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STRESS-STRAIN DISTRIBUTION IN THE MODEL OF RETROCALCANEAL BURSITIS BY USING HEEL-ELEVATION INSOLES

The aim of this study is the analysis of the equivalent stress on the rear foot structures in retrocalcaneal bursitis, when using heel-elevation insoles of different heights (10 mm and 20 mm). Methods – mathematical calculations of the Achilles force required in the heel-off of the gait stance phase in the conditions of lifting the heel by 10 mm and 20 mm. A 3D-simulation foot model with an enlarged retrocalcaneal bursa was created. The analysis was carried out by the finite element method to calculate and study the stress and strain in the rear foot structures. Results. When using a 10.0 mm height heel-elevation insole, the calf muscle strength, which must be applied to the heel-off of the gait stance phase, was 19.0 % less than without support and 26.8 % less in 20.0 mm insole. Accordingly, analyzing the simulation results in terms of von-Mises stress, the maximum stress observed on the Achilles tendon decreases by 20.0 % and by 30.0 %. The total deformations maximum in the model when using heel-elevation insoles decreased up to 18.1 % and they were localized not in the tendon, but in the bone structures of subtalar joint. The maximum values of the total deformation of the model in the case of 10.0 mm and 20.0 mm heel-elevation insoles were 91.67 mm (–20.2 %) and 80.04 mm (–30.3 %), respectively, compared 114.92 mm in the absence of insoles. When using insole with a height of 10.0 mm, the stress in the retrocalcaneal bursa decreased by 20.0 % and was equal to 14.92 MPa compared to 18.66 MPa, and when using a 20.0 mm insoles by 30.0 %. Conclusions. It was found that when using 10.0–20.0 mm heel-elevation insoles, the stress distribution in the rear foot structures was significantly reduced by an average of 20.0-30.0 % and correlated with the height of the insoles.


Introduction
Despite the large number of scientific studies, the problem of diagnosis and treatment of diseases of the Achilles tendon (AT) and surrounding structures remains relevant. A special place is occupied by the problem of treatment of AT diseases -tendinopathies and tendinitis. It is believed that the cause of these diseases is a constant overload on the tendon, which leads to inflammatory and subsequently to degenerative changes in tendon tissue. However, there are studies that show a link between the inflammatory process in the retrocalcaneal bursa and concomitant changes in the AT. According to Pavlov H. and others [1] in 9 out of 10 cases of Haglund's syndrome, retrocalcaneal bursitis (RB) and tendinitis were diagnosed. In their study, Karjalainen, P. T., Soila, K. et al., found that in 118 ATs diagnosed by magnetic resonance imaging, 19 % of the cases had enlarged Original Research Article: full paper (2020), «EUREKA: Health Sciences» Number 6 Medicine and Dentistry retrocalcaneal bursa. It was also found that in 15 of 18 cases of insertional tendinopathy, RB was detected [2]. Todd A. Irwin in his study [3] also points to the link between an inflammatory process in the synovial bursa and degenerative changes in the tendon itself and between RB and concomitant tendinopathy. A retrospective study [4] of 176 patients with insertional tendinopathy of AT found that 74 % of patients were also diagnosed with superficial and retrocalcaneal bursitis, as well as Haglund syndrome. In our study [5] of the stress-strain state of the rear-foot structures in patients with retrocalcaneal/Haglund syndrome when standing and in the act of walking, it was proven that the maximum stress in all the rearfoot structures, regardless of the position of the foot and the ankle joint is concentrated on the AT. However, in cases of retrocalcaneal bursitis and Haglund syndrome, the stress values were significantly higher -by 10.1 % and 68.6 %, respectively, compared to normal values. The maximum values of stress on the AT were recorded in the dorsiflexion of the foot. It was also noted that in the model with Haglund syndrome, the values of stress on the AT remained higher compared to normal values in all positions of the foot. In conclusion, it can be argued that in RB and Haglund syndrome there are prerequisites for the development of secondary tendinopathy of the AT. Timely treatment of these diseases avoids the development of changes in the AT. Therefore, in the treatment, complex measures are needed to reduce the load on the AT. In the conservative treatment of tendinopathy, it has been suggested to use heel elevation insoles, which, by raising the heel, presumably reduce the load on the AT [6]. However, scientific works indicate controversial results: raising the heel by 15-18 mm increases [7], decrea ses [8] or does not affect [9,10] the load on the AT during walking. We have not found any work that describes the effectiveness of heel elevation insoles in the treatment of patients with RB or Haglund syndrome.
According to a few authors, the use of orthopedic insoles does not reduce the risk of exacerbations and in fact has no therapeutic effect [11]. However, in some works [12] the authors used high-heeled shoes (3-5 cm) in the postoperative period in Haglund syndrome in order to reduce pain. However, they do not justify the reason for choosing such a height of the heel and do not indicate the duration of its use and effectiveness in reducing pain. Therefore, the study of the amount of stress on the rear-foot structures in patients with RB with the use of a heel elevation insole is relevant and answers a number of questions regarding the prevention and treatment of concomitant changes in the AT.
The aim of the study -the equivalent stress analysis of the rear foot structures in retrocalcaneal bursitis, using heel-elevation insoles of different heights (10 mm and 20 mm).

