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Gait patterns after anterior cruciate ligament reconstruction

1997, Knee Surgery, Sports Traumatology, Arthroscopy

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The study investigates changes in gait parameters following anterior cruciate ligament (ACL) reconstruction using the bone-patellar tendon-bone technique. Data was collected from 15 subjects post-reconstruction, focusing on kinematic, kinetic, and electromyographic parameters. Results indicate that after surgery, gait patterns in the reconstructed subjects show significant normalization compared to untreated and healthy control groups, particularly regarding knee joint angles, joint moments, and muscle activation patterns.

Knee Surg, Sports Traumatol, Arthroscopy (1997) 5 : 14–21 KNEE © Springer-Verlag 1997 P. Bulgheroni M. V. Bulgheroni L. Andrini P. Guffanti A. Giughello Received: 13 May 1996 Accepted: 28 November 1996 P. Bulgheroni (Y) · M. V. Bulgheroni · L. Andrini · P. Guffanti · A. Giughello Clinica Ortopedica e Traumatologica “M. Boni”, Università degli Studi di Pavia – Varese, Ospedale F. Del Ponte, Via F. Del Ponte, I-21100 Varese, Italy Tel.: (39) 332–28 26 82 Fax: (39) 332–28 89 56 Gait patterns after anterior cruciate ligament reconstruction Abstract The aim of this study is to analyse the changes in select gait parameters following anterior cruciate ligament (ACL) reconstruction. The study was performed on 15 subjects who underwent ACL reconstruction by the bone-patellar tendon-bone technique. Gait analysis was performed using the Elite three-dimensional (3D) optoelectronic system (BTS), a Kistler force platform and the Telemg telemetric electromyograph (BTS). Kinematic data were recorded for the principal lower limb joints (hip, knee and ankle). The examined muscles include vastus lateralis, rectus femoris, biceps femoris and semitendinosus. The results obtained from the operated subjects were compared with those of 10 untreated subjects and 5 subjects without ACL damage. In the operated subjects the knee joint angular values Introduction Changes in the gait patterns of subjects with anterior cruciate ligament (ACL) injury have been assessed in a number of studies, all using different techniques; however, few studies have evaluated the changes in gait parameters following ACL reconstruction. Timoney et al. [32] examined the gait patterns of 10 normal and 10-ACL reconstructed (bone-patellar tendon-bone technique) subjects considering only kinetic data. Comparing these results to those of Andriacchi [1, 2, 8], it appears that ACL-reconstructed subjects show a behaviour closer to normal values than do untreated subjects. regained a normal flexion pattern for the injured limb during the stance phase. The analysis of joint moments shows: (a) sagittal plane: recovery of the knee flexion moment at loading response and during preswing; (b) frontal plane: recovery of the normal patterns for both hip and knee adduction-abduction moments during the entire stance phase. The examination of ground reaction forces reveals the recovery of frontal component features. The EMG traces show the normal biphasic pattern for the operated subjects as compared to the untreated subjects. The results suggest that the gait parameters shift towards normal value patterns. Key words Gait analysis · Anterior cruciate ligament reconstruction · 3D kinematics · Kinetics · Electromyography Ciccotti et al. [12, 13] analysed the electromyographic (EMG) patterns during gait in three groups: (a) normal subjects, (b) ACL-deficient subjects undergoing rehabilitation and (c) ACL-reconstructed subjects (bone-patellar tendon-bone technique). ACL-reconstructed subjects showed EMG patterns very close to normal values, whereas subjects undergoing rehabilitation demonstrated abnormal EMG activity. This study used a comprehensive approach (including kinematic, kinetic and EMG data analysis) for the measurement of changes in the dynamic equilibrium during gait following ACL injury and their modification following ACL reconstruction. 15 Patients and methods The study was carried out with a group of 10 male subjects with ACL injury (age 27 ± 6 SD years), a different group of 15 male ACL-reconstructed subjects (bone-patellar tendon-bone technique) (age 25 ± 3 years) and 5 normal male subjects with no history of musculoskeletal pathology (age 28 ± 3 years). The data collected for the normal group concorded with previously published results [12, 18, 19, 28]. The ACL-deficient group was examined on average 20.4 months after injury (range 8–48 months); all the subjects complained of knee instability and showed positive anterior drawer, Lachman and pivot shift tests with no associated ligament injury upon clinical examination. The mean KT-2000 arthrometer differences in excursion between knees