Loading conditions in the spine, hip and knee during different executions of back extension exercises

Background

Back extension (BE) is a strength exercise for training the dorsal trunk and hip muscles. To optimise training recommendations that avoid overloading and possible injury, the aim of this study was to determine the loading conditions and the influence of different execution forms of BE on spine, hip and knee ranges of motion (RoMs), joint moments and muscle activity.

Methods

The kinematics, kinetics and muscle activity (EMG) of two execution types (BE_h: dynamic hip, BE_s: dynamic spine) and two versions (one-legged and two-legged) of BE were measured in 16 subjects. RoMs and external joint moments were calculated using an inverse dynamics approach and analysed with a linear mixed model.

Results

Although lumbar spine flexion was observed in both execution types, thoracic spine flexion predominantly occurred during BE_s, whereas thoracic spine extension was observed during BE_h. Larger maximal back and hip moments were observed for BE_h than for BE_s. The activity of the dorsal back and hip muscles, as observed using EMG, was increased for one-legged executions.

Conclusion

To strengthen the hips and lower back, BE_h seem to be more efficient due to the higher moments, with higher or similar RoMs in the hip and lower back. One-legged BE_s seem to provide an effective training for the hamstrings and hip regions without subjecting the spine to excessive loading, possibly promoting this as an effective exercise during training and rehabilitation.

Strength exercises are part of most training and rehabilitation programs. The back extension (BE) is often performed by athletes as well as low back pain patients to strengthen the dorsal trunk and hip musculature [1]. Because a majority of injuries during strength training occur due to the overloading and incorrect execution of the exercises [2], biomechanical knowledge of the loading conditions that occur during BE exercises, especially in the hip and knee joints and in the lower back, is important to provide safe and efficient recommendations for training and rehabilitation.

Two dynamic types of BE are commonly used: the activity can be predominantly driven either by movement at the hip while the spine is stabilised (BE_h) or by movement at the spine executed with a stabilised hip (BE_s). In addition, one- and two-legged versions are also possible and frequently used. Historically, the execution of BE_s has been based on the Sorensen test, which was developed to assess the isometric endurance of the dorsal trunk muscles [3, 4]. During this test, subjects lie on a table with their held legs horizontal to the ground and attempt to hold their unsupported upper body stable for as long as possible. In a more recent development of the exercise, instead of a horizontal table, a variable-angle Roman chair is used, which allows the legs to be placed at an angle to the horizontal of, e.g., 45° [1, 5–8], and thereby allows the highest loading conditions (i.e., when the upper body is horizontal) to act at different hip flexion angles [9]. This idea has been supported by electromyography (EMG) measurements that demonstrated changes in lumbar muscle activity resulting from different starting postures and the associated changes in muscle lengths [10]. In addition, higher endurance of the lumbar dorsal trunk muscles has been observed when BE was performed on a variable-angle Roman chair compared to the horizontal Sorensen set-up [5]. These authors assumed that the contribution of the passive structures, mainly the thoraco-lumbar fascia, was greater due to the increased stretch of the hip extensors in the variable-angle Roman chair set-up and that less lumbar muscle effort was thus required to support the mass of the upper body.

Many studies have investigated the muscle recruitment of trunk and hip muscles in different forms of BE exercises. Direct comparisons between these studies should be considered with caution because the test protocols and analyses were different. Lumbar and thoracic trunk muscles were highly activated during BE without additional loading (39–56 and 43% maximum voluntary contraction (MVC) on a 40° Roman chair) and similar between different execution forms. Gluteal and hamstring activities can be slightly increased using a more horizontal BE execution (40° Roman chair: 15–23%, 12–16% MVC, respectively; horizontal position: 22–23 and 16-24% MVC, respectively) [1, 11].

Changing the kinematic parameters during BE lead to different activation levels and different spine postures (e.g., +18% activation level for lumbar extensors with an accentuated lumbar lordosis of +25% by performing BE with an internal rotated hip) [8]. Therefore, different loading conditions act on the spine with different execution forms and lead to different risks of injury because disk deformation and ligament and spinal loading can be reduced if BE exercises are performed with neutral lordosis [11].

