mandibular reconstruction – biomechanical strength ... · after mandibular body resection due to...

Acta of Bioengineering and Biomechanics Original paperVol. 15, No. 2, 2013 DOI: 10.5277/abb130203

Mandibular reconstruction– biomechanical strength analysis (FEM)

based on a retrospective clinical analysis of selected patients

MAGDALENA JĘDRUSIK-PAWŁOWSKA*1, MAGDALENA KROMKA-SZYDEK2,MAGDALENA KATRA1, IWONA NIEDZIELSKA1

1 Department of Cranio-Maxillofacial and Dental Surgery, Medical University of Silesia, Katowice, Poland.2 Department of Experimental Mechanics and Biomechanics, Cracow University of Technology, Poland.

Restoration of mandible discontinuity defects continues as a challenge for maxillofacial surgeons. Despite the development of algo-rithms for reconstruction plates fixation and autogenous grafting techniques, complications are still encountered including screw loosen-ing, bone resorption or delayed/incomplete union.

The aim of the study was to analyze the possibility of obtaining bone union in the aspect of biomechanical conditions of two mandi-ble reconstructions using an autogenous iliac crest bone graft stabilized with a reconstruction plate, and to attempt to predict patientoutcomes based on strength parameters obtained by the finite element analysis.

The authors of the present paper were trying to determine to what extent the reconstruction model and changes occurring in hard tis-sues of the bone and autogenous graft (simulated by changes in material properties) might help predict individual patient courses. Theeffort of reconstruction plates was defined using the values of the von Mises stress (σHMH) while the effort of bones was determinedbased on the values of strain intensity εint. The results of the above mentioned simulations are presented in the form of bar graphs andstrain/stress distribution maps. Our strength analyses indicate that uncomplicated healing of grafts fixed with reconstruction plates re-quires that the initial loading of the stomatognatic system should not result in strain intensity exceeding 20–40 [×10–4]. This range ofstrain intensity evokes an increase in the mineral phase. The state of nonunion between the mandibular bone and the graft might resultfrom prolonged periods of insufficient loading of the mandible during treatment.

Key words: bone grafts, mandibular reconstruction, finite element method (FEM), reconstruction plates, bone healing

1. Introduction

Better technologies and strategies are needed forreconstruction of large facial defects in order to notonly restore facial contour but also function (for func-tional and aesthetic restoration).

A large variety of oncological, traumatic and in-flammatory pathologies of the face, which can causebone discontinuity both as a result of the diseaseprocess and treatment are described in related litera-ture [1]–[4]. The consequences include obstruction

of air passages, restriction of food intake, mucusstasis, speech disturbances and facial disfigurement.Therefore, each and every mandible discontinuityshould be restored. Autogenous bone grafts stabi-lized with titanium reconstruction plates are thetreatment of choice. Reconstruction plate fixationschemes are, of course, demonstrated by plate manu-facturers and company representatives. Instructionsare provided regarding plate fixation which permitsthe optimum healing; this involves appropriate platecontouring to the surface of the bone, insertion of theright number of screws in each bone fragment, and

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* Corresponding author: Magdalena Jędrusik-Pawłowska, Department of Cranio-Maxillofacial and Dental Surgery, Medical Universityof Silesia, ul. Francuska 20/24, 40-027 Katowice, Poland. Tel: +48 502 26 26 98, fax: +48 32 256 26 49, e-mail: [email protected]

Received: March 16th, 2012Accepted for publication: February 13th, 2013

M. JĘDRUSIK-PAWŁOWSKA et al.24

plate positioning [2], [3], [5], [6]. However, the widediversity of clinical cases, intraoperative findings,surgeon’s experience and, last but not least, highlyindividual course of the healing process frequentlyhinder the therapeutic efforts of maxillofacial sur-geons. Thus, a common algorithm should be devel-oped to reduce complication rates.

The purpose of the present study was to performa biomechanical assessment of the bone healing proc-ess using a numerical analysis by the finite elementmethod (FEM). Such calculations, based on someselected strength parameters, allow objective evalua-tion of changes which occur within the bone/graftinterface and in implanted elements.

A biomechanical analysis of a system composed ofthe mandible, graft and reconstruction plate facilitatesthe assessment of whether, and to what extent, thefunction of the stomatognatic system has actuallybeen restored; thus, treatment effectiveness can alsobe determined. Numerical simulations enable re-searchers to define the optimum surgical fixationmethod, compare the efficiency of various recon-structions or analyse mandibular bone remodelingduring healing.

