- Research article
- Open Access
Exploring the role of transtibial prosthetic use in deep tissue injury development: a scoping review
BMC Biomedical Engineering volume 2, Article number: 2 (2020)
The soft tissue of the residual limb in transtibial prosthetic users encounters unique biomechanical challenges. Although not intended to tolerate high loads and deformation, it becomes a weight-bearing structure within the residuum-prosthesis-complex. Consequently, deep soft tissue layers may be damaged, resulting in Deep Tissue Injury (DTI). Whilst considerable effort has gone into DTI research on immobilised individuals, only little is known about the aetiology and population-specific risk factors in amputees. This scoping review maps out and critically appraises existing research on DTI in lower-limb prosthetic users according to (1) the population-specific aetiology, (2) risk factors, and (3) methodologies to investigate both.
A systematic search within the databases Pubmed, Ovid Excerpta Medica, and Scopus identified 16 English-language studies. The results indicate that prosthetic users may be at risk for DTI during various loading scenarios. This is influenced by individual surgical, morphological, and physiological determinants, as well as the choice of prosthetic componentry. However, methodological limitations, high inter-patient variability, and small sample sizes complicate the interpretation of outcome measures. Additionally, fundamental research on cell and tissue reactions to dynamic loading and on prosthesis-induced alterations of the vascular and lymphatic supply is missing.
We therefore recommend increased interdisciplinary research endeavours with a focus on prosthesis-related experimental design to widen our understanding of DTI. The results have the potential to initiate much-needed clinical advances in surgical and prosthetic practice and inform future pressure ulcer classifications and guidelines.
Pressure injuries frequently affect individuals in hospitals, homes, and care settings. They are defined as “localised damage to the skin and underlying soft tissue”, and are caused by “intense and/or prolonged pressure or pressure in combination with shear” . The severity of this damage can range from superficial, skin bound deteriorations, to full thickness tissue loss. Whilst severely impairing the well-being of affected patients, pressure injuries also pose a tremendous burden on the health care system. In the UK, the estimated cost for pressure ulcer management amounts to £ 507–531 million p.a ..
This high number reflects the shortfalls in the prevention, diagnosis, and treatment of pressure injuries, which may be ascribed to ambiguities about their aetiology . An example for ongoing controversies is the recent addition of Deep Tissue Injuries (DTI) to the established pressure ulcer staging system of the National Pressure Ulcer Advisory Panel (NPUAP) . It has long been the prevailing opinion that pressure injuries originate at superficial layers and may evolve into deeper tissues . Accordingly, the NPUAP defined pressure injury stages based on their visual appearance from 1, representing superficial damage, to 4, describing full depth tissue loss . However, an increasing body of literature supports the theory of an opposite route of development [4, 6,7,8,9]: Researchers now believe that most pressure-related damage initiates in deep tissues at the bone-muscle interface, from where it may progress towards superficial layers in a bottom-up pathogenesis [10, 11]. Based on its origin, this type of injury is classified as DTI.
The aetiology of DTI is affiliated with a variety of biomechanical, physiological, and biochemical processes on cell and tissue level [7, 12]. In brief, four mechanisms of injury have been postulated to date:
Direct deformation can disrupt the integrity of skeletal muscle cells if the applied load is sufficiently high or prolonged.
Ischemia is caused by a collapse of blood vessels, which obstructs the blood flow and therefore the cells’ oxygen and nutrient supply.
Ischemia reperfusion describes the phase following load removal, where the reoxygenation of the tissue exacerbates ischemic damage, mainly due to oxidative stress.
Impaired lymphatic drainage is induced by obstructed lymphatic vessels, which inhibits the removal of potentially damaging substances from the interstitial space and creates a toxic cell environment.
All these mechanisms contribute to the onset of inflammatory cascades and ultimately cell death. In healthy individuals the cellular damage is usually balanced out by regenerative processes. For certain populations, however, this equilibrium between stress-induced damage and recovery may be disturbed. Accordingly, researchers defined several internal and external determinants of DTI development for a number of risk groups like patients with spinal cord injury (SCI) and wheelchair users [13,14,15,16,17,18,19].
Conversely, other populations such as transtibial amputees have gained less attention. During an amputation surgery, foot, ankle joint, and distal tibia and fibula are removed. To restore the capabilities of the amputee, a prosthesis is fitted to the residuum, which transfers forces between the ground and the body’s support structures during ambulation. The soft tissues that cover the stump become part of this load bearing system, even though they are not physiologically adapted to withstand high external forces. Consequently occurring skin problems, pain, and ulceration can lead to rejection of the prosthesis [20,21,22,23].
Whilst the prevalence and incidence of superficial wounds is well documented [20, 22], only few case studies have recorded DTI occurrence [24, 25]. A lack of knowledge, ambiguities in classification, and the absence of established reporting procedures  may play into this. To provide a basis for much-needed advances in the prevention, diagnosis, and treatment of DTI, a better understanding of the underlying aetiology and risk factors is necessary.
We therefore aim to map out and critically discuss research on DTI in transtibial amputees as a result of prosthetic use. Our focus is on (1) the population specific aetiology, (2) risk factors, and (3) methodologies to quantify and measure both. Because randomised controlled trials are sparse in rehabilitation science , we chose to conduct a scoping review. The systematic approach allowed for the assessment of the nature and extent of various types of research and to identify gaps in the literature. We hope that connecting the multifaceted challenges of transtibial prosthetic users with the aetiology of DTI will provide the basis for future research in this area. Additionally, our results could inform prospective policies, guidelines, risk assessment tools, and international classifications.
Search results and grouping
The automated database search on the 14th of June 2019 resulted in 19 identified sources from Ovid Excerpta Medica, 12 from PubMed, and 68 from Scopus. Removal of duplicates left 72 articles for the screening process. After applying inclusion and exclusion criteria, 24 articles remained for full-text assessment, of which 11 met the eligibility criteria. An additional 5 articles were identified through references and forward-citation of these sources, amounting to 16 studies in total (Fig. 1).
The 16 identified articles covered a variety of study types. Eleven of them presented primary research, of which seven examined human subjects experimentally [28,29,30,31,32,33,34] and one tested ex vivo animal tissue . Three papers were in silico studies [36,37,38]. The other five sources were secondary articles in the form of literature [9, 26, 39, 40] or systematic reviews . They were all thematically grouped by research focus into the following categories (Fig. 2):
DTI aetiology in transtibial prosthetic users
Risk factors for transtibial prosthetic users
Methodological approaches to measure aetiological and risk factors in transtibial prosthetic users
Of the 16 articles, 44% (7) discussed the aetiology of DTI, focussing mainly on residuum biomechanics. Between 2007 and 2011, Portnoy and colleagues conducted four experimental studies [29, 31, 33, 34] on a total of 26, unilateral, transtibial amputees. The participants were typically 44 years old, male (85%), weighted 71.72 kg, and presented with trauma as cause of amputation (59%) (Table 1). The researchers aimed to quantify the internal loading states of deep muscle layers during scenarios encountered by prosthetic users in their daily life: Dynamic walking on various surfaces [29, 31], static weight bearing during standing , and prolonged sitting .