were 3.7 ± 2.1 mm at 20 lb and 6.7 ± 3.24 mm at manual maximum. The ACL injury was always confirmed during subsequent surgical intervention. The ACL-reconstructed subjects were examined 17 ± 5 months after the surgical intervention. All of them had resumed their normal activity, and there was no clinical evidence of instability. The mean KT-2000 arthrometer differences in excursion between knees were 1.77 ± 1.00 mm at 20 lb and 2.27 ± 1.29 mm at manual maximum. Each subject was asked to perform at least 5 trials of walking at his natural cadence (112 ± 5.1 steps/min). A 20-m distance was used to allow the subject to reach a steady state of walking. The analysis of gait features was performed using an ELITE system (BTS, Milan, Italy) composed of the following: (a) four TV cameras for the recording of the kinematic data; (b) a force plate (Kistler, Winterthur, Switzerland) for the acquisition of ground reaction forces; and (c) a telemetric EMG system (BTS, Milan, Italy) equipped with surface electrodes for the recording of neuromuscular activity. Both ground reaction forces and EMG signals were ac- quired at a sampling rate of 500 Hz, whereas the four TV cameras worked at a sampling rate of 100 Hz. Further elaboration of all the variables was carried out by computer. Reflective passive markers (n = 22) were positioned over specific anatomical points of both lower limbs, pelvis and trunk (Fig. 1). The data obtained from the camera recording of these markers allowed the reconstruction of internal points (centre of rotation of hip, knee and ankle joints) and segmentally embedded coordinate systems according to the model described by Davis [14]. For all trials, the joint angles were computed according to the protocol defined by Davis [14]. For the external moments, consideration was given to both the reaction force trend and the inertial parameters of each body segment. The data were normalized (both time and amplitude) prior to the calculation of the averaged values. EMG activity of vastus lateralis, rectus femoris, biceps femoris (lateral hamstrings) and semitendinosus (medial hamstrings) muscles was recorded bilaterally. Prior to acquisition, the electrode positions were tested to control for crosstalk between different muscle groups. The raw data were highpass filtered to eliminate frequency components below 10 Hz, then rectified and filtered to eliminate the components of the signal over 200 Hz. Before calculating the average values, all EMG measurements were subject to normalization procedures. A single gait cycle (complete stride) was identified, and all the corresponding data sets were then reduced to 100 points. Individual subject data relating to (a) the amplitude of force were normalized to subject weight, (b) the amplitude of joint moment were normalized to the subject’s weight and height, and (c) the EMG were normalized to the maximum recorded signal amplitude during a single walking cycle [28]. Three different groups were defined: (a) ACL-deficient subjects, (b) ACL-reconstructed subjects and (c) control subjects. The average trend for all variables was computed for each group. Student-Neuman-Keuls tests were adopted to determine levels of significance when comparing the groups. The tests were applied to all variables and for each stride bin. Results Fig. 1 Positioning of the markers, as viewed from the front and from the back (BTS, Milan, Italy). Analysis of the frame-by-frame data recorded from these markers during the gait cycle allows the determination of (a) the centre of rotation for each joint examined and (b) orientation of the coordinate systems identifying the body segments With respect to joint angles (Figs. 2–4), the injured subjects showed changes as a consequence of the ACL injury mainly at the hip and knee joints. During all phases of the gait cycle, both of these joints demonstrated reduced excursions. However, the functional pattern of the flexionextension angle was maintained. In contrast, hip, knee and ankle angular values of the ACL reconstructed group showed behaviour similar to the normal control subjects. Analysis of the external joint moments (Figs. 5–7) also indicated that the hip and knee joints were most affected by the injury. At heel strike the knee joint revealed a greater extension moment in the ACL-deficient subjects (Fig. 5; P < 0.05). During the loading response phase, a reduction of the knee flexion moment was compensated for by an increased flexion moment at the hip joint (P < 0.05). The joint also tended to show a reduced flexion moment during the preswing phase, but our data did not achieve statistical significance. Both the knee and the hip indicated a decreased adduction moment during the entire stance phase (Fig. 6; P < 0.05). However, the internal and external rotation moments did not appear to be affected by the injury.