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Biomechanical Determinants of Knee Joint Loads Associated with Increased Anterior Cruciate Ligament Loading During Cutting: A Systematic Review and Technical Framework



Cutting actions are associated with non-contact ACL injuries in multidirectional sports due to the propensity to generate large multiplanar knee joint loads (KJLs) that have the capacity to increase ACL loading and strain. Numerous studies have investigated the biomechanical determinants of KJLs in cutting tasks. The aim of this systematic review was to comprehensively review the literature regarding biomechanical determinants of KJLs during cutting, in order to develop a cutting technical framework alongside training recommendations for practitioners regarding KJL mitigation.


Databases (SPORTDiscus, Web of Science and PubMed) were systematically searched using a combination of the following terms: “Biomechanical determinants”, or “Knee abduction moment”, or “Technical determinants”, or “Knee loading”, or “Knee loads”, or “Mechanical determinants”, or “ACL strain”, or “Knee adduction moment”, or “Anterior tibial shear”, or “Knee internal rotation moment”, or “Knee valgus moment” AND “Change of direction”, or “Cutting manoeuvre”, or “Run and cut”, or “Run-and-cut”, or “Sidestepping”, or “Side-stepping”, or “Shuttle run”. Inclusion criteria were as follows: studies examining a cutting task < 110° with a preceding approach run that examined biomechanical determinants of KJLs using three-dimensional motion analysis.


The search returned 6404 possibly eligible articles, and 6 identified through other sources. Following duplicate removal, 4421 titles and abstracts were screened, leaving 246 full texts to be screened for inclusion. Twenty-three full texts were deemed eligible for inclusion and identified numerous determinants of KJLs; 11 trunk, 11 hip, 7 knee, 3 multiplanar KJLs, 5 foot/ankle and 7 identifying ground reaction forces (GRFs) as determinants of KJLs.


Using the framework developed from the results, cutting KJLs can be mitigated through the following: reducing lateral foot-plant distances, thus lowering hip abduction and orientating the foot closer to neutral with a mid-foot or forefoot placement strategy; minimising knee valgus and hip internal rotation angles and motion at initial contact (IC) and weight acceptance (WA); avoiding and limiting lateral trunk flexion and attempt to maintain an upright trunk position or trunk lean into the intended direction; and finally, reducing GRF magnitude during WA, potentially by attenuation through increased knee flexion and emphasising a greater proportion of braking during the penultimate foot contact (PFC).

Key Points

  • High-risk postures in cutting include frontal plane trunk alignment away from the cutting direction, an internally rotated hip; initial valgus alignment of the knee at weight acceptance; a knee close to full extension; wide foot-plant distance (analogous with hip abduction); increased foot progression angle (inverted foot towards the midline), rearfoot landings and a lack of PFC braking strategy.

  • Practitioners are encouraged to coach a reduction in lateral foot-plant distances, reducing hip abduction and orientating the foot closer to neutral with a mid-foot strike strategy. Coupling this with a minimisation of knee valgus and hip internal rotation at initial contact (IC) and weight acceptance (WA) alongside encouraging trunk lean in the intended direction should ameliorate KJLs. An attempt to reduce the magnitude of the GRF in the final foot contact should be made, through emphasising a greater proportion of braking in the prior steps to turning.

  • Practitioners should consider training strategies which reduce high-risk postures and biomechanics, both of which are modifiable risk factors for potentially hazardous multiplanar knee loads.


Non-contact anterior cruciate ligament (ACL) injuries are one of the most devastating injuries an athlete can sustain. They occur in a multitude of sports [1,2,3], typically during high-impact tasks such as decelerations, landing and changes of direction (CODs), namely cutting [1, 2, 4,5,6,7,8]. There are a large number of ACL injuries reported annually (80,000 per year in the USA alone) [9], 70% arising from non-contact situations [10] with an incidence rate of 0.42 per 1000 player hours [11]. Such injuries carry with them a return to play period of approximately 6–24 months [12, 13] and are associated with an increased risk in the development of osteoarthritis in later life [14]. Furthermore, the estimated cost of ACL reconstructions in America is estimated to be 17,000 dollars per reconstruction [9], highlighting the financial burden they can place on healthcare and public health services, thus providing rationale for their mitigation.

ACL injuries occur when a load exceeds the ligament’s tolerance [15]. Cadaver [16,17,18] and computer simulated modelling studies [19, 20] have examined ACL strain and forces to gain a greater understanding of the respective biomechanical parameters responsible. Externally applied knee abduction moments (KAMs) and knee internal rotation moments (KIRMs), alongside anterior tibial shear force (ASF), have all been identified as loading parameters that have the potential to increase ACL strain [17, 18, 20, 21] and are subsequently used as surrogates of non-contact ACL injury risk. McLean et al. [22] suggest that uniplanar loading in the sagittal plane is insufficient to elicit ACL rupture, elsewhere the mechanism of ACL injury has been described as multiplanar [23, 24]. Unsurprisingly, a plethora of studies have identified multiplanar knee joint loads (KJLs) to elicit significantly greater ACL strain than uniplanar loads alone [17, 18, 21]. Recently, Bates et al. [18] identified KAMs as eliciting the greatest change in ACL strain in isolated conditions than ASF or tibial internal rotation. However, the greatest level of ACL strain observed was when all three loading parameters were applied in the greatest magnitude conditions, substantiating previous evidence of multiplanar loading being the most potent stimulus for ACL strain [16, 17, 21].

COD tasks such as cutting manoeuvres (which for the purpose of this review will be referred to as changes of direction between 30° and 110°) are key actions associated with non-contact ACL injuries; thus, understanding the biomechanical determinants of multiplanar KJLs in cutting is of great importance, particularly for athletes who participate in cutting dominant sports. Cutting has retrospectively been identified as the primary action associated with non-contact ACL injury in rugby (66% [7];) American football (60% [5];) and handball (60% [2];). Furthermore, cutting has been found to elicit greater multiplanar KJLs than both single legged landings (SLLs) [25] and multiplanar side jumps amongst athletes [26]. When considering the large number of cuts in invasion games [27, 28], this creates a problem for health practitioners and athletic development staff, whereby athletes are being continuously exposed to potentially injurious loads. Therefore, understanding the technical and mechanical determinants of these loads in cutting tasks is of paramount importance to inform appropriate injury mitigation practice.

In order to better understand the mechanism of non-contact ACL injuries, several studies have identified several key postures during visual observations of non-contact ACL injuries. For example, contralateral trunk lean has been observed in numerous ACL incidents in female athletes [29]. Frontal and sagittal hip motion whereby an abducted and flexed hip has been observed in 86% and 96% (respectively) of non-contact ACL injuries in a cohort of National Football League (NFL) players across three seasons [5]. Additionally, a knee posture that is close to full extension is a prominent characteristic in non-contact ACL ruptures in American football [5], elite rugby [7] and handball [7]. Knee abduction was observed in 11/12 non-contact ACL incidents in handball (with tibial rotation) [2], 92% of non-contact ACL injuries in American Football [5] and in injured basketball players (28.7° ± 19.5° greater in injury incidents) [4]. Regarding the foot, a rearfoot landing was a consistently observed feature in rugby (90% of cases: p < 0.001) [7] and basketball [4]. Finally, an everted ankle/foot position has been observed in 90% of non-contact ACL injuries in the NFL [5]. All of the above detail a phenomenon first described by Hewett as “dynamic valgus” [30] that has been identified as a contributory movement pattern in non-contact ACL injuries.

The apparent consistencies between non-contact ACL rupture incidents suggest that these commonly observed technical postures are contributory to the biomechanical load elicited at the knee, leading to rupture. A plethora of research has investigated these “biomechanical determinants” (i.e. body postures and kinetics that determine the magnitude of KJLs) in order to advise practitioners what is best regarding optimal technique to reduce multiplanar KJLs in cutting [31,32,33,34,35,36,37]. However, these studies have used varying cutting angles, approach velocities and cohort of athlete all which can affect multiplanar KJLs [32, 38, 39] making between-study comparisons difficult. Numerous intervention studies have attempted to reduce KJLs through targeting these segments that contribute to multiplanar KJLs with mixed success [31, 40, 41]. Dempsey et al. elicited 36% reduction in KAMs through modifying contralateral trunk lean and foot-plant width. Adopting this multi-segmental approach may be more beneficial, considering other uni-segmental interventions have failed to elicit any reduction in KJLs [40, 41]. Furthermore, these intervention studies [31, 40, 41] have failed to measure any possible detrimental effect upon performance which would have a succinct effect on engagement and adherence to an intervention, as athletes will not engage with an intervention that will elicit performance decrements [34].

Previous reviews have commentated on risk factors associated with cutting and non-contact ACL injury risk [42, 43], although these have been narrative and not developed guidelines for practitioners. To date, no technical model for cutting exists. Therefore, to inform effective and adhered to injury mitigation protocols, the construction of a research informed technical model detailing optimal cutting technique would be beneficial for practitioners working with athletes in cutting dominant sports. This would provide a better understanding of the “high-risk” postures and mechanics that increase KJLs during cutting and subsequent ACL loading and provide clarity on safe cutting technique. Therefore, the aim of this systematic review is twofold: firstly, to comprehensively review the literature available regarding biomechanical determinants of KJLs in cutting tasks and factors affecting them with regard to injury and performance; and secondly, to develop a technical framework alongside recommendations for practitioners regarding mitigations of KJLs during cutting tasks.