Across all these scenarios, the researchers located peak loads at the distal end of the bones [29, 31, 33, 34]. During normal gait, the peak was reached between midstance and toe off , and its magnitude appeared to be terrain-dependent . When sitting with a donned prosthesis, the load increased simultaneously to the degree of knee flexion . However, high inter-patient variability made the interpretation of absolute values difficult . Portnoy et al. therefore compared individual stress and strain values to loading-thresholds for deformation-induced cell death to assess the risk for DTI development [18, 42, 43]. They hereby surmised hazardous loading conditions during weight bearing , walking over complex terrain , and sitting with the knee in 90 degree flexion . Overall, DTI appeared to be a threat for several transtibial prosthetic users in everyday situations.
Cellular deformation is only one of several aetiological factors of DTI. Mak et al. [9, 40] and Bader et al.  suspected a link between prosthetic use and disruptions of the lymphatic and microvascular system (Table 2). When externally applied pressure and shear deforms the deep tissues of a residuum [29,30,31, 33], the embedded lymphatic and vascular structures will be distorted as well. However, the extent of this deformation and its consequences have not been investigated on transtibial amputees.
A total of 68.75% (11) of the identified literature examined risk factors of DTI in transtibial prosthetic users. The population investigated in three experimental and two in silico studies amounts to 33, typically male (90.90%), transtibial amputees with traumatic amputation (84.84%), a mean age of 49 years, and an average weight of 81.1 kg. These studies, together with an additional in silico study and five review papers, were divided by non-prosthesis induced (63.63%, 7) and prosthesis-induced (54.54%, 6) risk factors.
Non-prosthesis induced risk factors
Non-prosthesis induced risk factors originate from intrinsic characteristics of the transtibial residuum. According to the literature body, those factors are tissue morphology, the mechanical properties of the soft tissue, and sensory impairments (Table 3).
Tissue morphology was the most frequently investigated determinant. Henrot et al.  and Portnoy et al. [30, 36, 37] focussed on surgery-related and pathological changes in tissue morphology. They identified the following risk factors: Thin muscle flaps [36, 37], minimal adipose tissue padding , sharp bone edges [30, 36, 39], and osteophytes [36, 39]. Results on the influence of the bone radius were ambiguous. A numerical in silico study indicated that the soft tissue load is reduced with wider bone radii , whilst an analytical study found no relationship between the two .
The effect of sensory impairment was discussed by three papers. According to reviews [26, 40] the loss of sensation, as it is commonly seen during diabetes, causes a dysfunction of the natural protective pain mechanism to redistribute excessive loads. Kosasih et al.  suspected that sensory changes could also result from the amputation process. However, contrary to their expectations, deep pressure sensation of their test subjects seemed to be intact.
The mechanical properties of soft tissue were examined in two in silico studies. Both indicate a higher susceptibility of stiff muscle to loading damage compared to a flaccid one [36, 37]. This stiffening might be the result of muscle contraction during normal gait [36, 37] or pathological changes like spasticity . Portnoy et al.  also suggest that surgical scars change the stress distribution across the residuum. The lower elasticity of fibrous scar tissue may put the surrounding muscle at risk of DTI development.
Prosthesis induced risk factors
The prosthesis itself also influences the development of DTI in transtibial amputees. Relevant factors are socket design and prosthetic components (Table 4). The most abundantly discussed prosthetic element was the socket (4). It distributes pressure and shear forces across the limb during weight-bearing [9, 26, 40]. Based on two fundamentally different socket design philosophies, these loads may either be concentrated on proclaimed tolerant areas (Patellar Tendon Bearing (PTB)), or spread as evenly as possible over the entire residuum (Total Surface Bearing (TSB)) [9, 40]. Whilst differences in interface loads between both design approaches have been found [40, 41], the internal loading conditions have yet to be quantified [26, 40, 41].
Two papers on prosthesis induced risk factors addressed components other than the prosthetic socket. Across two experimental studies, a total of 18 traumatic, mainly male (94%) and unilateral (94%) amputees with an average age of 49.8 years and weight of 85 kg participated. Researchers thereby investigated the influence of prosthetic foot design  as well as gel liners and socks  on the internal loading states. Hydraulic and split-toed feet seemed to improve loading conditions in comparison to energy storage and return (ESR) and single-toe feet. Furthermore, the use of gel liners, especially stiff and thin ones, appeared to provide a positive cushioning effect. In contrast, the common practice of adding socks over the liner to accommodate volume fluctuations of the stump was predicted to increase interface shear, which may adversely affect deeper tissues.
All experimental and in silico studies (11) were included in an overview of methodologies in DTI research on transtibial prosthetic users. The studies were grouped by methodological approaches, namely finite element (FE) analysis, analytical modelling, acoustic signalling, and sensory analysis.
Finite element analysis
FE analysis is based on computational models of the residuum with defined geometries, material properties, and boundary conditions. These models are numerically analysed to create visual stress and strain maps. With 54.54% (6), FE analysis constitutes the most common methodology in primary research (Table 5). The studies can be divided into three groups: individualised biomechanical models for aetiological research [30, 33, 34], in silico studies for parametric analysis of risk factors [36, 38], and real-time FE for clinical applications .
When investigating residuum biomechanics for aetiological research, individualisation and high accuracy are key . Accordingly, researchers obtained subject-specific morphological and loading data from MRIs and interface pressure sensors. Certain aspects of mechanical properties of soft tissue were also integrated into the analyses, for example viscoelasticity  or hyperelasticity [30, 33]. Others, like heterogeneity and anisotropy were disregarded. The resulting computed stress and strain levels were compared to threshold values for deformation-induced cell death to determine the subject-specific DTI risk [30, 33]. For further refinement, damage progression was predicted by iterative post-processing , which incorporated muscle stiffening following the initial damage .
For risk factor research, in silico modelling is an important tool. By changing single input parameters of an FE model, their effect on internal loading conditions can be tested. Portnoy et al.  produced an FE model, following the process described above, before altering bone geometry, mechanical properties of the muscle, and tissue homogeneity. Lenz  simulated the use of different liners and liner-socket interface conditions in a slightly different way. Instead of representing a full residuum, she reduced her FE model to a cuboid shape with soft tissue thicknesses taken from literature. The loading conditions were recorded with a two-axis load cell, rather than pressure sensors, and with motion capture data of liner displacements during gait.
To translate these complex models into clinical use, real-time availability of information is desirable. Thus, Portnoy et al.  proposed an X-Ray based FE model of the residual limb, with interface pressure measurements and patient-specific elastic moduli feeding into it. Rendering bones as rectangles and assuming linear elasticity, isotropy, and homogeneity was accepted as trade-off between accuracy and computing time.