Distinct recommendations are missing in the literature and controversially discussed, such as for the specific strengthening of the lumbar trunk muscles relative to hip extensors. Whereas Da Silva and co-workers [1] stated that a 40° Roman chair reduced the activity of the biceps femoris but did not alter the activity of the lumbar back extensors compared to a horizontal position, Mayer and co-workers [9] found that the lumbar back extensors were more active in a more horizontal position. Furthermore, Larivière and co-workers [7] stated that the 40° condition was not well suited to specifically fatigue the dorsal back muscles relative to the dorsal hip muscles. Moreover, increased external load or several sets of exercises could increase the muscle activity of the hip extensors to a higher degree than that of the lumbar back extensors and therefore more specifically train the dorsal hip muscles [12]. In contrast, with an external load of 60% of 1RM, De Ridder and co-workers [13] stated that the gluteal muscles played a smaller role compared to the lumbar muscles. Regarding the breathing pattern during strength training, the National Strength and Conditioning Association recommends to instruct athletes to exhale through the sticking point and to inhale during the less stressful phase of the repetition [14].

A detailed biomechanical analysis of the movement, loading patterns and muscle activities of the BE exercise including trunk, hip and knee joints, is missing. However, as stated above, to avoid injuries and derive training recommendations, knowledge of the loading conditions is fundamental.

Therefore, the aim of this study was to determine the influence of different execution forms of BE exercises on the spine, hip and knee ranges of motion (RoMs) and the corresponding external joint moments as well as muscle activities. The different execution forms include single or double legged execution, performed either using an isometric hip and a dynamic spine or using a dynamic hip and an isometric spine.

Participants

Sixteen subjects (8male, 8female, age 26.3 ± 4.2 years, body mass 71.9 ± 15.1 kg, height 1.76 ± 0.09 m) were evaluated and provided written informed consent to participate in this study. They were required to have personal experience in strength training, be physically active at least three hours per week and have neither past surgery on back, hip or knee nor any current injuries or illnesses. All subjects were instructed to wear normal sports shoes and shorts, and female subjects additionally wore a bikini top. The study was approved by the ethics committee of ETH Zurich, Switzerland (EK 2014-N-31).

Data acquisition

To analyse the kinematic motion of the body, 21 cameras (MX40 and MX160) of an opto-electronic motion system (Vicon, Oxford Metrics Group, Oxford, UK) operating at a sampling frequency of 100 Hz were used. 77 reflective markers were placed onto the subjects according to the method described by List and co-workers [15]. The markers were attached to the upper and lower extremities, the pelvis, and the trunk using double-sided, skin-friendly tape. The markers on the feet and spine had a diameter of 9 mm, whereas the markers on the other segments had a diameter of 14 mm. To functionally determine the joint centres of the ankle, knee and hip joints, the subjects performed standardised basic motion tasks [15].

The ground reaction forces were measured using two 40 × 60 cm² force plates (type 9281B Kistler Instrumente AG, Winterthur, Switzerland) operating at 2 kHz. The specially constructed BE bench consisting of two mechanically decoupled parts was mounted onto these force plates (Fig. 1). The frontal part was adjusted in height such that the subject’s hip joint centre was just above the edge of the bench. Moreover, the force plates were specifically calibrated to correct the centre of pressure [16].

Measurement Setup: Back Extension (BE) exercises on a 45° BE bench: a: subject, b: opto-electronic motion cameras, c: two decoupled force plates, d: reflective markers, e: EMG sensors, f: video camera

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To record muscle activities, surface EMG was used. 16 EMG sensors (Trigno^™ Wireless EMG System, Delsys, USA) operating at a frequency of 2 kHz were placed bilaterally onto the following muscle bellies [17]: M. gluteus maximus (GlutMax), M. gluteus medius (GlutMed), lateral hamstrings (HamLat), medial hamstrings (HamMed), lumbar part of M. erector spinae (ErecLum), thoracic part of M. erector spinae (ErecThor), M. rectus abdominis (Abdo) and M. obliquus externus abdominis (Obli). After a five-minute general warm-up, the subjects performed standardised MVC tasks [18]. Directly thereafter, the subjects received standardised instructions (Table 1) and performed randomized the following types of BE:

• BE_h: Dynamic flexion and extension of the hip while the spine is stabilised in its neutral position.