A literature search was performed using PubMed, Web of Science and SPORTDiscus databases from January 2019 to May 2020 with the final search date of 5 May 2020. A schematic of search methodology in accordance with established guidelines [44] will be presented in the results below. Search terms were as follows:

(1) “Biomechanical determinants”, or “Knee abduction moment”, or “Technical determinants”, or “Knee loading”, or “Knee loads”, or “Mechanical determinants”, or “ACL strain”, or “Knee adduction moment”, or “Anterior tibial shear”, or “Knee internal rotation moment”, or “Knee valgus moment” AND

(2) “Change of direction”, or “Cutting manoeuvre”, or “Run and cut”, or “Run-and-cut”, or “Sidestepping”, or “Side-stepping”, or “Shuttle run”

Subsequently bibliographies of prospectively eligible studies were compiled and hand searched to screen for further suitable studies. If disagreement occurred between the two reviewers (TD and TDS), a third independent reviewer (PJ) was consulted and their decision deemed as final.

Study Inclusion and Exclusion Criteria

Inclusion criteria for studies were as follows:

  1. 1.

    Investigated a pre-planned or unplanned cutting task that contained a preceding approach run and subsequent change in direction. The decision was made to omit tasks that included a false step or hop or that omitted an approach run. Omission of an approach run would not truly replicate the loading parameters of non-contact ACL injury situations due to the absence of a deceleration (which has been identified as the component where most non-contact ACL ruptures occur) and redirection component that are asymptomatic of horizontal velocity. Cutting tasks of up to 110° were considered for inclusion as it was deemed that any COD greater than this (i.e. pivoting actions) would possess succinct biomechanical differences that would require a different technical framework.

  2. 2.

    Examined technical or biomechanical determinants of knee joint moments or loads in a cutting task using 3D motion and GRF analysis including the effect of exercise intervention or technique modification.

  3. 3.

    Included healthy participants with no previous history of ACL injury.

  4. 4.

    Original research, full text published in a peer review journal, in English.

Studies that did not meet the abovementioned criteria were excluded from the review.

Assessment of Study Quality

An assessment of study quality was conducted as per previously established methods [45, 46] using the modified scale constructed by Brown et al. [46]. This is deemed to be more suitable for assessing the methodological quality of COD studies due to the omission of criteria such as random allocation, assessor blinding and subject blinding that are present in more commonly used scales such as the Cochrane or Delphi, Physiotherapy, Evidence Database scales. Each component was individually scored from 0 to 2 (where 0 = clearly no, 1 = maybe or insufficient information and 2 = clearly yes).

Data Collation

Data were independently extracted from each study by the lead reviewer (TD). Results were collated through identifying significant findings (p < 0.05), correlational R values and coefficients of determination (R2). Data were then systematically separated by cutting angle investigated and the subsequent biomechanical determinant/segment that was cited by each respective study. Data was sought for all primary outcome measures which were multiplanar KJLs. Peak variables obtained from discrete point analysis methods, and variables derived from continuous analysis methods such as statistical parametric mapping (SPM) were sought for all primary outcome measures. The external and internal (respectively) joint moment conventions were all searched for and included the following: knee abduction moment (KAM), knee adduction moment (KADM), knee flexion moment (KFM), knee extension moment (KEM), and knee internal rotation moment (KIRM).


Search Results

Figure 1 presents a flow chart summarising the results of the systematic search process whereby 6404 potentially eligible articles were identified across PubMed, Web of Science and SPORTDiscus databases. Following title, abstract and full text screening, 17 studies were deemed eligible for inclusion in this review. A further 6 eligible studies were identified from the reference list screening of eligible studies. Of the 23 studies deemed eligible for inclusion, 15 [31, 34, 35, 37, 38, 40, 41, 47,48,49,50,51,52,53,54] examined a 45° cut; six [34, 36, 55,56,57,58] a 90° cut; three involved self-selected ranges of 35°–60° [59] and 70°–90° [60] and a mean cutting angle of 67° [61], and one utilised a 110° cut [37]. With regard to anticipation, 12 studies [34, 36, 38, 48, 51, 53, 55,56,57,58, 60, 61] adopted a pre-planned cut, with eight [35, 37, 40, 41, 47, 49, 50, 54] utilising unplanned cuts; three studies [31, 52, 59] examined both pre-planned and unplanned cuts. Regarding the approach velocity of tasks, five studies adopted a maximum effort approach [34, 56, 57, 60, 61], with four utilising a self-selected pace [35, 40, 50, 55]. Seven studies utilised approach velocity windows [36, 37, 49, 51, 53, 54, 58] ranging from 3.5–4.5 m/s [54] to 5.5–7.0 m/s [53]. Six studies [31, 41, 47, 48, 59, 62] utilised approach velocities ranging from 3.5 [55] to 5.2 m/s [31]. Finally, one study adopted varying incremental approach speeds of 2, 3, 4 and 5 m/s [38]. All 23 studies examined KAMs, with three examining KIRMS [35, 54, 60] and two examining KFMs (external)/KEMs respectively [54, 60].

Fig. 1

Flow chart illustrating the different phases of the search strategy and study selection process. Key: 3D: three-dimensional; GRF: ground reaction force; KJL: knee joint load; ACL: anterior cruciate ligament

Assessment of Methodological Quality

In accordance with the methods of Dos’Santos et al. [45] and Brown et al. [46], assessment of methodological quality was conducted on the 23 studies deemed eligible for inclusion in this review and is presented in Table 1. Of the 23 studies, the mean methodological quality score was 11.86 (66%). Scores ranged from 6 (33%) [35] to 16 (88%) [60]. Eleven studies were below this mean score [35, 36, 38, 49,50,51, 54,55,56, 58, 61], with 12 studies presenting methodological quality greater than the mean [31, 34, 37, 40, 41, 47, 48, 52, 53, 57, 59, 60].

Table 1 Assessment of methodological quality for 23 studies retrieved examining KJLs in cutting tasks


Eleven studies [31, 35, 36, 40, 41, 48, 50, 52, 54, 55, 61] identified trunk biomechanics as a biomechanical determinant responsible for generating large KJLs namely KAMs, or targeted the trunk in an intervention with the view to reducing KJLs and are presented in Table 2. Being the largest segment of the body, containing approximately half of the body’s mass, trunk positioning plays a significant role regarding the direction of the GRF vector during the weight acceptance phase of the cut. A contralateral lean of the trunk in the opposite direction of travel results in a greater laterally directed GRF [36]. This results in a greater perpendicular distance between the GRF and the knee, and increases KJLs due to a greater moment arm of the GRF in the frontal plane. Numerous other studies retrieved identified lateral trunk flexion as being a significant contributor to KJLs in pre-planned [36, 48, 55, 61] and unplanned [35, 52, 54] cuts of varying magnitudes (Table 2).

Table 2 Studies whereby trunk motion has observed to be contributory to KJLs

Three interventions [31, 40, 41] targeted the trunk with regard to lowering KJLs in unplanned cuts [40, 41] and alongside pre-planned cuts of 45° [31]. Of these, two observed no changes in KAMs as a result of an intervention of static trunk exercises [40], and perturbed plyometric training [41] respectively. Dempsey et al. [31] elicited a meaningful reduction in KAMs following a technique modification protocol of reducing trunk lean and foot-plant width (Table 2).


Eleven studies have identified hip kinematics or kinetics as determinants in generating greater KJLs in cutting tasks (Table 3). Of these, 2 identified sagittal plane kinematics/kinetics as determinants of KAMs [51, 60] and IRMs [60]. Seven identified frontal plane mechanics as determinants of KAMs [31, 36, 48, 53, 54, 59, 61] and IRMs [54, 60]. Finally, 5 studies [34, 37, 51, 53, 61], implicated transverse plane motion such as hip internal rotation as a determinant of KAMs.

Table 3 Studies identifying hip kinematics and kinetics in generating large KJLs.

Seven studies retrieved observed frontal plane hip motion, namely hip abduction to influence the magnitude of KAMs [31, 36, 48, 53, 54, 59, 63] and IRMs [54] in cuts of 45° [31, 48, 54], 90° [36], and self-selected ranges of 35–60° [59] and 70–90° [60] and a mean angle of 67° [61]. Excessive levels of hip abduction or lateral foot-plant distance (often used interchangeably) would result in the distal portion of the femur to be aligned medial to the GRF vector, resulting in greater KJLs. Greater abduction would also result in greater laterally orientated GRFs [36], resulting in a greater lever arm from the application of force relative to knee joint centre further amplifying KJLs.

Five studies identified transverse plane hip motion as a determinant of KJLs [34, 37, 51, 53, 61]. Four of the five studies identified an increased amount of internal hip rotation as responsible for generating greater KJLs [37, 51, 53, 61]. Transverse plane motion (internal rotation of the hip) would result in the knee being placed in a more medial position to the GRF vector and increase the perpendicular distance of the moment arm which would amplify the GRF resulting in a greater KAM. A significantly greater abundance of internal hip rotation (Table 3) was observed in a cohort of female athletes that generated greater KAMs than their counterparts, during 45° cuts [53]. Similar findings were observed whereby greater internal rotation of the hip is a determinant of KAMs in 45° [51], self-selected [61] and unanticipated 45° and 110° cuts [37]. Conversely, one study identified increased internal hip rotation as significantly associated with a reduction of KAMs in 90° cuts [34]. Finally, two studies identified sagittal plane biomechanics in the form of hip flexion and hip flexor moment as determinants of KAMs in 45° [51] and 70–90° [60] cuts.