Materials and methods
At the initial stage, calculation schemes were created ( Fig. 1). Mathematical calculations of the force of the calf muscle, which must be applied to the heel to push off from the plane of support in the act of walking were performed. According to the calculation scheme, depending on the height of the insoles, the center of mass of the body is shifted forward by the distance AC with a simultaneous change to the «angle of attack» α and the tensile force F of the Achilles tendon. Mathematical calculations are presented in Formula 1, where α is the inclination angle of AT; P -human weight 750 H (75 kg); F is the tension force of the tendon.
The calculation of the force F required to stabilize the ankle joint in the vertical position of the body when pushing the hind leg from the area of support (dorsiflexion + 10°) was made according to Formula 2.
The obtained data was used in further calculations by the method of finite element analysis (FEA).
In the next step, a three-dimensional simulation model of the tibia and rear foot was generated using the SolidWorks software package (Dassault Systèmes SolidWorks Corporation, Canada). Anatomical, anthropometric and CT data was used to create the model. To determine the geometric characteristics of the AT, the average anthropometric data of a person with a normosthenic posture, approximate body weight 70-75 kg, height 170-176 cm were used. AT was schematically divided into the following areas ( Fig. 2): -heel bump; -upper edge of the calcaneus; -middle part of the AT; -transition of the AT to the soleus muscle; -transition of the AT to the calf muscle.

Fig. 2. Geometric characteristics of the Achilles tendon
Geometric parameters of width and thickness at each part of the AT are presented in Table 1. The boundary conditions assumed, material properties, and muscle forces applied in the model presented in Fig. 2, with a restriction on moving the heel forward and blocking rotational movements. The load applied on the ankle represented by double-support standing simulation -50 % of the body weight of the average subject 75 kg, 300 H (C) on the tibia and 75 H (D) on the fibula. In the model all the materials were considered linear.
Further calculations performed by FEA, allows exploration of the evolution of the deformation process simulation model elements -bone, bursa and the tendon, with large nonlinear geometric and physical properties of materials and time variables and external influences. For the stress-strain analysis by the FEA, the simulation models were imported into the «ANSYS» (ANSYS, Inc., USA). The following physical properties of biological tissues used ( Table 2). The finite element (FE) models were generated in semiautomatic mode (Fig. 3, 4) and were represented mainly by tetrahedral elements, consisted of 381574 nodes and 223604 elements. The FE mesh size of the basic model does not exceed 1 mm. To increase the accuracy of FEA, the mesh is compacted in the contact areas of the bursa and tendon elements with FE mesh size 0.1-0.5 mm.
The calculations were performed for different heel elevation positions -0, 10 mm and 20 mm at the heel-off of the gait stance phase, from which the maximum stress takes place.  According to the obtained results, it was proven that the use of heel-elevation insoles reliably and effectively reduces the stress in the retrocalcaneal bursa and AT (Fig. 7.). Thus, when the heel elevated by 10

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The maximum strain of the model tended to decreases -up to 18.1 % (0.14 mm vs. 0.171 mm) and was localized not on the AT, but on the subtalar joint area.
The maximum values of the Total Deformations of the model were located in the calf muscle. In the 10