• BE_s: Dynamic flexion and extension of the spine (vertebrae by vertebrae) while the hip is stabilised in its neutral position.

These two types were each executed two-legged (2L) and one-legged (1L, left and right). To allow proper averaging, eight repetitions of each execution form were performed, for a total of 48 repetitions per subject. Between each execution form, there was a break of at least 90 seconds. Because there was no additional loading, this test protocol was expected to be in a submaximal range for BE for all participants.

Data processing & analysis

The kinetic and kinematic data were reconstructed in Vicon Nexus (version 1.8, Oxford Metrics Group, UK), and any further calculations were conducted with Matlab (version 8.3, The MathWorks Inc., Natick, MA, USA).

The joint centres of ankle, knee and hip were determined functionally using the data from the basic motion tasks [15], whereas the joint centre of L4/L5 was defined anatomically based on anthropometric data [19]. The highest value (peak) reached by the middle point between the shoulder markers and its corresponding time point defined the starting and ending point of each repetition. If there was more than one peak between two repetitions, the first peak was taken as the ending point of the former repetition, and the last peak was taken as the starting point of the following repetition. For the first and last repetitions to be included, the height of the shoulder markers had to lie within 10% of the following or the previous repetition, respectively. The repetitions were time-normalised according to the defined starting and ending points.

The joint moments in the knee, hip and back (L4/L5) were calculated using a quasistatic inverse dynamic approach [20] that considered the joint centres, the ground reaction forces [21] and the gender-specific different segment masses [22]. The resulting joint moments were normalised to the subject’s body mass. Joint angles were based on a least squares fit of redundant skin marker clouds [23] and a helical axis approach [24], and the orthogonal anatomically defined joint coordinate systems [15] were defined. The RoMs for the hip, knee and different parts of the back were calculated, as were the lumbar and thoracic spine curvature and range of curvature [15].

The means and standard deviations over all 8 repetitions of a particular execution form and all subjects were calculated for the RoMs [°] of the middle to upper back (RoM_mub), lower to middle back (RoM_lmb), pelvis to lower back (RoM_plb), hip (RoM_h) and knee (RoM_k). For the lumbar and thoracic curvature [1/m], the starting (C_l,s, C_t,s) and reversal points (C_l,rp, C_t,rp) of the movement and the maximal joint moments [Nm/kg] of back at L4/L5 (M_b,max), hip (M_h,max) and knee (M_k,max) were calculated. Positive values corresponded to flexion angles, and positive moments corresponded to external flexion moments.

EMG data processing involved zero compensation, rectification, a third-order Butterworth (10-500 Hz) and a moving average filter (49 frames) [adapted from: [25]. The following parameters were chosen as the threshold: (20% of the maximal peak), threshold for the on/off-pattern (10% MVC), minimal sub period duration “on” (25 ms) and minimal sub period duration “off” (13 ms). Muscles reaching values higher than three times the MVC for a specific trial were excluded from that trial. The means of the processed EMG signals over all cycles of each subject were then calculated separately for the concentric and eccentric phase of each muscle (mean curve parameters). Furthermore, a Fast-Fourier-Transformation (FFT) was performed to calculate the median frequency both for each repetition and for the whole trial. To evaluate fatigue during each trial and during the whole session, the mean frequency of the first repetition or trial was set to zero, and the deviation of the median frequency of each repetition or trial from this initial value was calculated.

Statistical analysis

All statistical analyses were conducted using IBM SPSS Statistics (version 22, SPSS AG, Zurich, Switzerland). The normal distribution was visually evaluated using Q-Q-Plots and tested with Kolmogorov-Smirnov-Tests for each parameter. A linear mixed model (significance: p < 0.05) was used for statistical analysis. Significant differences of all parameters between BE_h and BE_s and among 1L and 2L within BE_h and BE_s were examined and adjusted using Bonferroni correction within each statistical test.