Several retrieved studies identified biomechanical variables about the knee as significant modulators of KJLs [34, 36, 37, 51, 54, 60, 61] (Table 4). Of these, two examined KJLs in pre-planned [51] and unplanned [54] 45° cuts. Two studies examined 45° and 90° pre-planned [34] and unplanned 45° and 110° cuts, respectively [37]. Two studies utilised a self-selected protocol of 35–60° [59] and a mean cutting angle of 67° [61]. Five [36, 37, 51, 54, 61] of the above studies identified frontal plane knee motion (knee abduction angle) as a determinant of KJLs. A knee valgus position is problematic, by placing the knee more medial to the GRF vector and amplifying the moment arm in the frontal plane resulting in a greater KJL. Two studies [34, 60] identified multiplanar moments of the knee in the form of internal knee extension moments (external KFMs), knee internal rotation moments (KIRMs) and knee flexion moments (KFMs) as responsible for eliciting greater KAMs.

Table 4 Studies implicating biomechanical variables about the knee in generating large KJLs

Determinants of Multiplanar KJLs

Three studies examined the biomechanical determinants of multiplanar KJLs [35, 54, 60]. Of these, two utilised an unplanned 45° cut [35, 54], and the third adopting a pre-planned cut of 70–90° [60]. A range of biomechanical kinematics and kinetics were implicated in the generation of multiplanar knee loads and are presented in Table 5.

Table 5 Studies identifying determinants of multiplanar loads about the knee

Ankle and Foot

Five studies [47, 49, 53, 56, 61] identified the ankle or foot as a determinant of KJLs. Three utilised 45° cuts, in unanticipated [47, 49] and pre-planned [53] conditions respectively. The other two consisted of pre-planned cutting tasks of 90° [56] and a self-selected protocol [61]. Of these, four [47, 49, 56, 61] studies identified sagittal plane alignment of the ankle as a significant determinant of KJLs. Three [49, 56, 61] of these studies identified a rearfoot strike as responsible for generating greater KAMs, with the remaining study observing opposite results to the contrary [47]. One study retrieved also identified transverse plane motion of the foot (a greater inverted foot) as a determinant of KAMs in an excessive “at-risk” group [53]. This would be due to the inverted foot placing the knee in a more compromised valgus position, for the foot to be orientated towards the direction of intended travel.

Ground Reaction Forces, Penultimate Foot Contact and Braking Strategy

Seven studies (Table 7) identified ground reaction forces or braking strategy as determinants of KJLs. Of these, three utilised 90° pre-planned cuts [36, 57, 58], two pre-planned 45° cuts [38, 53], one study examined a pair of cuts of 45 and 110° [37]; the remaining study used a cut of 70–90° [60]. Four [36, 57, 58, 60] examined the kinematics and/or kinetics during the preceding penultimate foot contact (PFC) in order to measure the effectiveness of braking strategies, to which two identified PFC variables as determinants of KJLs [57, 58]. Finally, four studies [37, 38, 53, 58] identified multiplanar GRFs as determinants of KJLs.


The primary aims of this systematic review were to critically evaluate the current literature regarding the determinants of KJLs during cutting tasks, and use this in order to construct a technical framework in order to inform practitioners regarding the management of KJLs in cutting. In addition, it was also the aim to identify areas of further research, limitations within the literature and provide recommendations to practitioners concerning the management of athletes regarding KJLs in cutting tasks. Twenty-three articles retrieved directly examined the biomechanical determinants of KJLs in cutting tasks. Of these, 11 implicated trunk motion as determinant of KJLs, 11 identifying hip biomechanics, seven about the knee, three examining multiplanar KJLs, five implicating foot and/ or ankle positioning, and seven identifying GRFs and braking strategy as contributory factors regarding KJLs.


Trunk positioning is integral to mitigating KJLs during cutting (Table 2), due to the effect upon the GRF orientation and frontal plane moment arm of the knee as described above. Optimal trunk positioning therefore would constitute of the athlete leaning towards the intended direction of travel to mitigate this risk. High-risk and optimal trunk positioning are presented in Fig. 2a respectively.

Fig. 2

a Sub-optimal (left) and optimal (right) trunk alignment in cutting. b Sub-optimal (left) and optimal (right) frontal plane hip alignment in cutting. c Sub-optimal (left) and optimal (right) transverse plane hip alignment in cutting. d Sub-optimal (left) and optimal (right) frontal plane knee alignment in cutting. e Sub-optimal (left) and optimal (right) foot progression angles in cutting. f Sub-optimal (left) and optimal (right) foot landings in cutting. g Sub-optimal (left) and optimal (right) PFC braking in cutting

Trunk positioning also has specific implications for athletes in ball carrying or implement carrying sports such as rugby, American football, lacrosse and hurling whereby the carrying of an object could constrain the plant side arm, and result in increased contralateral trunk flexion or possible rotation. Chaudhari et al. [55] identified that constraining the plant side arm by the trunk in numerous sport-specific conditions such as holding a football and lacrosse stick resulted in significant increases in KAMs, against a non-constrained control condition (Table 2). This is of importance for practitioners involved in ball or implement carrying sports, as there appears to be a propensity to generate greater KAMs due to the influence that carrying an object can have on frontal plane motion. Although carrying a ball or implement can increase KJLs, athletes cannot simply put down their stick or refuse to carry the ball if required. Therefore, prioritising sagittal plane alignment of the lower limb and training appropriate deceleration technique is suggested as a more effective way of reducing KJLs in these populations, due to the demands of implement carrying sports.

If certain sub-optimal movement patterns have succinct relationships with contraindicative knee loading, it is of interest to further understand what actually causes poor trunk alignment, so practitioners can appropriately address whether it is a technique deficit, or one on a neuromuscular level. Jamison et al. [50] examined pre-activation in the core muscles via percent differences and co-contraction indices, and hypothesised that possible asymmetry in activation could be responsible for a trunk misalignment, and therefore KAMs. No significant differences were found across a multitude of asymmetry co-contraction index differences and KAMs, and lateral trunk lean (Table 2) suggesting that poor trunk control in cutting is not due to a neuromuscular trunk deficit. Therefore, technique modification may be more appropriate in addressing trunk lean as opposed to strengthening trunk musculature.

Numerous interventions have attempted to address trunk movement in order to reduce KJLs in cutting with mixed success [31, 40, 41]. Considering that greater KJLs are caused by numerous segmental contributions, adopting a multi-segmental approach in intervention may be most effective in eliciting reductions. Dempsey et al. [31] adopted a technique modification approach whereby a reduction in trunk lateral flexion with a reduced foot-plant width elicited a 36% reduction (Table 2) in KAMs in 12 athletes over a 6-week intervention. Additionally, change in torso lateral flexion exhibited a moderate relationship (r = − .377) with KAM. However, the failure to include a control group and to report performance times pre-post intervention is worth noting, as athletes will seldom engage in a programme that will be detrimental to performance [34]. Jamison et al. [40] failed to elicit any reduction in trunk lean or KAMs in 11 males following 6 weeks of a trunk stabilisation programme that incorporated prone planks, side planks and other trunk stabilisation exercises, in unanticipated 45° cuts. A shortcoming of the study to only utilise static stabilisation exercises may explain these findings, as they would have limited transfer to high velocity dynamic movements such as cutting.

More dynamic training methods such as plyometrics may carry greater efficacy in modifying KJLs during cutting tasks. This is resultant of the need to attenuate and redirect multiplanar GRFs, which would carry improved transfer into cutting. Using novel methods, Weltin et al [41] examined the utility of perturbed and unperturbed plyometric training in reducing KAMs. Significant reductions were observed in contralateral trunk and pelvic rotations (Table 2) although this did not translate into a reduction in KAMs. However, increased levels of pelvic axial rotation were present, which could indicate a change in strategy or a preparatory movement prior to cutting. Increased pelvic motion in the transverse plane would result in a more medially placed limb relative to the GRF that increases KAMs [36, 51, 54, 61] and could have offset any potential KJL reduction from corrected trunk motion. Future research examining the interaction between preparatory strategies, different body segments and their respective contribution to KJLs is recommended. A greater understanding of these preparatory strategies would be useful for practitioners and could inform technique-orientated interventions.

Athletes should aim to align the trunk to the intended direction of travel, in order to reduce KJLs. Examining the effectiveness of a multi-segmental approach when aiming to reduce KJLs is warranted, considering the only study to elicit a meaningful reduction [31] adopted this strategy. This should be tested through more interventions carried out in “high-risk” populations utilising more dynamic exercises and technique modification, as opposed to the utilisation of static exercises. Following this, any effect on performance could be observed and possibly inform future practice and compliance if said interventions had a positive effect on performance times alongside ameliorating the magnitude of KJLs.