Overall, FE analysis is a common tool in biomechanical research of DTI development. It provides full field information on the internal loading state of soft tissue and allows to assess the influence of single risk factors. The model complexity, input, and output data vary widely across the different studies.
For clinical applications, two-dimensional analytical solutions, as utilised in three primary studies [29, 31, 32], are an alternative to FE analysis (Table 6). The models evaluate the internal loading state of the residuum mathematically, based on simplified tissue geometries and mechanical behaviour. The first approach developed by Portnoy et al.  calculated the contact pressure between bone and soft tissue based on Hertz contact theory. Despite being validated in silico, this model was to the authors’ knowledge never translated to experimental research.
Instead, Portnoy et al. utilised a similar model  in their experimental studies [31, 32]. The bone was assumed as an axisymmetric, flat indenter, which compresses a linear elastic soft tissue layer. Individual interface pressure measurements and X-Rays in combination with literature-based values for tissue material properties and boundary conditions provided data on the essential variables. This allowed for a real-time estimation of internal loading states.
Following the idea of direct deformation as major aetiological factor, Buis et al.  attempted to find ways other than imaging to measure tissue distortion (Table 7). The idea was that deformation would create acoustic signals. In an ex vivo experimental study, they subjected porcine and galline tissue immersed in a saline bath to tensile stress whilst recording acoustic emissions with a hydrophone. However, they were unable to detect sufficient acoustic signals to support their hypothesis.
The only primary study that was not biomechanics related was an experimental study on sensory changes in transtibial prosthetic users  (Table 7). A physician applied light touch, deep pressure, vibration, and pin pricks to the residuum as well as the sound limb of participants. The resulting sensory perception for each stimulus was evaluated via qualitative feedback.
In this scope review we identified research and literature on DTI as a result of transtibial prosthetic use. We addressed three key areas: Firstly, the aetiology of DTI in prosthetic users is only partially understood. Whilst direct deformation seems to be an important factor, the contribution of ischemia, ischemia reperfusion, and an impaired lymphatic drainage has yet to be evaluated. Secondly, we identified several risk factors. Intrinsic determinants of DTI damage are tissue morphology and its mechanical properties, as well as sensory impairment of the residuum. Extrinsic determinants are socket design and prosthetic components. Finally, we found that methodological approaches in both aetiological and risk factor research focussed mainly on biomechanics. The most common research design combined static or dynamic loading with medical imaging and computational analysis. However, the diversity of input data, modelling assumptions, and outcome measures, together with the variability in geometrical patient characteristics and prosthetic components make a quantitative comparison of results and their clinical translation difficult.
Within the last two decades, major research efforts led to advancements in our understanding of DTI. The pathways of tissue damage from external loading were investigated on different organisational levels, from cell cultures over engineered muscle constructs to in vivo animal studies [7, 46]. The results indicate that the relationship between the degree of deformation and time is essential: Whilst high strain can cause immediate direct deformation damage, moderate strain may injure the tissue by occluding the vascular and lymphatic system over a longer period.
Loading biomechanics and direct deformation
The biomechanical profile at the stump-socket interface of lower-limb amputees differs significantly from the frequently studied immobile individuals [15, 16, 18, 47,48,49,50,51]. Prolonged loading is only seen in situations of static weight bearing like standing or sitting with a donned prosthesis. In contrast, with over 8000 steps taken daily by transtibial amputees , the residuum often experiences dynamic, cyclic loading. During gait, complex internal stresses and strains develop: weight bearing causes pressure at the socket-limb interface ; the vertical pistoning movement between the residuum and the socket invokes shear forces ; and gait action and bone movement lead to the development of additional forces and moments [55, 56]. The combination of these forces and moments results in internal compressive, tensile, and shear stress . However, the individual contribution of each stress component to the development of DTI is difficult to quantify.
So far, DTI research focussed mainly on compressive loading. Researchers have defined threshold levels for direct deformation damage, based on the relationship between pressure or compressive strain, and time [42, 43]. Subsequently, they compared these thresholds to computed values of internal compressive stress and strain in prosthetic patients to predict the likelihood of DTI development [30, 31, 33]. However, the results of these studies must be interpreted with caution.
Firstly, the threshold levels were deducted from experiments on animal tissue and bioartificial muscle constructs, and not intended to be translated directly to human studies [42, 43]. Secondly, the experimental design of threshold studies was oriented towards measuring direct deformation damage, whilst the microvascular and lymphatic system were mostly neglected. And lastly, the application of a static, compressive load differs from residuum biomechanics. Researchers showed that a cyclic force application may reduce the static threshold levels [40, 51, 58, 59], implying that the predicted risk of DTI in transtibial amputees has been underestimated. The addition of a shear component might also induce a greater damage potential by reducing the capillary closure pressure, which in turn increases the risk for ischemia [60, 61].
To minimise these limitations, new research approaches are needed. The effects of shear and distortion on tissues and cells should be examined with mechanical, microvascular, and lymphatic damage in mind. Additionally, researchers repeatedly stressed the need for a dynamic threshold level that combines compression, tension, and shear [29, 30, 33]. For this reason, our research group is working on investigating tissue response to a cyclic loading protocol under a variety of loading conditions that represent transtibial prosthetic use. This will allow for a better interpretation of existing data on internal loading conditions and contribute to the knowledge of DTI development.
Microvasculature and the lymphatic system
Our review revealed a gap in the aetiological research. Whilst the connection between deformation damage and prosthetic use has been established experimentally, the role of microvasculature and the lymphatic system was only discussed in general review papers.
Regarding the vascular system, the effects of a cyclic loading protocol with ischemic and reperfusion phases altering at high frequencies are unknown. The literature on similar loading scenarios is ambiguous: Some experimental results indicate an accumulation of cellular and tissue damage in comparison to continuous loading. However, the studies were either based on animal skin [58, 59, 62] or used prolonged time intervals [50, 51]; these were far below frequencies of about 1 Hz commonly seen during prosthetic gait [31, 63]. Other studies report on the adaptive capabilities of soft tissue [64,65,66,67], which indicates an increased tissue tolerance towards ischemic and reperfusion damage .
The structure and function of the lymphatic system and its response to loading are barely understood. In general, compression in combination with shear stress may affect lymph formation and propulsion . The resulting dysfunction of lymphatic drainage can lead to an accumulation of toxic waste products, which damages cells and tissues [70, 71]. In the last decade, this theory was supported by a small number of studies. Researchers confirmed a reduction of lymphatic clearance during compressive loading , as well as toxic effects of accumulated bio-wastes on cell viability . Reperfusion seems to add additional stress on the lymphatic system . These factors might be aggravated in transtibial amputees. The initial amputation process causes traumatic injury to the lymphatic system [39, 75], followed by a reduced muscle tone post-amputation, which might reduce the propulsive capabilities of lymphatic vessels and results in oedema .