In general, no differences between left and right 1L were found. Therefore, they were analysed together. Additionally, the FFT analysis did not show any fatigue between the different trials, which indicated that the breaks were sufficiently long to fully recover between the different execution types. The kinematic and kinetic results for back, hip and knee and the muscular activities are presented below.

Back

Kinematics

For all RoMs (back, hip and knee), significant differences between BE_h and BE_s were found. Whereas higher RoMs for BE_s acted in the middle and upper back, higher values were found in the lower back during BE_h compared to BE_s. (Tables 2 and 3).

The RoM of C_l was comparable for BE_h and BE_s (Fig. 2c and Tables 2). The curvature in the thoracic region (C_t) proceeded differently between BE_h and BE_s during a cycle, which led to significant different starting and reversal points of C_t (Fig. 2d, Tables 2 and 3). Moreover, for BE_s, C_t,s was larger for 2L compared to 1L.

Loading conditions: Moments (positive for external flexion moment) as a function of joint angle averaged over all repetitions and all subject plots are plotted for all BE exercise types (solid: BE_h, dashed: BE_s; blue: 2L, green: 1L; *: starting point) (a): Normalised knee moment in the sagittal plane [Nm/kg] as a function of the corresponding knee flexion angle [°]. b: Normalised hip moment in the sagittal plane [Nm/kg] as a function of the corresponding hip flexion angle [°]. c: Normalised back moment at the level L4/L5 in the sagittal plane [Nm/kg] as a function of the corresponding lumbar curvature [1/m]. d: Normalised thoracic curvature in the sagittal plane [1/m] for a cycle [%]

Full size image

Kinetics

M_b,max was 0.1 Nm/kg greater for BE_h than for BE_s for all versions and occurred at the reversal point (Fig. 2c, Tables 2 and 3).

Hip

Kinematics

RoM_h was twice as high for BE_h than for BE_s for all versions. Additionally, a shifted starting point for 1L executions could be identified, which led to a smaller RoM_h for 1L compared to 2L during BE_h (Fig. 2b; Tables 2 and 3).

Kinetics

For all versions, M_h,max was approximately 0.2 Nm/kg higher for BE_h than for BE_s; for both types, it was approximately 0.3 Nm/kg higher for 1L compared to 2L. M_h,max occurred at the reversal point for all execution forms (Fig. 2b, Tables 2 and 3).

Knee

Kinematics

The participants fully extended their knees during BE_h, whereas during BE_s, they kept their knees in a slightly bent position. This difference techniques resulted in a greater RoM_k for BE_h. The 1L executions already started with more extended legs compared to 2L, which caused a higher RoM_k for 2L executions during BE_h (Fig. 2a, Tables 2 and 3).

Kinetics

M_k,max occurred at the reversal point and was more than 0.1 Nm/kg higher for BE_h than BE_s for all versions and higher for 1L than for 2L for both types (Fig. 2a, Tables 2 and 3).

Muscular activity

Eccentric phase

GlutMax and GlutMed showed higher activities for the trained leg of 1L executions compared to 2L executions for both types of BE. HamLat was more active for BE_s than BE_h for 2L. HamMed for BE_h and ErecLum For BE_s were more active for 1L than 2L, whereas ErecThor showed a higher activity for BE_h compared to BE_s. Abdo and Obli were more active for BE_s than BE_h, however, the activity level for these muscles was very low (Tables 4 and 5).

Concentric phase

Similarly, GlutMax, GlutMed and ErecLum showed higher activities for the trained leg of 1L compared to 2L. HamLat was more active in BE_h during 1L execution, whereas ErecThor showed a higher activity for BE_h compared to BE_s for all types (Tables 4 and 5).

The aim of this study was to study the influence of different BE execution forms on the spine, hip and knee RoMs, external joint moments and on the muscle activity. In total, 16 subjects performing six different versions of BE were measured and analysed.