Frontal and transverse plane hip alignment is imperative when attempting to mitigate KJLs during cutting (Table 3). Malalignment of the hip in either of these planes can result in sub-optimal orientation of the distal joints (knee and ankle) further down the kinetic chain. This results in a greater frontal plane moment arm about the knee, due to a medially positioned knee relative to the GRF and laterally directed GRFs [36]. Therefore, when cutting, athletes should avoid excessive abduction and internal rotation of the hip to mitigate KJLs. Figure 2 b and c display sub-optimal and optimal hip alignment in the frontal and transverse planes respectively.

The need to attenuate and redirect forces in the sagittal plane is of great importance when changing direction, considering the mechanisms of frontal and transverse hip alignment that amplify KJLs. Although limited evidence has implicated sagittal plane biomechanics as a determinant of KJLs. McLean et al. [51] elucidated increased hip flexion to be contributory to greater KAMs in 20 NCAA athletes. This is somewhat counterintuitive when considering the relationships that frontal and transverse plane hip motions share with KAMs [37, 53, 61]. Despite the numerous studies retrieved, this finding has not been substantiated elsewhere. This could however be attributed to the low percentage of variance explained in KAMs by hip flexion (R2 = 16%), despite the significance of the findings.

McBurnie et al. [60] identified peak hip flexor moments as a strong correlate of KAMs and IRMs (Table 3) in 70°–90° cuts, a somewhat novel finding. Peak hip flexor moments have been suggested as having a protective role against KAMs in 180° pivots [64]. Greater sagittal plane alignment would allow for better absorption of loads through large musculature of the thigh and hip, and thus reduce loading through utilising the substantial eccentric strength of these muscle groups. However, the lower reduction in velocity present throughout a cutting movement due to a desire to maintain velocity along the path of the cut could explain this finding. This would amplify the GRF generated [38] and thus greater moments about the hip, eliciting a greater knee joint load. Considering the above, alongside sagittal plane hip power and extensor moment being identified as determinants of 45° cutting performance [34], it is possible that the biomechanics required for faster cutting performance may be disparate with those for mitigating KJLs and injury risk as previously proposed [34, 60].

First identified by Havens [34], it appears there is a clear conflict between optimal cutting performance biomechanics, and those optimal for mitigating KJLs. Faster completion times require shorter ground contact times [65] and a greater approach velocity, rate of deceleration and GRFs to be produced [60, 66]. This would also result in a greater GRF [38] being amplified by any frontal plane moment arm, which would result in greater KJLs. Greater hip flexor moments previously were identified as a significant determinant of KAMs and performance time in 70–90° cuts [60], and identified as having a strong relationship with 45° cut completion time [34]. In addition, medio-lateral separation distance has also been identified as a strong predictor of both cutting performance and KJLs [34]. Furthermore, McBurnie et al. identified KAMs, IRMs and KFMs (external) to possess significant relationships with faster cutting performance times (R = − 0.590; d = − 1.0; R = 0.525; p = 0.001; R = − 0.509; p = 0.002 respectively) and a presence of greater knee abduction angles in faster performers in a 70–90 cut°. Taken together, the greater kinetics and moments that are required for performance will undoubtedly elevate KJLs. However, the detrimental effect of these despite their need could be mitigated through minimising the frontal plane moment arm to which these forces can be amplified. In addition, it is proposed that effective deceleration training could reduce the magnitude of the GRF in the final contact, where injury commonly occurs.

There is strong evidence for constraining frontal plane hip motion during cutting tasks, due to the effect of increasing the frontal plane lever arm which amplifies the GRF (Table 3). If one abducts the hip to a greater extent, it would shift the centre of mass (COM) and GRF laterally, possibly causing a greater contralateral trunk lean, which as discussed above would elicit greater KAMs. This combination has been previously observed [54] and is further consolidated by Dempsey et al.’s [31] intervention study whereby reducing these two parameters resulted in a significant reduction in KAMs (36%, p = 0.034). This multi-segmental approach is recommended to practitioners to maximise intervention effectiveness, although further research is required to determine if a more medial foot plant would elicit performance detriment.

It appears there may be a greater requirement for a wider foot plant in cuts of a greater degree (90° and 67° respectively) [36, 61] in order to generate greater perpendicular forces, which may explain relationships of hip abduction with increased KJLs in these tasks. During unconstrained cuts, Kristianslund et al. [61] found hip abduction to be significantly contributory to KAMs (Table 3). More interestingly, the cutting angle was also found to be synonymous with greater KAMs. This does highlight a somewhat mechanical influence that is caused by the discrete demands of the task, which has been recently discussed in the literature [39]. In further support, Jones et al. [36] identified lateral leg-plant distance as a significant determinant (Table 3) of KAMs in 90° cuts. A moderate (R = .59) correlation was also observed between lateral leg-plant distance and medial GRFs, substantiating the notion that a wide foot plant is required to generate the GRFs necessary to facilitate direction change in greater angled turns. Therefore, if greater angled cuts are being performed, it may be necessary to adopt a wide foot plant to meet the demand of the task. In this instance, it is recommended KJLs are mitigated through ensuring appropriate trunk positioning, sagittal plane alignment of the lower limb and sufficient braking prior to the foot plant.

Transverse plane hip motion has been identified as a significant determinant of KJLs (Table 3). Similarly, it appears there may be an angular interaction regarding this variable, with the majority of studies identifying internal rotation of the hip as a significant determinant of KJLs in 45° cuts (Table 3). Conversely, one study [34] found a decreased amount of hip internal rotation to be contributory to KAMs. This is somewhat counterintuitive, considering the plethora of research and theory supporting the idea that internal rotation would increase KJLs. Such results were attributed to the cutting angle used being of a greater magnitude (90°). Although Sigward et al. [37] identified internal rotation of the hip to be a significant predictor of KAMs in 110° cuts. However, it is possible that there may have been an element of “pre-rotation” of the pelvis which has been observed in greater angled CODs, which could explain such findings, as it would reduce the need for a greater amount of internal hip rotation through axial pelvis rotation, although an omission of such measurement from these studies leaves this theory speculative.

It is recommended that frontal and transverse plane hip motion is limited when cutting due to the propensity to generate greater KJLs. During greater angled cuts (> 70°) where there is a need to adopt a wide foot plant, it is recommended that KJLs are mitigated through appropriate trunk lean towards the intended direction and sagittal plane alignment of the lower limb. This is likely to reduce KJLs and performance times, although may result in a “deceptive disadvantage” (whereby an opponent may find it easier to anticipate the movement), thus highlighting further conflict between the biomechanics required for optimal performance and mitigating KJLs. Sagittal plane alignment is recommended to reduce the moment arm that would amplify the greater GRFs associated with faster performance. Appropriate braking and deceleration strategies may be useful in reducing the magnitude of the GRF generated in the final foot contact, whereby the greater loads are generated and injury occurs.


Frontal plane knee motion would have a direct effect on KJLs, namely KAMs, due to placing the knee in a more medial position to the resultant GRF vector. This is a fundamental component of the “dynamic valgus” position proposed by Hewett [30] whereby an abducted knee, adducted and internally rotated hip, alongside an everted ankle and pronation have been observed as an established injury risk for non-contact ACL injuries. Sagittal plane alignment of the knee during cutting is therefore encouraged. Figure 2d displays optimal and sub-optimal frontal plane knee alignment in cutting tasks.

In a seminal study, McLean et al. [51] examined the determinants of KAMs in a cohort of 20 NCAA athletes in 45° cuts identifying initial peak valgus position to be predictive in both males and females. However, it is questionable if the determinants found would extrapolate to greater angled cuts that are mechanically discrete [39] that have been found to occur in abundance in team sports [28]. In contrast, adopting a self-selected cutting protocol, Kristianslund et al. [61] found initial knee abduction angle to be a significant predictor of KAMs in cuts of an uncontrolled magnitude. A 4.4° increase in abduction angle was found to correspond to a 19% increase in KAM. Similarly, Jones et al. [36] found knee abduction angle to correlate strongly with KAMs (Table 4) during 90° cuts in a cohort of female footballers, consolidating that an abducted knee is a universal biomechanical determinant of KAMs across all angles.

Considering that an abducted knee is contraindicative regarding knee loads during cutting, appropriate injury prevention practice would be to avoid such “risky” posture to reduce the likelihood of generating loads that will strain and could ultimately rupture the ACL. This has been typical practice in injury mitigation programmes to eliminate any valgus/ abduction alignment of the knee and appears warranted. A limitation of the majority of identified studies is that they adopt controlled approach velocities to identify determinants of KJLs; however, this may not be sufficient enough to elicit loads similar to the magnitude generated in sport-specific scenarios. Further research is recommended with uncontrolled approach velocities or maximal effort to examine if these identified determinants of KJLs remain present under greater velocity conditions. From the above, eliminating frontal plane knee alignment in line with current injury prevention guidelines is advised to practitioners working with athletes in cutting sports.