For a better understanding of the role of the vascular and lymphatic system in DTI development, the simulation of high-frequency cyclic loading protocols with perfused tissue will be necessary. Beside histological analysis of muscle damage in animal models, arterial spin labelling or dynamic contrast MRI could relate the damage to muscle perfusion and oxygenation . For clinically oriented studies, near-infrared (NIR) spectroscopy is potentially capable of evaluating the oxidative function of transtibial residua [78, 79]. The lymphatic system could be explored in a similar fashion by visualising lymph flow with NIR fluorescent imaging . Together with information from direct deformation studies, the results of microvascular and lymphatic experiments can feed into the prevention, diagnosis, and treatment of DTI.
Population-specific risk factors
Identifying population-specific characteristics that may have a negative influence on the soft tissue in amputees is equally as important as estimating internal loading states. We found a variety of risk factors that link transtibial prosthetic use to DTI development, as detailed in the following paragraphs.
Influence of tissue characteristics
Our review identified a range of tissue-related determinants of DTI risk. Firstly, tissue morphology and geometry change as a result of the surgical process. By revisiting established amputation procedures and considering alternatives, for example the use of bone bridges  instead of bevelled bone edges, or different flap techniques that change the location of surgical scars [81, 82], some of these risk factors might be avoidable.
On the other hand, naturally occurring risk factors are hard to eliminate. The residuum commonly undergoes changes of intramuscular fat infiltration and muscular atrophy post-amputation [65, 83], which were both shown to enhance internal tissue deformation in SCI patients . Additionally, amputees often experience complications after surgery like osteophytes or angular deformities [24, 25], which also have adverse effects on tissue loading [36, 39]. Overall, a multitude of amputation-related tissue characteristics aggravates the challenging loading conditions in transtibial amputees.
The role of co-morbidities
The main cause of transtibial amputation in the high-income countries is disvascularity. In the UK and the US, most patients suffer from diabetes and other peripheral vascular diseases [84,85,86]. This affects the perfusion of their residua, which facilitates ischemic damage and exacerbates inflammation. In diabetic patients, neuropathy is another common complication. The review papers we identified stressed that as the body’s protective pain mechanism is suspended, affected individuals may not distribute potentially damaging loads anymore [26, 40].
To validate this link between co-morbidities and DTI development in transtibial amputees, epidemiological studies would be beneficial. These studies also offer a chance to uncover possible correlations of other factors, such as time since amputation or age. Additionally, they could give an insight into the extent of the prevalence of DTI in transtibial amputees in general. The epidemiology of DTI in lower-income countries should also be investigated, as their amputation population profiles, surgical procedures, and prosthetic componentry differ significantly from high-income countries [86,87,88].
Prosthesis-related risk factors
Prosthetic sockets are in direct contact with the residuum. Hence, they are the component most frequently associated with DTI development. Researchers highlighted the influence of the socket shape on internal pressure distribution and soft tissue deformation [9, 40, 41]. However, studies that quantify differences in internal loading conditions between the two main socket designs PTB and TSB are missing. To close the gap, biomechanical and physiological studies could be conducted. This information would help to define good prosthetic fit and improve clinical practice.
Other prosthetic componentry like prosthetic feet and liners have also shown to influence the internal loading conditions [32, 38]. Before this information can be utilised reliably in clinical practice, more studies with large sample sizes and low variability are needed. This applies not only to studies on prosthesis-related risk factors, but to all experimental DTI studies on human subjects. Thus, consistency in patient groups, socket types, alignment, and componentry are crucial.
Tissue loading is undoubtedly a major factor in the development of DTI. Traditionally, the interface pressure between the socket and the residuum was quantified with sensor technologies [40, 89]. With the discovery of deep tissue layers as the potential origin of pressure ulcers [4, 11], the focus shifted towards assessing internal mechanics. New methodologies were needed as the forces applied at the interface do not reflect the internal loading states [90, 91].
Computational and analytical modelling
According to our review, modelling was the measure of choice. Medical images, interface pressure measurements, and data on mechanical properties of soft tissue informed numerical and analytical models. Researches then used the estimated stress and strain values of those models to determine general loading patterns during various scenarios and patient-specific DTI risks.
However, the interpretation of estimated stress and strain values beyond basic trends is limited. This comes down to the complexity of soft tissue mechanics. Skeletal muscle shows time-dependent behaviour under load, including hysteresis, stress relaxation, and creep [92, 93]. Due to its cellular arrangement in parallel fibrous structures, the direction of load application alters the mechanical properties, known as anisotropy . Additionally, the residuum consists not only of skeletal muscle, but also adipose tissue, connective tissue, and skin, which all have different, patient-specific mechanical properties. Each layer might also be affected by inhomogeneities, like scar tissue or fat infiltration. Taken together, the intricate nature of soft tissues exceeds the modelling capabilities of existing computational approaches . The research on biomechanics of the residual limb is no exception and usually draws on simplified concepts with assumptions of linear elasticity, isotropy, or homogeneity. Even though clinical translatability is a core issue in DTI research, the accuracy of the proposed patient-specific modelling approaches based on these simplifications is questionable.
Nevertheless, promising methodological developments may increase the accuracy of future research efforts (Table 8). An additional advancement is the integration of model post-processing. Muscle stiffening is a phenomenon observed after the onset of DTI, which redistributes subsequent loads towards adjacent sites and promotes damage progression in a positive feedback loop [44, 99]. Integrating this damage law into FE models for prolonged loading increases the accuracy of DTI prediction [33, 44]. Widening this approach to model pre-processing by incorporating the effects of the donning procedure, as Lacroix and Patino  did for transfemoral amputees, would improve modelling even further.
Alternatives to determine internal loading states
Modelling is not the only approach to determine internal loading states. Medical imaging offers ways to visualise soft tissue deformation directly. MRI tagging has been proposed and used to derive strain values of compressed muscle [96, 101]. Another option would be to measure physiological features that are indirectly related to the mechanical state of tissues. DT MRI for example captures changes in diffusivity due to compression , making it a potential measure for strain . Given the complexity and limitations that the predictive nature of analytical and computational modelling inheres, it seems sensible to integrate technologies that have not yet been used in the context of pressure ulcer research.
Whilst we believe that our systematic approach according to the PRISMA-ScR guidelines identified most of the relevant literature, there are various sources of potential bias. Firstly, the lack of registration of the review protocol prior to performing this scoping review may have introduced conduction and reporting bias. By restricting the search to English language and excluding grey literature, we might have missed studies and introduced selection bias. Further papers might have been overlooked due to the heterogeneities in wording and definitions of pressure injuries [8, 104, 105], despite the use of common DTI- and prosthesis-related expressions in our search strategy. Additionally, the review process was mainly conducted by one reviewer. We aimed to limit possible selection bias by consulting a second reviewer in case of uncertainty. Lastly, we focussed on transtibial prosthetic users, whereas transfemoral amputees might experience similar conditions and could therefore be included in future endeavours.