Back

Kinematics

Due to the different exercise specifications, higher RoM_mub, RoM_lmb and C_t,rp and smaller RoM_plb were expected for BE_s compared to BE_h and could be analysed (Tables 2 and 3). It is remarkable that a similar lumbar spine flexion was found for BE_h compared to BE_s. However, whereas a thoracic spine flexion was analysed during BE_s, a spine extension was observed during BE_h from the starting to the reversal point (Fig. 2c and d). This difference resulted in an opposed movement for the dorsal spine muscles in BE_h. This opposed movement in the spine during the eccentric part of BE_h might affect the dorsal back muscles. ErecLum becomes stretched and experiences an eccentric force, whereas ErecThor contracts in a concentric manner.

The RoMs in the lumbar and thoracic spine of non-fatigued BE reported by Larivière and co-workers [7] were within the values of BE_h and BE_s of this study. This finding supports the assumption based on the FFT analysis of the EMG data that the BE in the present study were performed in a non-fatigued state. With fatigue, Larivière and co-workers [7] observed RoMs in the lumbar spine that were closer to those of this study’s BE_h, whereas the values of the RoMs in the thoracic spine were closer to those of the BE_s (Table 2). Although the participants tried to start in the exact same position for all execution forms, the significant differences in C_t,s, especially between BE_h and BE_s, indicated that this was not entirely the case (Tables 2 and 3). Although BE_s involved an isolated spine flexion and BE_h a stabilised spine, the RoM in C_l seemed to be comparable between BE_h and BE_s, which indicates that it was not possible to completely isolate one movement.

Kinetics

BE_h resulted in a slightly higher M_b,max (Fig. 2c, Tables 2 and 3). A higher moment in the back is assumed with a greater exerted strain on the lumbar back muscles, which probably led to a larger training effect on those specific muscles. This difference could be explained by a bigger lever arm of the segmental mass of the upper body in BE_h. For comparison, the back moments estimated for L5/S1 by Plamondon and co-workers [26] were normalised with a mean body weight (BW, 1.42 Nm/kg). The smaller values for L4/L5 (0.94-1.05 Nm/kg) found in this study can be argued as followed. First, a less horizontal leg position causes a smaller external torque [6] and second, a smaller lever arm due to L4/L5 being more cranial compared to L5/S1 is presented. Furthermore, Plamondon and co-workers [26] described that the maximal back moment occurred at or near a horizontal trunk position, which agrees with this study's M_b,max occurring at the reversal point along with the smallest C_l (Fig. 2c).

Comparing found back moments to other back strength exercises, such as deadlifts and goodmornings, the maximal moment in the back, M_b,max, is two to three times smaller during BE [maximal back moment = 2.75–2.81 Nm/kg with 25% extra barbell load for deadlifts and goodmornings; 27].

Hip

Kinematics

Because of different exercise specifications, RoM_h was expected to be higher for BE_h compared to BE_s. This assumption was confirmed by the results (Fig. 2b, Tables 2 and 3). Larivière and co-workers [7] achieved a RoM_h of 13°, which was in accordance with this study’s BE_s values. The smaller RoM_h for 1L compared to 2L (Fig. 2b) could be explained by the inability of the participants to fully extend their hip in the starting position of 1L executions due to a lack of stabilising capacity.

Kinetics

Similar to the kinetic results in the lower back, the maximal moment in the hip, M_h,max, was slightly higher for BE_h compared to BE_s (Fig. 2b, Tables 2 and 3), which presumably resulted in a higher training effect for the dorsal hip muscles during BE_h. Additionally, a significantly higher M_h,max and, thus, probably a better training effect were achieved for 1L compared to 2L for both types of BE (Fig. 2b, Tables 2 and 3).

Comparing to other strength exercises, M_h,max during 2L BE was similar to squats without any extra load [27, 28] and was approximately half for 2L and two thirds for 1L of the load reached by deadlifts and goodmornings with 25% BW extra barbell load [29]. The latter is quite astonishing, considering that the BE were performed without any extra load. For comparison with this study's results, the maximal hip moment for 45° BE calculated by Contreras and co-workers [6] was normalised with BW (5.43 Nm/kg). Because they used an external weight of approximately 50% BW, it is reasonable that their value is approximately five times larger than what the present study measured for M_h,max.