Determinants of Multiplanar Loads of the Knee

Externally applied knee flexion moments (KFMs) and internal rotation moments (KIRMs) have been identified as prominent ACL stressors [18, 21]. A knee close to full extension would amplify the moment arm of the GRF perpendicular to the knee and subsequently increase the amount of anterior shear force (ASF) generated, resulting in greater ACL loading [18]. In a similar manner, a greater KIRM would result in greater tibial angular acceleration, consequently resulting in greater ACL strain [21]. Jamison et al. [35] identified contralateral trunk lean as possessing significant negative associations with KIRMs (Table 5). However, caution is advised, due to the poor methodological quality observed (33% of desired criteria) and abovementioned relationship of trunk lean with KAMs. Unsurprisingly, frontal plane kinetics have been found to significantly predict KIRMs in sub-elite athletes alongside average and peak horizontal GRFs [60]. KFMs have been implicated as a determinant of the range of motion the knee goes through during cutting manoeuvres. A reduced knee ROM has been proposed to be contraindicative [54] due to an increased sagittal plane moment arm. However, moving through a greater knee flexion ROM would result in a greater ground contact time, which possesses an inverse relationship with performance times [65].

It is worth noting that multiplanar KJLs were all found to have significant associations with performance time in the study of McBurnie et al. [60] Taken together, with the aforementioned relationship regarding KFMs, this further signifies the performance injury conflict between “safe” cutting biomechanics and ones required for faster performance. Further research is recommended examining this phenomenon to identify the true extent to which it exists, and exploring ways to reduce KJLs without a significant detriment to performance. It is recommended that a knee close to full extension in the plant phase of the cut is avoided, due to the established relationships with ASF, and ACL loading. Landing with a “soft knee” (a knee flexion angle > 15°) is therefore warranted, due to increased ACL strain associated with extended knee postures [67].

Ankle and Foot

Foot positioning, whether this may be inwardly or outwardly rotated, first cited in the literature as a “foot progression angle” [53] has been identified as predictive of KJLs. It can be postulated that an inverted foot angle that is needed to facilitate rotation of the body in a new direction could result in the knee being placed in a somewhat medially compromised position, due to the impact of tibial internal rotation needed to inwardly rotate the distal segment and foot. Conversely, an outwardly rotated foot would lead to an increased susceptibility to eversion and pronation, which could also lead to knee abduction and tibial rotation, and thus ACL loading [68,69,70].

Sagittal plane ankle positioning can also have an effect on KJLs through the type of footfall strike adopted. Within running literature [71, 72], it has been established that runners utilising a forefoot-strike pattern (i.e. plantarflexed) will generate significantly lower GRFs than rear-footfall pattern runners. Striking with the rearfoot and a knee joint close to extension would render the gastrocnemius complex passively insufficient, and thus inhibit their ability to attenuate GRFs, resulting in greater KJLs [4]. Therefore, it appears a relationship between the ankle and the knee whereby work and load absorption of the two joints are dependent on the footfall pattern adopted. Whether this could be advantageous for practitioners in managing knee joint loading in athletic populations requires further examination. Figure 2e exhibits sub-optimal and optimal foot progression angles. In addition, Fig. 2f exhibits sub-optimal and optimal landings respectively during cutting manoeuvres.

Conflicting results have been observed in the literature regarding foot progression angle [36, 53, 61]. Sigward and Powers [53] found a significant correlation between an inwardly rotated foot contact position to KAM (Table 6), although Jones et al. [36] found no relationship between foot progression angle when examining determinants of KAMs in 90° cuts. However, the “high-risk” participants in this study (exhibiting KAMs + 0.5 SD above the mean) had a substantially greater inward foot rotation compared to the low-risk cohort (0.5 SD below the mean) (Table 6), suggesting this relationship still exists. Such disagreement between results could be explained by differing cutting angles (45° vs 90°) and approach velocities (5.5–7.0 vs 4.0–5.0 m s-1). On the contrary, Kristianslund et al. [61] found no significant relationships between foot progression angle and KAMs. However, the use of a self-selected cut and inclusion of a static defender may provide some mitigation for these results, considering the pronounced effect on kinematics and kinetics that static defenders have been found to elicit [59].

Table 6 Studies identifying foot and ankle positioning as contributory to KJLs

Regarding sagittal plane ankle position, an increased downward landing angle (e.g. more plantarflexed/ toe landing) was also found to modulate KAMs, with a 16° increase in plantarflexion corresponding to approximately a 13% decrease in KAM [61]. Cortes et al. [47] found heel striking to produce lower KAMs compared to forefoot striking in unanticipated 45° turns, a somewhat counterintuitive finding. However, a lack of familiarisation and appropriate training (three practice trials), coupled with instructed technique suggests that this protocol does not represent individual movement strategies. Alongside this, there was no calculation of mechanical work done by each joint, failing to give a valid representation of the loads the ankle and knee had attenuated respectively.

Grouping athletes by their habitual foot-strike pattern would be more useful, as this would give a more accurate representation of their pre-learned motor programmes which would be used in game situations. Donnelly et al. [49] retrospectively identified habitual forefoot and rearfoot strikers in 19 elite female hockey players performing 45° cuts. Habitual forefoot strikers exhibited significantly lower KAMs alongside significantly lower power absorption at the knee (Table 6). Interestingly, this shared a somewhat inverse relationship with ankle power, whereby forefoot strikers absorbed significantly more power through the ankle (Table 6). These results show clear interactions between the knee and the ankle in terms of power absorption and load distribution. Further research is required to investigate interactions between segments and preferential load distribution further. David et al. [56] identified three habitual movement patterns in a cohort of 50 participants; a rearfoot strike, a forefoot strike with a clear impact peak and a “true” forefoot strike with no impact peak suggested to be resultant of pre-orientation of the body. Rearfoot striking resulted in greater KJLs than both habitual forefoot striking conditions (Table 6). Within the forefoot conditions, a pre-rotated trunk and backwards leaning resulted in lower knee loading than the other forefoot striking condition that was deemed to generate a KAM similar to that of a heel strike with an impact peak. This again emphasises the multi-segmental mechanism to which KJLs are generated.

From the above, it is recommended that a neutral foot progression angle is adopted when cutting to prevent any knee abduction or internal rotation of the tibia, which would elevate KJLs. Modification of foot-strike pattern may be useful, whereby adopting a more forefoot orientated “ankle dominant” strategy when cutting will reduce load and power absorption through the knee. This could have implications for the ankle joint, as forefoot striking has been reported to elicit considerable strain [73] and eccentric load [74] on the triceps surae muscle- tendon complex when running. During cutting, this would be amplified further by the large deceleration component present [33] and require substantial force production from the triceps to meet the demands of the task. Without sufficient strength present, this would elevate the risk of acute muscle strain injury. Foot-strike modification is not something yet to be observed in injury prevention programmes and further research is recommended to investigate if this would be beneficial in reducing knee joint loads in athletic populations without overloading the ankle joint.

GRF, Penultimate Foot Contact and Braking Strategy

Despite the numerous biomechanical determinants that have been mentioned above, and their influential role in the modulation of KJLs, it must be noticed that these predominantly affect the lever arm of the moment. This either shifts the GRF orientation or knee position respective to such, resulting in a more medial, compromised dynamic valgus position of the knee relative to the GRF. Although the lever arm to which a moment operates about is significantly contributory to the resultant moment, it is also noteworthy that the orientation and magnitude of the GRFs in the penultimate and turning steps can influence KJLs.

In theory, a greater GRF that is generated during the foot contact initiating the turn would result in a greater KJL, due to the magnitude of the force generated, subsequently amplified by the respective moment arm. Greater GRFs have been observed in greater angled cuts (> 45°) [37] and in cuts performed at greater velocities [38]. In theory, if the magnitude of GRF was lower during the final contact, the KJL generated would be substantially lower. If one were to dissipate the majority of momentum in the steps prior to turning through applying greater antero-posterior braking forces, there would be a reduction in velocity (deceleration) through the impulse-momentum relationship (Impulse = Δ Momentum), which would result in a reduced GRF generated during the turning step. This could be accomplished by a “large anterior placement of the foot relative to the COM and backward inclination of the trunk relative to planted foot” [58] in the preceding steps. Figure 2g exhibits sub-optimal and optimal braking strategy during cutting tasks.

Sigward et al. [53] identified significantly greater laterally directed GRFs being up to three times greater (Table 7) in a “high-risk” increased KAM group, in line with other findings [36]. This was attributed to contacting the ground differently with a more medial orientation of the foot (resulting in greater lateral forces due to Newton’s third law) and may explain the strong relationship identified with an increased foot progression angle being a determinant of greater KAMs (p = 0.04). Instead of creating laterally directed GRFs as means to complete the task, it may be more advisable for practitioners to encourage greater amounts of pre-orientation as elucidated by David et al. [57]. A greater amount of pelvic rotation and so called “pre-orientation” resulted in a more ankle dominant loading pattern in terms of power absorption and joint work done. This could also be facilitated during the penultimate foot contact (PFC) to reduce the re-directional requirements during the final foot contact (FFC). Whether such a strategy modulates KJLs remains to be seen, and further research is recommended to investigate this theory.

Table 7 Studies identifying GRFs, penultimate foot contact and braking strategy as contributory to KJLS

Jones et al. [36] observed a moderate relationship between medial GRF and lateral leg-plant distance (R = .59). This is likely due to the nature of the 90° cut used which encompasses a substantial redirection component in comparison with lower angled cuts [33]. When taking into account that lateral leg-plant distance was identified as a significant predictor of KAM (Table 7), it is possible that medial GRFs are contributory to the generation of greater KAMs that are typically seen in greater angled cuts [37, 75]. Vertical GRFs (vGRFs) have also exhibited established relationships with KAMs, due to the magnitude of the GRF being contributory to the resultant and final moment generated about the knee [37]. A greater vertical force component would be present in lower angled cuts [75] due to the absence of greater re-directional demands, and an ability to perform such a task with a greater approach velocity, and such an angle-velocity trade-off has been highlighted in a recent review [39].

