW, Ong BN, Dawes PT: The reliability of the three-dimensional FASTRAK measurement system in measuring cervical spine and shoulder range of motion in healthy subjects. Rheumatology (Oxford). 2000, 39 (4): 382-388. 10.1093/rheumatology/39.4.382.View ArticleGoogle Scholar
- Meskers CG, Vermeulen HM, de Groot JH, van Der Helm FC, Rozing PM: 3 D shoulder position measurements using a six-degree-of-freedom electromagnetic tracking device. Clin Biomech (Bristol, Avon). 1998, 13 (4-5): 280-292. 10.1016/S0268-0033(98)00095-3.View ArticleGoogle Scholar
- Amiri M, Jull G, Bullock-Saxton J: Measuring range of active cervical rotation in a position of full head flexion using the 3 D Fastrak measurement system: an intra-tester reliability study. Man Ther. 2003, 8 (3): 176-179. 10.1016/S1356-689X(03)00009-2.View ArticlePubMedGoogle Scholar
- Mannion A, Troke M: A comparison of two motion analysis devices used in the measurement of lumbar spinal mobility. Clin Biomech (Bristol, Avon). 1999, 14 (9): 612-619. 10.1016/S0268-0033(99)00017-0.View ArticleGoogle Scholar
- Laprade J, Lee R: Real-time measurement of patellofemoral kinematics in asymptomatic subjects. Knee. 2005, 12 (1): 63-72. 10.1016/j.knee.2004.02.004.View ArticlePubMedGoogle Scholar
- Mills PM, Morrison S, Lloyd DG, Barrett RS: Repeatability of 3 D gait kinematics obtained from an electromagnetic tracking system during treadmill locomotion. J Biomech. 2007, 40 (7): 1504-1511. 10.1016/j.jbiomech.2006.06.017.View ArticlePubMedGoogle Scholar
- Jordan K, Dziedzic K, Mullis R, Dawes PT, Jones PW: The development of three-dimensional range of motion measurement systems for clinical practice. Rheumatology (Oxford). 2001, 40 (10): 1081-1084. 10.1093/rheumatology/40.10.1081.View ArticleGoogle Scholar
- Jasiewicz JM, Treleaven J, Condie P, Jull G: Wireless orientation sensors: their suitability to measure head movement for neck pain assessment. Man Ther. 2007, 12 (4): 380-385. 10.1016/j.math.2006.07.005.View ArticlePubMedGoogle Scholar
- Johnson MP, McClure PW, Karduna AR: Use of a digital inclinometer to assess scapular upward rotation: A reliability and validity study. Proceedings of the 23rd Annual Meeting of the American Society of Biomechanics, Pittsburgh, PA. 1999, 56-57.Google Scholar
- Menadue C, Raymond J, Kilbreath SL, Refshauge KM, Adams R: Reliability of two goniometric methods of measuring active inversion and eversion range of motion at the ankle. BMC Musculoskelet Disord. 2006, 7: 60-10.1186/1471-2474-7-60.View ArticlePubMedPubMed CentralGoogle Scholar
- Clarkson HM: Musculoskeletal Assessment: Joint Range of Motion and Manual Muscle Strength. 2000, Baltimore: Lippincott Williams & WilkinsGoogle Scholar
- Lee RY, Wong TK: Relationship between the movements of the lumbar spine and hip. Hum Mov Sci. 2002, 21 (4): 481-494. 10.1016/S0167-9457(02)00117-3.View ArticlePubMedGoogle Scholar
- Piazza SJ, Okita N, Cavanagh PR: Accuracy of the functional method of hip joint center location: effects of limited motion and varied implementation. J Biomech. 2001, 34 (7): 967-973. 10.1016/S0021-9290(01)00052-5.View ArticlePubMedGoogle Scholar
- Wren TA, Do KP, Hara R, Rethlefsen SA: Use of a patella marker to improve tracking of dynamic hip rotation range of motion. Gait Posture. 2008, 27 (3): 530-534. 10.1016/j.gaitpost.2007.07.006.View ArticlePubMedGoogle Scholar
- Wu G, Cavanagh PR: ISB recommendations for standardization in the reporting of kinematic data. J Biomech. 1995, 28 (10): 1257-1261. 10.1016/0021-9290(95)00017-C.View ArticlePubMedGoogle Scholar
- Grood ES, Suntay WJ: A joint coordinate system for the clinical description of three-dimensional motions: application to the knee. J Biomech Eng. 1983, 105 (2): 136-144. 10.1115/1.3138397.View ArticlePubMedGoogle Scholar
- Bland JM, Altman DG: Statistical methods for assessing agreement between two methods of clinical measurement. Lancet. 1986, 1 (8476): 307-310.View ArticlePubMedGoogle Scholar
- Passing H, Bablok : A new biometrical procedure for testing the equality of measurements from two different analytical methods. Application of linear regression procedures for method comparison studies in clinical chemistry, Part I. J Clin Chem Clin Biochem. 1983, 21 (11): 709-720.PubMedGoogle Scholar
- Ludbrook J: Confidence in Altman-Bland plots: a critical review of the method of differences. Clin Exp Pharmacol Physiol. 2010, 37 (2): 143-149. 10.1111/j.1440-1681.2009.05288.x.View ArticlePubMedGoogle Scholar