Discussion
The current study aimed to analyze the equivalent stress on the rear foot structures in retrocalcaneal bursitis, when using heel-elevation insoles of different heights (10 mm and 20 mm). One of the causes of posterior heel pain is impingement of the retrocalcaneal bursa between the postero-superior part of the calcaneus (an increase of this part is called «Haglund's deformity») and AT. An increase in the retrocalcaneal bursa, its thight and an increase in pressure inside it directly indicate bursitis [12]. The enlargement and thight of the bursa leads to a local overload of the AT near the insertion site and the adjacent part of the calcaneus [5]. This explains the development of insertional tendinopathy in patients with retrocalcaneal bursitis [3,4]. Therefore, one of the goals of treatment is to enlargement the retrocalcaneal recess. This can be done surgically (by removing the enlarged part of the calcaneus), or reducing the heel inclination angle, thereby increasing the angle of attack of the AT. For this, various orthopedic insoles are used.
Previous studies [13] have shown reduction of Achilles Tendon load during running by using customized arch support orthosis (CASO) or an orthotic heel lift (HL). Regarding the Achilles Tendon load, both orthoses, CASO (p=0.003, d=0.93) and HL (p=0.004, d=0.78), exhibited significant lower value than the control but similarly, no significant difference was noted between them in which the use of CASO yielded a slightly lower loading rate than that of HL. It should be noted that the study was conducted in healthy people who did not have tendinopathy. In another study [14] studied relative contributions of altered material properties and geometry to free AT stress distribution during a sub-maximal contraction in tendinopathic relative to healthy tendons. FEA revealed that tendinopathic tendons experience 24 % less stress under the same submaximal external loading conditions compared to healthy tendons. The lower tendon stress in tendinopathy was due to a greater influence of tendon cross-sectional area, which alone reduced tendon stress by 30 %, compared to a lower Young's modulus, which alone increased tendon stress by 8 %. These findings suggest that the greater tendon cross-sectional area observed in tendinopathy compensates for the substantially lower Young's modulus, thereby protecting pathological tendon against excessive stress. However, both of these studies were devoted to the study of the pathogenetic aspects of tendinopathy.
In our study, we studied the features of load distribution on all structures of the rear foot in conditions of an enlarged retrocalcaneal bursa. FEA revealed a linear relationship between the decrease in load on all structures of the hindfoot with an increase in the height of the insole. High accuracy of the results was achieved due to the large detailing of the three-dimensional model, especially in the places of contact of the bursa with the tendon and calcaneus. In research Wulf, M. et al. [15] tensile load was calculated by measuring the propagation speed of ultrasound, which is governed by the elastic modulus and density of tendon and proportional to the tensile load to which it is exposed. This method makes it possible to obtain the results of the tensile load in the same patient, however, unlike the FEA, this method cannot visualize the distribution of the maximum load on all structures of the hindfoot.
There are several limitations to our study. Firstly, FEA does not allow to calculate absolute values of the peak load. We assumed that the AT material properties were homogeneous, which does not reflect the possibility that tendon material properties could be anisotropic [16] and thereby influence the local stress-strains, particularly in the region of the developing tendinopathy [17]. However as the spatial variations of Achilles tendon material properties are as yet unknown, and may even be homogenous in tendinopathy [18], this assumption seemed justified in the first instance. Secondly, although we were able to match global strains from our model to experimental data, validation of local strain estimates remains challenging [19]. We also assumed that the boundary force applied to our FE model could be represented by the measured ankle joint plantarflexion moment divided by the AT moment arm, which neglects the effects of antagonistic co-contraction and assumes the calculated force is fully transmitted to the AT. Future studies may need to include subject-specific estimates of AT moment arm which may also be assessed using freehand three-dimensional ultrasound [20] and include more detailed muscle force representations via musculoskeletal modelling approaches [21,22]. The effect of more detailed representation of tendon microstructure including tendon tissue architecture and tendon twist [23,24], as well as the effect of calcaneal rotation [25], may also need to be included in future models. It is also conceivable that such models could operate in near real-time and help guide tendon training programs that seek to use targeted mechanical loading as a way of optimizing training adaptation [26,27]. However, even at this stage, the FEA revealed an inverse relationship between the stress on the tendon and the height of the heel elevation.

Conclusions
1. Investigation of the stress-strain state of the rear foot structures by FEA makes it possible to study not only the averaged absolute values of stress, but also its distribution on different structures.
2. In this study, the effect of 10.0-20.0 mm height heel insoles on the stress distribution in the rear foot structures in retrocalcaneal bursitis was determined using computer simulations. It revealed a linear relationship between the decrease in stress on all rear foot structures with an increase in the height of the insole.
3. It was found that when using heel elevation insoles, the stress-strain distribution in different structures was significantly reduced by an average of 20.0-30.0 %.
4. According to the results of the study, we consider it appropriate to include the use of heelelevation insoles with 10-20 mm height to the retrocalcaneal bursitis treatment program. This will achieves a fast pain reduction and prevents secondary degenerative changes in the AT due to overload.