GRFs applied in the steps prior to the final contact that initiates the direction change can be a determinant of KJLs. A rationale for examining the preceding foot contacts of a cut when taking into account typical contact times in cutting (0.319 ± 0.06 s [61]) has previously been identified [58], inferring deceleration occurs over a multitude of steps. This has been substantiated by research that has examined braking characteristics occurring in the preceding footsteps in cutting tasks [33, 36, 58, 60]. Havens and Sigward [33] subsequently found disproportionately greater braking present in 90° cuts compared to 45° cuts. Braking demands were accommodated across both foot contacts for the 45° cut, although the need to produce a greater medio-lateral impulse to meet the more mechanically challenging nature of the 90° cut required greater ground reaction impulse to be applied. This increased contact time in the final and braking impulse in the penultimate foot contact. This emphasises the importance of deceleration and braking in turns of a greater magnitude (≥ 60°). However, a limitation of the aforementioned study is that the relationship between braking and KAMs was not directly examined.

Jones et al. [58] investigated the potential efficacy of braking strategies whilst investigating the biomechanical determinants of cutting, through examining a ratio of peak horizontal (antero-posterior) GRFs between the penultimate and final foot contacts. No relationship was observed between this ratio and KAMs [36]. However, solely examining peak variables may not provide an in-depth analysis of the braking effect that occurs when dissipating momentum over a multitude of steps. The authors mentioned their failure to consider average horizontal braking force and impulse, which in turn would provide greater insight into braking in the penultimate step. A greater average horizontal braking force applied over the time of contact during the penultimate step would lead to a greater impulse applied to the ground, causing a reduction in forward momentum through the impulse-momentum relationship. Subsequently, average horizontal GRF during the penultimate contact (Table 7) explained large amounts of variance in cutting in a follow-up investigation [58]. Consequently, this provides a rationale for practitioners to encourage braking prior to the final contact to lessen the risk of generating high KJLs during cutting. Recently, McBurnie et al. [60] found no significant relationships between any penultimate foot contact variables including peak and average horizontal GRFs and ratios in a cohort of 33 sub-elite footballers. However, the shorter approach distances between the studies (5 m vs 10 m and 15 m) may substantiate such differences.

Little is known yet regarding the underpinning strength and biomechanical qualities that facilitate braking capacity. Furthermore, there has been little research examining the distinct differences in braking profiles across a range of cutting angles. Further research is recommended examining the effect of eccentric strength on braking capacity and profiles, and whether this could translate into a mitigation of KJLs in cutting tasks. Practitioners are advised to emphasise the importance of a neutral (straight) foot position when coaching cutting technique to their athletes. It also appears there is usefulness in examining braking strategies with view to reducing KJLs. This can be accomplished by emphasising braking in the steps prior to initiating the cut, through a large COM–COP distance, and backward lean of the trunk. Consequently, less momentum would have to be dissipated in the final contact prior to turning, reducing ground contact times and allowing the athlete to redirect and reaccelerate in a faster manner. It is therefore possible that interventions improving braking strategy may address the performance injury conflict previously identified [34] and that improving braking ability may also translate into enhanced performance, alongside ameliorating KJLs.


Based on the associative work regarding determinants of KJLs during cutting (“Discussion” section), a deterministic model has been created identifying the variables which amplify KAMs during 30°–110° cutting, potentially predisposing athletes to an increased risk of non-contact ACL injury (Fig. 3). It should be noted that insufficient evidence is available at the moment to provide technical models for CODs between 110° and 180°. These identified determinants influence the moment arm, GRF, or a combination of the two, therefore elevating KAMs; however, it appears that these biomechanical deficits are modifiable with appropriate training, feedback and conditioning [76,77,78]. Particularly, technical characteristics associated with safer side-stepping are as follows: reduced lateral foot-plant distances, thus lower hip abduction and orientating the foot closer to neutral with a mid-foot or forefoot placement strategy; minimising knee valgus and hip internal rotation angles and motion at IC and WA; avoiding and limiting lateral trunk flexion and attempt to maintain an upright trunk position or trunk lean into the intended direction; reducing the magnitude of GRF during WA in the plant foot, potentially by attenuation through increased knee flexion and emphasising a greater proportion of braking in the penultimate foot contact. The variables associated with increased KAMs support the commonly identified visual characteristics of ACL injuries including wide lateral foot plant with hip abduction, knee valgus and the trunk flexed and/or rotated towards the plant foot [2, 4,5,6,7, 79]; thus, strengthening the argument to avoid and limit these potentially hazardous alignments, motions and higher GRFs during rapid cuts. These determinants and biomechanical deficits can subsequently be used to identify athletes displaying “high-risk” patterns during screening and can also form the basis for ACL injury mitigation programmes. However, practitioners should be aware that some of the “high-risk” postures identified in this review are necessary for faster cutting performance (i.e. wide foot plant, decreased knee flexion); thus, practitioners should be conscious of the “performance injury conflict” when addressing certain high-risk postures, because athletes are unlikely to adopt “safer” movement strategies at the expense of faster performance. Appropriate strength and conditioning intervention to improve eccentric strength, and thus braking capacity, may offer the answer to this performance injury conflict, by concurrently reducing KJLs and performance times.

Fig. 3

A deterministic model identifying the variables which amplify KAMs during cutting 30°–110°

Availability of Data and Materials

Not applicable



Three dimensional


Anterior cruciate ligament


Change of direction


Centre of mass


Centre of pressure


Ground reaction force


Horizontal braking force


Initial contact


Knee flexion moment


Knee abduction moment/peak knee abduction moment


Knee extension moment


Knee internal rotation moment


Knee joint load


Penultimate foot contact


Weight acceptance


  1. 1.

    Faude O, Junge A, Kindermann W, Dvorak J. Injuries in female soccer players: a prospective study in the German national league. Am J Sports Med. 2005;33(11):1694–700.

    Article  Google Scholar 

  2. 2.

    Olsen OE, Myklebust G, Engebretsen L, Bahr R. Injury mechanisms for anterior cruciate ligament injuries in team handball: a systematic video analysis. Am J Sports Med. 2004;32(4):1002–12.

    Article  Google Scholar 

  3. 3.

    Joseph AM, Collins CL, Henke NM, Yard EE, Fields SK, Comstock RD. A multisport epidemiologic comparison of anterior cruciate ligament injuries in high school athletics. J Athl Train. 2013;48(6):810–7.

    Article  Google Scholar 

  4. 4.

    Boden BP, Torg JS, Knowles SB, Hewett TE. Video analysis of anterior cruciate ligament injury: abnormalities in hip and ankle kinematics. Am J Sports Med. 2009;37(2):252–9.

    Article  Google Scholar 

  5. 5.

    Johnston JT, Mandelbaum BR, Schub D, Rodeo SA, Matava MJ, Silvers-Granelli HJ, et al. Video analysis of anterior cruciate ligament tears in professional American football athletes. Am J Sports Med. 2018;46(4):862–8.

    Article  Google Scholar 

  6. 6.

    Krosshaug T, Nakamae A, Boden BP, Engebretsen L, Smith G, Slauterbeck JR, et al. Mechanisms of anterior cruciate ligament injury in basketball: video analysis of 39 cases. Am J Sports Med. 2007;35(3):359–67.

    Article  Google Scholar 

  7. 7.

    Montgomery C, Blackburn J, Withers D, Tierney G, Moran C, Simms C. Mechanisms of ACL injury in professional rugby union: a systematic video analysis of 36 cases. Br J Sports Med. 2018;52(15):994–1001.

    Article  Google Scholar 

  8. 8.

    Walden M, Krosshaug T, Bjorneboe J, Andersen TE, Faul O, Hagglund M. Three distinct mechanisms predominate in non-contact anterior cruciate ligament injuries in male professional football players: a systematic video analysis of 39 cases. Br J Sports Med. 2015;49(22):1452–60.

    Article  Google Scholar 

  9. 9.

    Griffin LY, Agel J, Albohm MJ, Arendt EA, Dick RW, Garrett WE, et al. Noncontact anterior cruciate ligament injuries: risk factors and prevention strategies. J Am Acad Orthop Surg. 2000;8(3):141–50.

    CAS  Article  Google Scholar 

  10. 10.

    Boden BP, Sheehan FT, Torg JS, Hewett TE. Noncontact anterior cruciate ligament injuries: mechanisms and risk factors. The Journal of the American Academy of Orthopaedic Surgeons. 2010;18(9):520–7.

    Article  Google Scholar 

  11. 11.

    Brooks JHM, Fuller CW, Kemp SPT, Reddin DB. Epidemiology of injuries in English professional rugby union: part 1 match injuries. British journal of sports medicine. 2005;39(10):757–66.

    CAS  Article  Google Scholar 

  12. 12.

    Shah VM, Andrews JR, Fleisig GS, McMichael CS, Lemak LJ. Return to play after anterior cruciate ligament reconstruction in National Football League athletes. Am J Sports Med. 2010;38(11):2233–9.

    Article  Google Scholar 

  13. 13.