This scoping review recorded an overwhelming interplay of aetiological and risk factors for DTI in transtibial prosthetic users. It also highlighted the urgent need for fundamental research in this area. Particularly relevant is the unique biomechanical environment created by the interaction of the residuum and prosthetic socket during gait, which is characterised by high shear forces and repetitive loading. Combining the tissue’s response to dynamic loading, which is currently investigated by our research team, with advanced measurement methods like imaging techniques could provide new insights into the aetiology of DTI. A better understanding of the influence of prostheses on the vascular and lymphatic system is also essential.
To realise these endeavours effectively, an interdisciplinary approach and the integration of stakeholders is inevitable. The results of prosthesis-oriented research have the potential to provide the scientific basis for consensus on much-needed advancements in clinical practice: from improved amputation and rehabilitation processes, to updated socket design and fitting procedures, and the optimised use of componentry. A growing body of research on DTI in transtibial prosthetic users could also inform pressure ulcer categorisations, reporting standards, and international guidelines. Ultimately, the goal should be to reduce the prevalence and risk of DTI in transtibial prosthetic users and improve patient care.
This scope review follows a methodological framework [27, 106], which was refined by the Joanna Briggs Institute (JBI) . It is also compliant with the PRISMA-ScR checklist for scoping reviews  (see Additional file 1).
The database search included Pubmed (Medline), Ovid Excerpta Medica (Embase classic and Embase), and Scopus. It covered the first possible date for each database until June 2019, when we conducted the search. We utilised automatized categorisation of the MeSH term “pressure ulcer” or a database-specific equivalent. This inclusion of the generic pressure ulcer term ensured full coverage, as DTI was only recently accredited as separate pressure injury category . The full search strategy was constructed as follows (Table 9):
We scanned reference lists and forward-citation reports of eligible manuscripts for relevant articles that have not been identified in the automatic search. Additionally, we contacted an expert in the field of DTI for further literature suggestions.
Study selection and inclusion criteria
Primary and secondary sources were retrieved from the automatic search. We filtered out duplicate articles and duplicates published as conference proceedings with the aid of a citation software (Zotero 5.0.69).
For further assessment, one reviewer (M.G.) screened the remaining articles. They had to be written in English, have an available full text, and have a title and abstract relevant to DTI as a result of prosthetic use. Studies on unrelated conditions and with amputations other than at transtibial level were excluded. Likewise, papers describing superficial, Stage 1, or Stage 2 pressure injuries were disregarded. To ensure a minimum qualitative standard, all papers had to be peer reviewed.
In the following full-text examination, one reviewer (M.G.) evaluated the relevance, study group characteristics, and type of pressure injury. Additionally, transtibial prosthetics and DTI had to be the focus of the article. In case of uncertainty about eligibility of articles, a second reviewer (A.B.) was consulted and possible disagreements discussed until consensus was reached.
By scanning through reference lists and forward-citations of eligible papers, we identified further resources. We validated their suitability with the previously described process, before including them in the final qualitative synthesis. We also retrieved recommendations on relevant literature from expert contact. All but one of the suggested sources were already included in the current synthesis, with the additional paper being irrelevant for this review.
We extracted data from the combined search results according to suggestions by the JBI  and the PRISMA-ScR checklist  with slight adjustments. The variables of interest were author, year, country, type of study, aims and objectives, study population and sample size (if applicable), methodology, outcome measures, and key findings related to DTI in transtibial prosthetic users. The complete range of studies was then thematically grouped for further in-depth analysis, which is presented in the “Results” section in tables and supporting narratives.
Availability of data and materials
All data generated or analysed during this study are included in this published article and its supplementary information files.
- DT MRI:
Diffusion Tensor MRI
Deep Tissue Injury
Energy storage and return
Joanna Briggs Institute
Medical device related pressure ulcer
Magnetic resonance imaging
National Pressure Ulcer Advisory Panel
Patellar tendon bearing
Root mean square
Spinal cord injury
Strain energy density
Total surface bearing
National Pressure Ulcer Advisory Panel. NPUAP Pressure Injury Stages. 2016. http://www.npuap.org/resources/educational-and-clinical-resources/npuap-pressure-injury-stages/. Accessed 11 Oct 2018.
Guest JF, Ayoub N, McIlwraith T, Uchegbu I, Gerrish A, Weidlich D, et al. Health economic burden that different wound types impose on the UK’s National Health Service. Int Wound J. 2017;14:322–30.
Gould LJ, Bohn G, Bryant R, Paine T, Couch K, Cowan L, et al. Pressure ulcer summit 2018: an interdisciplinary approach to improve our understanding of the risk of pressure-induced tissue damage. Wound Repair Regen. 2019;27(5):497–508. https://doi.org/10.1111/wrr.12730.
Bouten CV, Oomens CW, Baaijens FP, Bader DL. The etiology of pressure ulcers: skin deep or muscle bound? Arch Phys Med Rehabil. 2003;84:616–9.
Black J, Baharestani MM, Cuddigan J, Dorner B, Edsberg L, Langemo D, et al. National Pressure Ulcer Advisory Panel’s updated pressure ulcer staging system. Adv Skin Wound Care. 2007;20:269–74.
Gefen A, Farid KJ, Shaywitz I. A review of deep tissue injury development, detection, and prevention: shear savvy. Ostomy Wound Manage. 2013;59:26–35.
Oomens CWJ, Bader DL, Loerakker S, Baaijens F. Pressure induced deep tissue injury explained. Ann Biomed Eng. 2015;43:297–305.
Kottner J, Balzer K, Dassen T, Heinze S. Pressure ulcers: a critical review of definitions and classifications. Ostomy Wound Manage. 2009;55:22–9.
Mak AFT, Zhang M, Tam EWC. Biomechanics of Pressure Ulcer in Body Tissues Interacting with External Forces during Locomotion. Annu Rev Biomed Eng. 2010;12:29–53.
Aoi N, Yoshimura K, Kadono T, Nakagami G, Iizuka S, Higashino T, et al. Ultrasound assessment of deep tissue injury in pressure ulcers: possible prediction of pressure ulcer progression. Plast Reconstr Surg. 2009;124:540–50.
Berlowitz D, Brienza DM. Are all pressure ulcers the result of deep tissue injury? A review of the literature. Ostomy Wound Manage. 2007;53:34–8.
Bouten CVC, Colin D. In: CWJ O, editor. Pressure Ulcer Research. Berlin/Heidelberg: Springer-Verlag; 2005. https://doi.org/10.1007/3-540-28804-X.
Sopher R, Nixon J, Gorecki C, Gefen A. Effects of intramuscular fat infiltration, scarring, and spasticity on the risk for sitting-acquired deep tissue injury in spinal cord injury patients. J Biomech Eng. 2011;133(2):021011. https://doi.org/10.1115/1.4003325.