- Armitage PP, Berry G, Matthews JNS: Statistical Methods in Medical Research. 2002, Oxford: Blackwell Science, 4View ArticleGoogle Scholar
- Atkinson G, Nevill AM: Statistical methods for assessing measurement error (reliability) in variables relevant to sports medicine. Sports Med. 1998, 26 (4): 217-238. 10.2165/00007256-199826040-00002.View ArticlePubMedGoogle Scholar
- Kramer MS, Feinstein AR: Clinical biostatistics. LIV. The biostatistics of concordance. Clin Pharmacol Ther. 1981, 29 (1): 111-123. 10.1038/clpt.1981.18.View ArticlePubMedGoogle Scholar
- Kubiak-Langer M, Tannast M, Murphy SB, Siebenrock KA, Langlotz F: Range of motion in anterior femoroacetabular impingement. Clin Orthop Relat Res. 2007, 458: 117-124.PubMedGoogle Scholar
- Philippon MJ, Maxwell RB, Johnston TL, Schenker M, Briggs KK: Clinical presentation of femoroacetabular impingement. Knee Surg Sports Traumatol Arthrosc. 2007, 15 (8): 1041-1047. 10.1007/s00167-007-0348-2.View ArticlePubMedGoogle Scholar
- Jäger M, Wild A, Westhoff B, Krauspe R: Femoroacetabular impingement caused by a femoral osseous head-neck bump deformity: clinical, radiological, and experimental results. J Orthop Sci. 2004, 9 (3): 256-263. 10.1007/s00776-004-0770-y.View ArticlePubMedGoogle Scholar
- Leunig M, Podeszwa D, Beck M, Werlen S, Ganz R: Magnetic resonance arthrography of labral disorders in hips with dysplasia and impingement. Clin Orthop Relat Res. 2004, 74-80. 10.1097/00003086-200401000-00013. 418Google Scholar
- Strehl A, Ganz R: [Anterior femoroacetabular impingement after healed femoral neck fractures]. Unfallchirurg. 2005, 108 (4): 263-273. 10.1007/s00113-004-0886-8.View ArticlePubMedGoogle Scholar
- Clohisy JC, Knaus ER, Hunt DM, Lesher JM, Harris-Hayes M, Prather H: Clinical presentation of patients with symptomatic anterior hip impingement. Clin Orthop Relat Res. 2009, 467 (3): 638-644. 10.1007/s11999-008-0680-y.View ArticlePubMedPubMed CentralGoogle Scholar
- Ganz R, Parvizi J, Beck M, Leunig M, Notzli H, Siebenrock KA: Femoroacetabular impingement: a cause for osteoarthritis of the hip. Clin Orthop Relat Res. 2003, 112-120. 417Google Scholar
- Leunig M, Beck M, Dora C, Ganz R: [Femoroacetabular impingement: trigger for the development of coxarthrosis]. Orthopade. 2006, 35 (1): 77-84. 10.1007/s00132-005-0896-4.View ArticlePubMedGoogle Scholar
- Cheng PL, Pearcy M: A three-dimensional definition for the flexion/extension and abduction/adduction angles. Med Biol Eng Comput. 1999, 37 (4): 440-444. 10.1007/BF02513327.View ArticlePubMedGoogle Scholar
- Croft PR, Nahit ES, Macfarlane GJ, Silman AJ: Interobserver reliability in measuring flexion, internal rotation, and external rotation of the hip using a plurimeter. Ann Rheum Dis. 1996, 55 (5): 320-323. 10.1136/ard.55.5.320.View ArticlePubMedPubMed CentralGoogle Scholar
- Klassbo M, Harms-Ringdahl K, Larsson G: Examination of passive ROM and capsular patterns in the hip. Physiother Res Int. 2003, 8 (1): 1-12. 10.1002/pri.267.View ArticlePubMedGoogle Scholar
- Pua YH, Wrigley TV, Cowan SM, Bennell KL: Intrarater test-retest reliability of hip range of motion and hip muscle strength measurements in persons with hip osteoarthritis. Arch Phys Med Rehabil. 2008, 89 (6): 1146-1154. 10.1016/j.apmr.2007.10.028.View ArticlePubMedGoogle Scholar
- Ekstrand J, Wiktorsson M, Oberg B, Gillquist J: Lower extremity goniometric measurements: a study to determine their reliability. Arch Phys Med Rehabil. 1982, 63 (4): 171-175.PubMedGoogle Scholar
- Chevillotte CJ, Ali MH, Trousdale RT, Pagnano MW: Variability in Hip Range of Motion on Clinical Examination. J Arthroplasty. 2008Google Scholar
- Della Croce U, Cappozzo A, Kerrigan DC, Lucchetti L: Bone position and orientation errors: pelvis and lower limb anatomical landmark identification reliability. Gait and Posture. 1997, 5 (2): 156-157. 10.1016/S0966-6362(97)83382-6.View ArticleGoogle Scholar
- Gajdosik RL, Bohannon RW: Clinical measurement of range of motion. Review of goniometry emphasizing reliability and validity. Phys Ther. 1987, 67 (12): 1867-1872.PubMedGoogle Scholar
- Reichenbach S, Juni P, Nuesch E, Frey F, Ganz R, Leunig M: An examination chair to measure internal rotation of the hip in routine settings: a validation study. Osteoarthritis Cartilage. 2009Google Scholar
- The pre-publication history for this paper can be accessed here:http://www.biomedcentral.com/1471-2474/11/194/prepub
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