    Shelbourne KD, Nitz P. Accelerated rehabilitation after anterior cruciate ligament reconstruction. Am J Sports Med. 1990;18(3):292–9.

    CAS  Article  Google Scholar 

  14. 14.

    Lohmander LS, Ostenberg A, Englund M, Roos H. High prevalence of knee osteoarthritis, pain, and functional limitations in female soccer players twelve years after anterior cruciate ligament injury. Arthritis Rheum. 2004;50(10):3145–52.

    CAS  Article  Google Scholar 

  15. 15.

    Lloyd DG, Buchanan TS. Strategies of muscular support of varus and valgus isometric loads at the human knee. J Biomech. 2001;34(10):1257–67.

    CAS  Article  Google Scholar 

  16. 16.

    Markolf KL, Burchfield DM, Shapiro MM, Shepard MF, Finerman GA, Slauterbeck JL. Combined knee loading states that generate high anterior cruciate ligament forces. J Orthop Res. 1995;13(6):930–5.

    CAS  Article  Google Scholar 

  17. 17.

    Bates NA, Nesbitt RJ, Shearn JT, Myer GD, Hewett TE. Knee abduction affects greater magnitude of change in ACL and MCL strains than matched internal tibial rotation in vitro. Clin Orthop Relat Res. 2017;475(10):2385–96.

    Article  Google Scholar 

  18. 18.

    Bates NA, Schilaty ND, Nagelli CV, Krych AJ, Hewett TE. Multiplanar loading of the knee and its influence on anterior cruciate ligament and medial collateral ligament strain during simulated landings and noncontact tears. Am J Sports Med. 2019;47(8):1844–53.

    Article  Google Scholar 

  19. 19.

    Shin CS, Chaudhari AM, Andriacchi TP. The influence of deceleration forces on ACL strain during single-leg landing: a simulation study. J Biomech. 2007;40(5):1145–52.

    Article  Google Scholar 

  20. 20.

    Shin CS, Chaudhari AM, Andriacchi TP. The effect of isolated valgus moments on ACL strain during single-leg landing: a simulation study. J Biomech. 2009;42(3):280–5.

    Article  Google Scholar 

  21. 21.

    Shin CS, Chaudhari AM, Andriacchi TP. Valgus plus internal rotation moments increase anterior cruciate ligament strain more than either alone. Med Sci Sports Exerc. 2011;43(8):1484–91.

    Article  Google Scholar 

  22. 22.

    McLean SG, Huang X, Su A, Van Den Bogert AJ. Sagittal plane biomechanics cannot injure the ACL during sidestep cutting. Clin Biomech (Bristol, Avon). 2004;19(8):828–38.

    Article  Google Scholar 

  23. 23.

    Levine JW, Kiapour AM, Quatman CE, Wordeman SC, Goel VK, Hewett TE, et al. Clinically relevant injury patterns after an anterior cruciate ligament injury provide insight into injury mechanisms. Am J Sports Med. 2013;41(2):385–95.

    Article  Google Scholar 

  24. 24.

    Quatman CE, Quatman-Yates CC, Hewett TE. A ‘plane’ explanation of anterior cruciate ligament injury mechanisms: a systematic review. Sports Med. 2010;40(9):729–46.

    Article  Google Scholar 

  25. 25.

    Jones PA, Herrington LC, Munro AG, Graham-Smith P. Is there a relationship between landing, cutting, and pivoting tasks in terms of the characteristics of dynamic valgus? Am J Sports Med. 2014;42(9):2095–102.

    Article  Google Scholar 

  26. 26.

    Nedergaard NJ, Dalbø S, Petersen SV, Zebis MK, Bencke J. Biomechanical and neuromuscular comparison of single-and multi-planar jump tests and a side-cutting maneuver: implications for ACL injury risk assessment. The Knee. 2019.

  27. 27.

    Sweeting AJ, Aughey RJ, Cormack SJ, Morgan S. Discovering frequently recurring movement sequences in team-sport athlete spatiotemporal data. J Sports Sci. 2017;35(24):2439–45.

    Article  Google Scholar 

  28. 28.

    Bloomfield J, Polman R, O'Donoghue P. Physical demands of different positions in FA Premier League soccer. J Sports Sci Med. 2007;6(1):63–70.

    Google Scholar 

  29. 29.

    Hewett TE, Torg JS, Boden BP. Video analysis of trunk and knee motion during non-contact anterior cruciate ligament injury in female athletes: lateral trunk and knee abduction motion are combined components of the injury mechanism. Br J Sports Med. 2009;43(6):417–22.

    CAS  Article  Google Scholar 

  30. 30.

    Hewett TE, Myer GD, Ford KR, Heidt RS Jr, Colosimo AJ, McLean SG, et al. Biomechanical measures of neuromuscular control and valgus loading of the knee predict anterior cruciate ligament injury risk in female athletes: a prospective study. Am J Sports Med. 2005;33(4):492–501.

    Article  Google Scholar 

  31. 31.

    Dempsey AR, Lloyd DG, Elliott BC, Steele JR, Munro BJ. Changing sidestep cutting technique reduces knee valgus loading. Am J Sports Med. 2009;37(11):2194–200.

    Article  Google Scholar 

  32. 32.

    Havens KL, Sigward SM. Joint and segmental mechanics differ between cutting maneuvers in skilled athletes. Gait Posture. 2015;41(1):33–8.

    Article  Google Scholar 

  33. 33.

    Havens KL, Sigward SM. Whole body mechanics differ among running and cutting maneuvers in skilled athletes. Gait Posture. 2015;42(3):240–5.

    Article  Google Scholar 

  34. 34.

    Havens KL, Sigward SM. Cutting mechanics: relation to performance and anterior cruciate ligament injury risk. Med Sci Sports Exerc. 2015;47(4):818–24.

    Article  Google Scholar 

  35. 35.

    Jamison ST, Pan X, Chaudhari AM. Knee moments during run-to-cut maneuvers are associated with lateral trunk positioning. J Biomech. 2012;45(11):1881–5.

    Article  Google Scholar 

  36. 36.

    Jones PA, Herrington LC, Graham-Smith P. Technique determinants of knee joint loads during cutting in female soccer players. Hum Mov Sci. 2015;42:203–11.

  37. 37.

    Sigward SM, Cesar GM, Havens KL. Predictors of frontal plane knee moments during side-step cutting to 45 and 110 degrees in men and women: implications for anterior cruciate ligament injury. Clin J Sport Med. 2015;25(6):529–34.

    Google Scholar 

  38. 38.

    Vanrenterghem J, Venables E, Pataky T, Robinson MA. The effect of running speed on knee mechanical loading in females during side cutting. J Biomech. 2012;45(14):2444–9.

    Article  Google Scholar 

  39. 39.

    Dos’Santos T, Thomas C, Comfort P, Jones PA. The effect of angle and velocity on change of direction biomechanics: an angle-velocity trade-off. Sports Medicine. 2018;48(10):2235–53.

    Article  Google Scholar 

  40. 40.

    Jamison ST, McNeilan RJ, Young GS, Givens DL, Best TM, Chaudhari AM. Randomized controlled trial of the effects of a trunk stabilization program on trunk control and knee loading. Med Sci Sports Exerc. 2012;44(10):1924–34.

    Article  Google Scholar 

  41. 41.

    Weltin E, Gollhofer A, Mornieux G. Effects of perturbation or plyometric training on core control and knee joint loading in women during lateral movements. Scand J Med Sci Sports. 2017;27(3):299–308.

    CAS  Article  Google Scholar 

  42. 42.

    Fox AS. Change-of-direction biomechanics: is what’s best for anterior cruciate ligament injury prevention also best for performance? Sports Medicine. 2018;48(8):1799–807.

    Article  Google Scholar 

  43. 43.

    Hughes G. A review of recent perspectives on biomechanical risk factors associated with anterior cruciate ligament injury. Research in sports medicine. 2014;22(2):193–212.

    Article  Google Scholar 

  44. 44.

    Moher D, Liberati A, Tetzlaff J, Altman DG. Preferred reporting items for systematic reviews and meta-analyses: the PRISMA statement. PLoS Med. 2009;6(7):e1000097.

    Article  Google Scholar 

  45. 45.

    Dos'Santos T, Bishop C, Thomas C, Comfort P, Jones PA. The effect of limb dominance on change of direction biomechanics: a systematic review of its importance for injury risk. Phys Ther Sport. 2019;37:179–89.

    Article  Google Scholar 

  46. 46.

    Brown SR, Brughelli M, Hume PA. Knee mechanics during planned and unplanned sidestepping: a systematic review and meta-analysis. Sports Med. 2014;44(11):1573–88.

    Article  Google Scholar 

  47. 47.

    Cortes N, Morrison S, Van Lunen BL, Onate JA. Landing technique affects knee loading and position during athletic tasks. J Sci Med Sport. 2012;15(2):175–81.

    Article  Google Scholar 

  48. 48.

    Dempsey AR, Lloyd DG, Elliott BC, Steele JR, Munro BJ, Russo KA. The effect of technique change on knee loads during sidestep cutting. Med Sci Sports Exerc. 2007;39(10):1765–73.

    Article  Google Scholar 

  49. 49.

    Donnelly CJ, Chinnasee C, Weir G, Sasimontonkul S, Alderson J. Joint dynamics of rear- and fore-foot unplanned sidestepping. J Sci Med Sport. 2017;20(1):32–7.