Lin F, Pandya A, Cichowski A, Modi M, Reprogle B, Lee D, et al. Deep tissue injury rat model for pressure ulcer research on spinal cord injury. J Tissue Viability. 2010;19:67–76.
Elsner JJ, Gefen A. Is obesity a risk factor for deep tissue injury in patients with spinal cord injury? J Biomech. 2008;41:3322–31.
Gefen A. The biomechanics of sitting-acquired pressure ulcers in patients with spinal cord injury or lesions. Int Wound J. 2007;4:222–31.
Bogie K, Bader D. Susceptibility of spinal cord-injured individuals to pressure ulcers. In: Pressure ulcer research. Berlin/Heidelberg: Springer-Verlag; 2005. p. 73–88. https://doi.org/10.1007/3-540-28804-X_6.
Linder-Ganz E, Shabshin N, Itzchak Y, Gefen A. Assessment of mechanical conditions in sub-dermal tissues during sitting: a combined experimental-MRI and finite element approach. J Biomech. 2007;40:1443–54.
Linder-Ganz E, Shabshin N, Itzchak Y, Yizhar Z, Siev-Ner I, Gefen A. Strains and stresses in sub-dermal tissues of the buttocks are greater in paraplegics than in healthy during sitting. J Biomech. 2008;41:567–80.
Dudek NL, Marks MB, Marshall SC, Chardon JP. Dermatologic conditions associated with use of a lower-extremity prosthesis. Arch Phys Med Rehabil. 2005;86:659–63.
Meulenbelt HE, Geertzen JH, Jonkman MF, Dijkstra PU. Determinants of skin problems of the stump in lower-limb amputees. Arch Phys Med Rehabil. 2009;90:74–81.
Colgecen E, Korkmaz M, Ozyurt K, Mermerkaya U, Kader C. A clinical evaluation of skin disorders of lower limb amputation sites. Int J Dermatol. 2016;55:468–72.
Ehde DM, Czerniecki JM, Smith DG, Campbell KM, Edwards WT, Jensen MP, et al. Chronic phantom sensations, phantom pain, residual limb pain, and other regional pain after lower limb amputation. Arch Phys Med Rehabil. 2000;81:1039–44.
Lineham B, Harwood P, Giannoudis P. Case study: correction of angular deformity post-trans-tibial amputation to improve prosthesis fit and comfort. Prosthetics Orthot Int. 2015;39:157–60.
Vocke AK, Schmid A. Osseous overgrowth after post-traumatic amputation of the lower extremity in childhood. Arch Orthop Trauma Surg. 2000;120:452–4.
Bader DL, Worsley PR, Gefen A. Bioengineering considerations in the prevention of medical device-related pressure ulcers. Clin Biomech. 2019;67:70–7.
Levac D, Colquhoun H, O’Brien KK. Scoping studies: advancing the methodology. Implement Sci. 2010;5. https://doi.org/10.1186/1748-5908-5-69.
Kosasih JB, Silver-Thorn MB. Sensory changes in adults with unilateral transtibial amputation. J Rehabil Res Dev. 1998;35:85–90.
Portnoy S, Yarnitzky G, Yizhar Z, Kristal A, Oppenheim U, Siev-Ner I, et al. Real-time patient-specific finite element analysis of internal stresses in the soft tissues of a residual limb: a new tool for prosthetic fitting. Ann Biomed Eng. 2007;35:120–35.
Portnoy S, Siev-Ner I, Shabshin N, Kristal A, Yizhar Z, Gefen A. Patient-specific analyses of deep tissue loads post transtibial amputation in residual limbs of multiple prosthetic users. J Biomech. 2009;42:2686–93.
Portnoy S, van Haare J, Geers RPJ, Kristal A, Siev-Ner I, Seelen HAM, et al. Real-time subject-specific analyses of dynamic internal tissue loads in the residual limb of transtibial amputees. Med Eng Phys. 2010;32:312–23.
Portnoy S, Kristal A, Gefen A, Siev-Ner I. Outdoor dynamic subject-specific evaluation of internal stresses in the residual limb: hydraulic energy-stored prosthetic foot compared to conventional energy-stored prosthetic feet. Gait Posture. 2012;35:121–5.
Portnoy S, Siev-Ner I, Shabshin N, Gefen A. Effects of sitting postures on risks for deep tissue injury in the residuum of a transtibial prosthetic-user: a biomechanical case study. Comput Methods Biomech Biomed Engin. 2011;14:1009–19.
Portnoy S, Yizhar Z, Shabshin N, Itzchak Y, Kristal A, Dotan-Marom Y, et al. Internal mechanical conditions in the soft tissues of a residual limb of a trans-tibial amputee. J Biomech. 2008;41:1897–909.
Buis A, Guarato F, Law J, Ralston Z, Courtney A. A feasibility study to investigate if there is a correlation between soft tissue deformation and acoustic emission. Can Prosthet Orthot J. 2018. https://doi.org/10.33137/cpoj.v1i1.30354.
Portnoy S, Siev-Ner I, Yizhar Z, Kristal A, Shabshin N, Gefen A. Surgical and morphological factors that affect internal mechanical loads in soft tissues of the transtibial residuum. Ann Biomed Eng. 2009;37:2583–605.
Portnoy S, Atlas E, Gefen A. Influence of bony prominence sharpness and underlying tissue stiffness on the susceptibility to pressure-related deep tissue injury: biomechanical computer model studies. L’escarre. 2007;36:4–7.
Lenz AL. A synergistic approach to transtibial socket interface mechanics: experiments and modeling [dissertation]. East Lansing: Michigan State University; 2017.
Henrot P, Stines J, Walter F, Martinet N, Paysant J, Blum A. Imaging of the painful lower limb stump. RadioGraphics. 2000;20:219–35.
Mak AFT, Zhang M, Boone DA. State-of-the-art research in lower-limb prosthetic biomechanics- socket interface: a review. J Rehabil Res Dev. 2001;38:14.
Dickinson AS, Steer JW, Worsley PR. Finite element analysis of the amputated lower limb: a systematic review and recommendations. Med Eng Phys. 2017;43:1–18.
Linder-Ganz E, Engelberg S, Scheinowitz M, Gefen A. Pressure–time cell death threshold for albino rat skeletal muscles as related to pressure sore biomechanics. J Biomech. 2006;39:2725–32.
Gefen A, van Nierop B, Bader DL, Oomens CW. Strain-time cell-death threshold for skeletal muscle in a tissue-engineered model system for deep tissue injury. J Biomech. 2008;41:2003–12.
Gefen A, Gefen N, Linder-Ganz E, Margulies SS. In vivo muscle stiffening under bone compression promotes deep pressure sores. J Biomech Eng. 2005;127:512.
Yang F. Asymptotic solution to axisymmetric indentation of a compressible elastic thin film. Thin Solid Films. 2006;515:2274–83.