Knee

Kinematics

Unsurprisingly, a small RoM_k was expected and confirmed in this study because the BE were performed with straight legs (Fig. 2a, Tables 2 and 3). Similar RoM_k values were obtained for the straight leg exercise goodmornings [29]. The RoM_k is significantly higher for BE_h, and the starting positions differ between BE_h and BE_s (Fig. 2a, Tables 2 and 3). To increase the RoM_h for BE_h, participants might have tilted their pelvis forward, which could have promoted knee extension and thus increased the RoM_k. However, compared to other strength exercises, the RoM_k is still extremely small. In the starting position of 1L, the knee might have been more extended than in the starting position of 2L due to stabilising reasons and higher moments (Fig. 2a, Tables 2 and 3).

Kinetics

For the knee joint not being directly involved in the movement, high M_k,max were obtained, especially for BE_h and 1L executions. It is important to note that M_k,max is an extension moment and is thus supporting the isometric contraction of the hamstrings and providing a training effect for these muscles. In addition to the positive effect on the hamstrings, the extension moment might exert forces on the passive structures in the knee, which must be considered in patients with current or past knee injuries. As far as we know, no one has ever looked at the kinematics and kinetics in the knee during BE although this exercise might shift the quadriceps/hamstring ratio towards hamstring as part of an Anterior cruciate ligament (ACL) prevention program. The knee extension moments obtained for goodmornings were slightly higher, probably due to the extra barbell load of 25% BW [29].

Muscular activity

Because BE are a dynamic exercise, the EMG results must be treated and interpreted with caution due to skin artefacts. This caution is especially important for the comparison between BE_h and BE_s, which are different movements.

In general, all muscles were more active during the concentric phase than during the eccentric phase (Tables 4 and 5). For the concentric phase, the activity levels for gluteal muscles and hamstrings agree with the literature [1]. The activity level for lumbar and thoracic dorsal back muscles are considerably lower (lumbar: 39-56% MVC, thoracic: 43% MVC; [1]). For gluteal muscles and hamstrings, no significant differences between BE_h and BE_s were found, which agrees with the results of Mayer and co-workers [8], who did not find any influence of lumbar posture on these muscles. Moreover, they also observed that an accentuated lumbar lordosis increased the activity of the lumbar extensors, whereas the present study found, for ErecLum, no significant differences between BE_h and BE_s. However, due to the different MVC measurement settings, electrode placements, starting positions and exercise executions, a direct comparison between different studies is difficult. The only study looking at the muscle activities in the eccentric phase of the BE exercise was a study by De Ridder and co-workers [13], who considered BE performed in a horizontal position and with an extra load of 60% 1RM. Due to the extra load, a comparison of the values between their study and the present study is not reasonable.

As expected, the ventral trunk muscles were almost inactive (2-5% MVC), which agrees with the results of Callaghan and co-workers [11]. The high standard deviations (see Table 4) suggest that some participants needed to activate those muscles more than others to stabilise the trunk.

Comparison of types BE_h and BE_s

Apart from the obvious differences in RoM_mub, RoM_lmb and RoM_h, there were other relevant differences between BE_h and BE_s. BE_h showed higher external moments in hip, knee and lower back with higher or similar RoMs (Fig. 2a-c, Tables 2 and 3). This finding suggests a higher training effect for BE_h for dorsal back and hip muscles and for hamstrings. However, the above-mentioned opposed movement in the spine for BE_h must be considered.

Comparison of versions 1L and 2L

The 1L version showed higher external moments in the hip and knee with smaller or similar RoMs (Fig. 2a-c, Tables 2 and 3). Because strength training requires high moments with high RoMs, we are unsure whether 1L provides a greater training effect for the dorsal hip muscles and hamstrings than 2L. These results suggest that the version should be chosen according to the specific requirements, i.e., whether high RoM or high external moments are desired.