    Article  Google Scholar 

  50. 50.

    Jamison ST, McNally MP, Schmitt LC, Chaudhari AM. The effects of core muscle activation on dynamic trunk position and knee abduction moments: implications for ACL injury. J Biomech. 2013;46(13):2236–41.

    Article  Google Scholar 

  51. 51.

    McLean SG, Huang X, van den Bogert AJ. Association between lower extremity posture at contact and peak knee valgus moment during sidestepping: implications for ACL injury. Clin Biomech (Bristol, Avon). 2005;20(8):863–S.

    Article  Google Scholar 

  52. 52.

    Mornieux G, Gehring D, Furst P, Gollhofer A. Anticipatory postural adjustments during cutting manoeuvres in football and their consequences for knee injury risk. J Sports Sci. 2014;32(13):1255–62.

    Article  Google Scholar 

  53. 53.

    Sigward SM, Powers CM. Loading characteristics of females exhibiting excessive valgus moments during cutting. Clin Biomech (Bristol, Avon). 2007;22(7):827–33.

    Article  Google Scholar 

  54. 54.

    Weir G, Alderson J, Smailes N, Elliott B, Donnelly C. A reliable video-based ACL injury screening tool for female team sport athletes. Int J Sports Med. 2019;40(3):191–9.

    Article  Google Scholar 

  55. 55.

    Chaudhari AM, Hearn BK, Andriacchi TP. Sport-dependent variations in arm position during single-limb landing influence knee loading: implications for anterior cruciate ligament injury. Am J Sports Med. 2005;33(6):824–30.

    Article  Google Scholar 

  56. 56.

    David S, Komnik I, Peters M, Funken J, Potthast W. Identification and risk estimation of movement strategies during cutting maneuvers. J Sci Med Sport. 2017;20(12):1075–80.

    Article  Google Scholar 

  57. 57.

    David S, Mundt M, Komnik I, Potthast W. Understanding cutting maneuvers - the mechanical consequence of preparatory strategies and foot strike pattern. Hum Mov Sci. 2018;62:202–10.

    Article  Google Scholar 

  58. 58.

    Jones PA, Herrington L, Graham-Smith P. Braking characteristics during cutting and pivoting in female soccer players. J Electromyogr Kinesiol. 2016 Oct;30:46–54.

    Article  Google Scholar 

  59. 59.

    Fedie R, Carlstedt K, Willson JD, Kernozek TW. Effect of attending to a ball during a side-cut maneuver on lower extremity biomechanics in male and female athletes. Sports Biomech. 2010;9(3):165–77.

    Article  Google Scholar 

  60. 60.

    McBurnie AJ, Dos'Santos T, Jones PA. Biomechanical associates of performance and knee joint loads during a 70-90 degrees cutting maneuver in subelite soccer players. J Strength Cond Res. 2019.

  61. 61.

    Kristianslund E, Faul O, Bahr R, Myklebust G, Krosshaug T. Sidestep cutting technique and knee abduction loading: implications for ACL prevention exercises. Br J Sports Med. 2014;48(9):779–83.

    Article  Google Scholar 

  62. 62.

    Mornieux G, Gehring D, Fürst P, Gollhofer A. Anticipatory postural adjustments during cutting manoeuvres in football and their consequences for knee injury risk. Journal of sports sciences. 2014;32(13):1255–62.

    Article  Google Scholar 

  63. 63.

    Kristianslund E, Krosshaug T, Mok KM, McLean S, van den Bogert AJ. Expressing the joint moments of drop jumps and sidestep cutting in different reference frames--does it matter? J Biomech. 2014;47(1):193–9.

    Article  Google Scholar 

  64. 64.

    Jones PA, Herrington LC, Graham-Smith P. Technique determinants of knee abduction moments during pivoting in female soccer players. Clin Biomech (Bristol, Avon). 2016;31:107–12.

    Article  Google Scholar 

  65. 65.

    Dos Santos T, Thomas C, Jones PA, Comfort P. Mechanical determinants of faster change of direction speed performance in male athletes. J Strength Conditioning Res. 2017;31(3):696–705.

    Article  Google Scholar 

  66. 66.

    Jones PA, Dos Santos T, JJ MM, Graham-Smith P. Contribution of eccentric strength to cutting performance in female soccer players. J Strength Conditioning Res. 2019.

  67. 67.

    Hashemi J, Breighner R, Chandrashekar N, Hardy DM, Chaudhari AM, Shultz SJ, et al. Hip extension, knee flexion paradox: a new mechanism for non-contact ACL injury. Journal of biomechanics. 2011;44(4):577–85.

    Article  Google Scholar 

  68. 68.

    Ford KR, Myer GD, Toms HE, Hewett TE. Gender differences in the kinematics of unanticipated cutting in young athletes. Med Sci Sports Exerc. 2005 Jan;37(1):124–9.

    Article  Google Scholar 

  69. 69.

    Loudon JK, Jenkins W, Loudon KL. The relationship between static posture and ACL injury in female athletes. J Orthopaedic Sports Physical Therapy. 1996;24(2):91–7.

    CAS  Article  Google Scholar 

  70. 70.

    Nyland J, Caborn D, Shapiro R, Johnson D, Fang H. Hamstring extensibility and transverse plane knee control relationship in athletic women. Knee Surgery Sports Traumatology Arthroscopy. 1999;7(4):257–61.

    CAS  Article  Google Scholar 

  71. 71.

    Kulmala JP, Avela J, Pasanen K, Parkkari J. Forefoot strikers exhibit lower running-induced knee loading than rearfoot strikers. Med Sci Sports Exerc. 2013 Dec;45(12):2306–13.

    Article  Google Scholar 

  72. 72.

    Stearne S, Alderson J, Green B. Redistribution of joint mechanical work and power in rear-vs forefoot strike running. Med Sci Sports Exerc. 2014;26(8):1578–87.

    Article  Google Scholar 

  73. 73.

    Lyght M, Nockerts M, Kernozek TW, Ragan R. Effects of foot strike and step frequency on Achilles tendon stress during running. J Appl Biomechanics. 2016;32(4):365–72.

    Article  Google Scholar 

  74. 74.

    Yong JR, Dembia CL, Silder A, Jackson RW, Fredericson M, Delp SL. Foot strike pattern during running alters muscle-tendon dynamics of the gastrocnemius and the soleus. Sci Rep. 2020;10(1):5872 2020/04/03.

    CAS  Article  Google Scholar 

  75. 75.

    Schreurs MJ, Benjaminse A, Lemmink K. Sharper angle, higher risk? The effect of cutting angle on knee mechanics in invasion sport athletes. J Biomech. 2017;63:144–50.

    Article  Google Scholar 

  76. 76.

    Dos’Santos T, Thomas C, Comfort P, Jones PA. The effect of training interventions on change of direction biomechanics associated with increased anterior cruciate ligament loading: a scoping review. Sports Medicine. 2019;49(12):1837–59.

    Article  Google Scholar 

  77. 77.

    Whyte EF, Richter C, O'Connor S, Moran KA. Effects of a dynamic core stability program on the biomechanics of cutting maneuvers: a randomized controlled trial. Scand J Med Scie Sports. 2018;28(2):452–462.

  78. 78.

    Pappas E, Nightingale EJ, Simic M, Ford KR, Hewett TE, Myer GD. Do exercises used in injury prevention programmes modify cutting task biomechanics? A systematic review with meta-analysis. Br J Sports Med. 2015;49(10):673–80.

    Article  Google Scholar 

  79. 79.

    Cochrane JL, Lloyd DG, Buttfield A, Seward H, McGivern J. Characteristics of anterior cruciate ligament injuries in Australian football. J Sci Med Sport. 2007 Apr;10(2):96–104.

    Article  Google Scholar 

  80. 80.

    McNutt MK, Bradford M, Drazen JM, Hanson B, Howard B, Jamieson KH, et al. Transparency in authors’ contributions and responsibilities to promote integrity in scientific publication. Proceedings Nat Acad Sci. 2018;115(11):2557–60.

    CAS  Article  Google Scholar 

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All authors have made substantial contributions to the conception, drafting and writing of this work as per the adapted regulations of McNutt et al [80], approved the submitted version and take accountability for their personal contributions.

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TD is a PhD candidate in Sports Biomechanics at Canterbury Christ Church University.

TDS is a lecturer in Strength and Conditioning at Manchester Metropolitan University.

GP is a PhD candidate in Strength and Conditioning at Canterbury Christ Church University.

PJ is a lecturer in Sports Biomechanics and Strength and Conditioning at the University of Salford.

MB is a senior lecturer in Sports Biomechanics at Canterbury Christ Church University.

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Correspondence to Thomas A. Donelon.

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The authors, Thomas Donelon, Thomas Dos'Santos, Guy Pitchers, Mathew Brown, and Paul Jones, declare that they have no competing interests.

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Donelon, T.A., Dos’Santos, T., Pitchers, G. et al. Biomechanical Determinants of Knee Joint Loads Associated with Increased Anterior Cruciate Ligament Loading During Cutting: A Systematic Review and Technical Framework. Sports Med - Open 6, 53 (2020).

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  • ACL
  • Knee joint loads
  • Sidestepping
  • Technical Framework
  • Injury-Performance Conflict