Gefen A, editor. Bioengineering research of chronic wounds: a multidisciplinary study approach. Berlin: Springer; 2009.
Bliss M. Aetiology of pressure sores. Rev Clin Gerontol. 1993;3:379.
Linder-Ganz E, Gefen A. Stress analyses coupled with damage laws to determine biomechanical risk factors for deep tissue injury during sitting. J Biomech Eng. 2009;131:011003.
Sopher R, Nixon J, Gorecki C, Gefen A. Exposure to internal muscle tissue loads under the ischial tuberosities during sitting is elevated at abnormally high or low body mass indices. J Biomech. 2010;43:280–6.
Loerakker S, Manders E, Strijkers GJ, Nicolay K, Baaijens FPT, Bader DL, et al. The effects of deformation, ischemia, and reperfusion on the development of muscle damage during prolonged loading. J Appl Physiol. 2011;111:1168–77.
Loerakker S, Stekelenburg A, Strijkers GJ, Rijpkema JJM, Baaijens FPT, Bader DL, et al. Temporal effects of mechanical loading on deformation-induced damage in skeletal muscle tissue. Ann Biomed Eng. 2010;38:2577–87.
Buis AWP, Dumbleton T, Murray KD, McHugh BF, McKay G, Sexton S. Measuring the daily stepping activity of people with Transtibial amputation using the ActivPAL™ activity monitor. J Prosthetics Orthotics. 2014;26:43–7.
Dou P, Jia X, Suo S, Wang R, Zhang M. Pressure distribution at the stump/socket interface in transtibial amputees during walking on stairs, slope and non-flat road. Clin Biomech. 2006;21:1067–73.
Klasson B, Buis A. Advanced prosthetic science - prosthetic socket fit; implications of basic engineering principles. University of Strathclyde. Glasgow: National Centre for Training and Education in Prosthetics and Orthotics; 2006.
Lilja M, Johansson T, Öberg T. Movement of the tibial end in a PTB prosthesis socket: a sagittal X-ray study of the PTB prosthesis. Prosthetics Orthot Int. 1993;17:21–6.
Papaioannou G, Mitrogiannis C, Nianios G, Fiedler G. Assessment of amputee socket–stump–residual bone kinematics during strenuous activities using dynamic roentgen Stereogrammetric analysis. J Biomech. 2010;43:871–8.
Wounds International. International review: pressure ulcer prevention: pressure, shear, friction and microclimate in context. A consensus document. London: Wounds International; 2010.
Tam EWC, Mak AFT, Evans JH, YYN C. Post occlusive hyperaemic effect of tissue under static and dynamic loading conditions [using laser perfusion imager]. In: Biomedical Engineering Towards the Year 2000 and Beyond. IEEE; 1998. p. 2294–6.
Tsuji S, Ichioka S, Sekiya N, Nakatsuka T. Analysis of ischemia-reperfusion injury in a microcirculatory model of pressure ulcers. Wound Repair Regen. 2005;13:209–15.
Linder-Ganz E, Gefen A. The effects of pressure and shear on capillary closure in the microstructure of skeletal muscles. Ann Biomed Eng. 2007;35:2095–107.
Manorama A, Meyer R, Wiseman R, Bush TR. Quantifying the effects of external shear loads on arterial and venous blood flow: implications for pressure ulcer development. Clin Biomech. 2013;28:574–8.
Peirce SM, Skalak TC, Rodeheaver GT. Ischemia-reperfusion injury in chronic pressure ulcer formation: a skin model in the rat. Wound Repair Regen. 2000;8:68–76.
Sanders JE, Daly CH, Burgess EM. Clinical measurement of normal and shear stresses on a trans-tibial stump: characteristics of wave-form shapes during walking. Prosthetics Orthot Int. 1993;17:38–48.
Goldstein B, Sanders J. Skin response to repetitive mechanical stress: a new experimental model in pig. Arch Phys Med Rehabil. 1998;79:265–72.
Sanders J. Stump-socket Interface conditions. In: Pressure ulcer research. Berlin/Heidelberg: Springer-Verlag; 2005. p. 129–47. https://doi.org/10.1007/3-540-28804-X_9.
Gawlitta D, Oomens CWJ, Bader DL, Baaijens FPT, Bouten CVC. Temporal differences in the influence of ischemic factors and deformation on the metabolism of engineered skeletal muscle. J Appl Physiol. 2007;103:464–73.
Hagisawa S, Shimada T. Skin morphology and its mechanical properties associated with loading. In: Pressure ulcer research. Berlin/Heidelberg: Springer-Verlag; 2005. p. 161–85.
Kalogeris T, Baines CP, Krenz M, Korthuis RJ. Cell biology of ischemia/reperfusion injury. Int Rev Cell Mol Biol. 2012;298:229–317.
Margaris KN, Black RA. Modelling the lymphatic system: challenges and opportunities. J R Soc Interface. 2012;9:601–12.
Miller GE, Seale J. Lymphatic clearance during compressive loading. Lymphology. 1981;14:161–6.
Reddy NP, Cochran GVB, Krouskop TA. Interstitial fluid flow as a factor in decubitus ulcer formation. J Biomech. 1981;14:879–81.
Gray RJ, Voegeli D, Bader DL. Features of lymphatic dysfunction in compressed skin tissues – implications in pressure ulcer aetiology. J Tissue Viability. 2016;25:26–31.
Yao Y, Da Ong LX, Li X, Wan K, Mak AFT. Effects of biowastes released by mechanically damaged muscle cells on the propagation of deep tissue injury: a multiphysics study. Ann Biomed Eng. 2017;45:761–74.
Kasuya A, Sakabe J, Tokura Y. Potential application of in vivo imaging of impaired lymphatic duct to evaluate the severity of pressure ulcer in mouse model. Sci Rep. 2014;4:4173.
Ruocco V, Brunetti G, Puca RV, Ruocco E. The immunocompromised district: a unifying concept for lymphoedematous, herpes-infected and otherwise damaged sites. J Eur Acad Dermatol Venereol. 2009;23:1364–73.
Bouch E, Burns K, Geer E, Fuller M, Rose A, Broomhead P. Guidance for the multi disciplinary team on the management of post operative residuum oedema in lower limb amputees. Bradford: British Association of Chartered Physiotherapists in Amputee Rehabilitation; 2012.
Prompers JJ, Jeneson JAL, Drost MR, Oomens CCW, Strijkers GJ, Nicolay K. Dynamic MRS and MRI of skeletal muscle function and biomechanics. NMR Biomed. 2006;19:927–53.
Barnay J, Joussain C, Orta C, Tourlonias B, Laroche D, Morard M, et al. Use of near-infrared spectroscopy (NIRS) in the evaluation of tissular oxygenation of under knee limb amputation from arteriopathy. Ann Phys Rehabil Med. 2014;57(Suppl 1):120.