In strength training, high moments with wide RoMs in the trained joint are desired in order to minimise the load on other parts of the body. To strengthen the hip and lower back, BE_h seem to be more efficient due to higher moments with higher or similar RoMs in the hip and lower back. According to Callaghan and co-workers [11], disk deformation, ligament and spinal loading can be reduced if BE exercises are performed with neutral lordosis. Therefore, BE_h are not only more efficient for training but also healthier. However, athletes and patients must be aware of the opposed movement in the lumbar and thoracic spine when performing BE_h.

Due to the extension moment in the knee and the flexion moment in the hip, 1L BE in particular, provide an effective training to strengthen the dorsal part of the limb in a specific RoM, especially the hamstrings and glutes. However, patients with knee deficits must be aware of the high external moments in the knee in 1L BE. In the future, kinetic and kinematic analysis combined with subject specific musculoskeletal modelling allow to quantify the individual loading conditions during strength training exercises.

(M_k,max):

Maximal joint moments of the knee [Nm/kg]

1 L:

One leg

2 L:

Two legs

Abdo:

M. Rectus abdominis

ACL:

Anterior cruciate ligament

BE:

Back extension

BE_h :

Back extension dynamic hip

BE_s :

Back extension dynamic spine

BW:

Body weight

C:

Thoracic curvature [1/m]

C_l :

Lumbar curvature [1/m]

C_l,rp :

Lumbar curvature at the reversal point [1/m]

C_l,s :

Lumbar curvature at the start [1/m]

C_t,rp :

Thoracic curvature at the reversal points [1/m]

C_t,s :

Thoracic curvature at the start [1/m]

EMG:

Electromyography

ErecLum:

Lumbar part of M. erector spinae

ErecThor:

Thoracic part of M. erector spinae

FFT:

Fast-Fourier-Transformation

GlutMax:

M. Gluteus maximus

GlutMed:

M. Gluteus medius

HamLat:

Lateral hamstrings

HamMed:

Medial hamstrings

L:

Leg

L4/L5:

Between lumbar vertebra 4 and 5

M_b,max :

Maximal joint moments of the back at L4/L5 [Nm/kg]

M_h,max :

Maximal joint moments of the hip [Nm/kg]

MVC:

Maximum voluntary contraction

Obli:

M. Obliquus externus abdominis

RoM:

Range of motion [°]

RoM_h :

RoM in the hip [°]

RoM_k :

RoM in the knee [°]

RoM_lmb :

RoM lower to middle back [°]

RoM_mub :

RoM middle to upper back [°]

RoM_plb :

RoM pelvis to lower back [°]

RoMs:

Ranges of motion [°]

We kindly thank Janine Weigand for the construction of the bench and Edeny Baaklini, Michele Mazzariello and Anna Kratschmar for measurement support.

Funding

No funding from third parties was contributed.

Availability of data and materials

The dataset generated and analysed during the current study are available from the corresponding author on reasonable request. Raw data and analysed results are stored for the next ten years at the laboratory for movement biomechanics, ETH Zurich, Switzerland.

Authors’ contributions

FS, RH and NH acquired the data and undertook the data analyses including the preparation of the tables and figs. FS and NS performed the statistical analysis and helped drafting the manuscript. BT helped in both interpreting the data and drafting the manuscript. FS and SL conceptualised and designed the study, supervised the data analyses and interpretation and helped draft the manuscript. All authors read and approved the final manuscript.

Competing interests

The authors declare that they have no competing interests.

Consent for publication

Written consent was obtained for the publication of fig. 1 from the participant shown.

Ethics approval and consent to participate

This study was approved by the ethics committee of ETH Zurich, Switzerland (EK 2014-N-31). All participants provided written agreement to be part of this study and one participant to publish this figure.

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Affiliations

1. Institute for Biomechanics, ETH Zürich, HCP H 21.1, Leopold-Ruzicka-Weg 4, 8093, Zürich, Switzerland
   • Florian Schellenberg
   • , Nicole Schmid
   • , Ramona Häberle
   • , Nicole Hörterer
   • , William R. Taylor
   •  & Silvio Lorenzetti

Corresponding author

Correspondence to Silvio Lorenzetti.

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