Ferrari M, Muthalib M, Quaresima V. The use of near-infrared spectroscopy in understanding skeletal muscle physiology: recent developments. Philos Trans R Soc A Math Phys Eng Sci. 2011;369:4577–90.
Ertl J. Über Amputationsstümpfe. Der Chirurg. 1949;20:218–24.
Brückner L. A standardised trans-tibial amputation method following chronic occlusive arterial disease; 1992.
Burgess EM. The management of lower-extremity amputations: surgery, immediate postsurgical prosthetic fitting, patient care. Washington: Prosthetic and Sensory Aids Service, Veterans Administration; 1969.
Lilja M, Hoffmann P, Öberg T. Morphological changes during early trans-tibial prosthetic fitting. Prosthetics Orthot Int. 1998;22:115–22.
Information Services Division NHSScotland. The Amputee Statistical Database for the United Kingdom 2004/2005. Edinburgh: National Amputee Statistical Database (NASDAB); 2005.
Ziegler-Graham K, MacKenzie EJ, Ephraim PL, Travison TG, Brookmeyer R. Estimating the prevalence of limb loss in the United States: 2005 to 2050. Arch Phys Med Rehabil. 2008;89:422–9.
Stewart CPU. Synopsis of causation lower limb amputation. Ministry of Defence; 2008.
Marino M, Pattni S, Greenberg M, Miller A, Hocker E, Ritter S, et al. Access to prosthetic devices in developing countries: Pathways and challenges. In: 2015 IEEE Global Humanitarian Technology Conference (GHTC); 2015. p. 45–51.
Eide AH, Øderud T. Assistive Technology in low-Income Countries. In: Disability & International Development. New York: Springer US; 2009. p. 149–60. https://doi.org/10.1007/978-0-387-93840-0_10.
Al-Fakih EA, Abu Osman NA, Mahmad Adikan FR. Techniques for Interface stress measurements within prosthetic sockets of Transtibial amputees: a review of the past 50 years of research. Sensors. 2016;16:1119.
Oomens C, Bressers O, Bosboom E, Bouten C, Bader D. Can loaded interface characteristics influence strain distributions in muscle adjacent to bony prominences? Comput Methods Biomech Biomed Engin. 2003;6:171–80.
Oomens CWJ, Loerakker S, Bader DL. The importance of internal strain as opposed to interface pressure in the prevention of pressure related deep tissue injury. J Tissue Viability. 2010;19:35–42.
Aritan S, Oyadiji SO, Bartlett RM. The in vivo mechanical properties of muscular bulk tissue. In: Annual international conference of the IEEE engineering in medicine and biology society. Minneapolis: IEEE; 2009. p. 5259–62. https://doi.org/10.1109/IEMBS.2009.5334084.
Robi K, Jakob N, Matevz K, Matjaz V. The physiology of sports injuries and repair processes. In: Hamlin M, editor. Current Issues in Sports and Exercise Medicine. InTech; 2013. https://doi.org/10.5772/54234.
Ramasamy E, Okan A, Dorow B, Chong S-Y, Gizzi L, Steidle G, et al. An efficient Modelling-simulation-analysis workflow to investigate stump-socket interaction using patient-specific, three-dimensional, continuum-mechanical, finite element residual limb models. Front Bioeng Biotechnol. 2018;6:1–17.
Bader DL, Worsley PR. Technologies to monitor the health of loaded skin tissues. Biomed Eng Online. 2018;17:40. https://doi.org/10.1186/s12938-018-0470-z.
Strijkers GJ, Araujo ECA, Azzabou N, Bendahan D, Blamire A, Burakiewicz J, et al. Exploration of new contrasts, targets, and MR imaging and spectroscopy techniques for neuromuscular disease – a workshop report of working group 3 of the biomedicine and molecular biosciences COST action BM1304 MYO-MRI. J Neuromuscul Dis. 2019;6:1–30.
Nelissen JL, de Graaf L, Traa WA, Schreurs TJL, Moerman KM, Nederveen AJ, et al. A MRI-compatible combined mechanical loading and MR Elastography setup to study deformation-induced skeletal muscle damage in rats. PLoS One. 2017;12:e0169864. https://doi.org/10.1371/journal.pone.0169864.
Sigrist RMS, Liau J, Kaffas AE, Chammas MC, Willmann JK. Ultrasound Elastography: review of techniques and clinical applications. Theranostics. 2017;7:1303–29.
Linder-Ganz E, Gefen A. Mechanical compression-induced pressure sores in rat hindlimb: muscle stiffness, histology, and computational models. J Appl Physiol. 2004;96:2034–49.
Lacroix D, Ramírez Patiño JF. Finite element analysis of donning procedure of a prosthetic Transfemoral socket. Ann Biomed Eng. 2011;39:2972–83.
Ceelen KK, Stekelenburg A, Mulders JLJ, Strijkers GJ, Baaijens FPT, Nicolay K, et al. Validation of a numerical model of skeletal muscle compression with MR tagging: a contribution to pressure ulcer research. J Biomech Eng. 2008;130:061015.
Gefen A, Cornelissen LH, Gawlitta D, Bader DL, Oomens CWJ. The free diffusion of macromolecules in tissue-engineered skeletal muscle subjected to large compression strains. J Biomech. 2008;41:845–53.
Sekino M, Kaneko A, Ueno S. Mapping of strain-induced diffusivity changes in biological tissues using magnetic resonance. IEEE Trans Magn. 2005;41:4176–8.
Kottner J, Sigaudo-Roussel D, Cuddigan J. From bed sores to skin failure: linguistic and conceptual confusion in the field of skin and tissue integrity. Int J Nurs Stud. 2019;92:58–9.
Ousey K, Schoonhoven L, Moore Z, Fletcher J. Should the EPUAP adopt the NPUAP’s new pressure ulcer terminology and definitions? Wounds UK. 2017;13:8–14.
Arksey H, O’Malley L. Scoping studies: towards a methodological framework. Int J Soc Res Methodol. 2005;8:19–32.
Peters M, Godfrey C, McInerey P, Baldini Soares C, Kahlil H, Parker D. Chapter 11: scoping reviews. In: Aromataris E, Munn Z, editors. Joanna Briggs Institute Reviewer’s Manual: The Joanna Briggs Institute; 2017. https://reviewersmanual.joannabriggs.org/. Accessed 2 Jul 2019.
Tricco AC, Lillie E, Zarin W, O’Brien KK, Colquhoun H, Levac D, et al. PRISMA extension for scoping reviews (PRISMA-ScR): checklist and explanation. Ann Intern Med. 2018;169:467.
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Graser, M., Day, S. & Buis, A. Exploring the role of transtibial prosthetic use in deep tissue injury development: a scoping review. BMC biomed eng 2, 2 (2020). https://doi.org/10.1186/s42490-020-0036-6
- Pressure ulcer
- Leg prosthesis
- Soft tissue injuries
- Biomechanical phenomena
- Risk factors