Numerical simulations are highly reproducibleand, additionally, less costly and more effective com-pared to clinical and laboratory investigations. Theyalso allow analysis of various cases taking into con-sideration the object’s geometrical variables, materialconstants and boundary conditions.

The aim of the study was to analyze the possibilityof obtaining bone union in the aspect of biomechani-cal conditions of two mandible reconstructions usingan autogenous iliac crest bone graft stabilized witha reconstruction plate, and to attempt to predict patientoutcomes based on strength parameters obtained bythe finite element analysis.

2. Materials and methods

In the years 2005 through 2011, four patients un-derwent mandibular reconstruction in the Departmentof Cranio-Maxillofacial and Dental Surgery, MedicalUniversity of Silesia, Katowice. The reconstructionswere performed using an autogenous bone graft and2.4 mm Synthes titanium reconstruction plates. Twoof these were selected for strength analysis by thefinite element method (FEM).

Patient 1 (uncomplicated healing during a three-year observation period): a 46-year-old female patientafter mandibular body resection due to ameloblastoma

and mandibular reconstruction using full-thicknessiliac crest bone graft fixed with a contoured 17-holeSynthes titanium reconstruction plate (2.4 mm) and 10UniLock screws: 3 screws were placed in the distalmandibular stump, 5 in the graft and 2 in the mesialmandibular stump. The plate was carefully contouredto the surface of the bone and placed closely to thelower mandibular margin so that it would be suffi-ciently covered by soft tissues (Fig. 1). The patientwas on a dental soft diet for 6 weeks following thereconstruction, and then gradually advanced to reha-bilitation of masticatory function through dental resto-rations. The surgery resulted in mandibular contourreconstruction; facial symmetry and aesthetics as wellas basic masticatory function and bite force were re-stored (Fig. 2a, b).

Fig. 1. Patient 1: Panoramic radiographfollowing mandibular body resection and reconstruction

using autogenous full-thickness iliac crest bone graft stabilisedwith a 2.4 mm titanium reconstruction plate

Patient 2 (delayed union, prolonged healing pe-riod): a 42-year-old male patient after several unsuc-cessful attempts of comminuted mandibular fracturereduction and resultant pseudoarthrosis. A partialthickness defect of 1 cm in length was filled with anautogenous graft of cancellous iliac crest bone andstabilized using a 7-hole Synthes titanium recon-struction plate (2.4 mm) with 2 UniLock screws ineach mandibular stump. The plate connecting bothstumps ran obliquely and upwards on the outer sur-face of the mandible towards the mandibular angle(Fig. 3a, b, c). The healing period was markedlyprolonged and c complicated by bone fragments mo-bility and facial asymmetry. Therefore, the positionof the mandible relative to the maxilla was securedby interarch fixation wires for 8 weeks followingsurgery. Ultimately, over 2 years after the procedure,bone union occurred and normal dental occlusion aswell as masticatory function and bite force were re-stored (Fig. 4a, b).

Mandibular reconstruction – biomechanical strength analysis (FEM)... 25

Fig. 3. Patient 2: Panoramic radiographs:(a) prior to reconstruction; notice the pseudoarthrosis

in the left molar region of the mandible with a 1 cm partialthickness defect (arrow); (b) after mandibular reconstruction

with autogenous graft of cancellous iliac crest bonestabilised with a 2.4 mm titanium reconstruction plate;

(c) 2 years and 4 months after reconstruction(note normal trabecular architecture and bone

remodeling at reconstruction site (arrow))

Numerical analysis of the cases under considerationwas performed using (CAD) FEMAP®. Teeth weredisregarded and alveolar processes ‘replaced’ by themandibular osseous tissue. The coronoid process,pterygoid fovea, mental spine and masseteric tuberositywere also disregarded. The resultant numerical modelof the mandible was assigned appropriate material con-stants, i.e., elasticity modulus E = 18000 [MPa] andPoisson’s ratio ν = 0.32. A simplified model of the tem-poromandibular joint consisted of the articular disc andarticular surface of the temporal bone. Consistent withliterature data [7], material constants of the articularmodel components were E = 50 [MPa] and ν = 0.45, andE = 15000 [MPa] and ν = 0.32, for the articular disc andtemporal bone, respectively. An element was also takeninto consideration corresponding to the biomechanicalproperties of anterior teeth periodontium. According tothe preassumed load scheme, the system was con-strained on the surface of the temporal bone and theperiodontium-corresponding element.

The autogenous, iliac bone-harvested graft ofPatient 1 was assigned material constants of E =8000 MPa and ν = 0.35. Simulations concernedchanges in callus mineralization between the initialphase of the healing process and ultimate bone unionabout 6 to 8 weeks following the procedure. Minerali-zation changes were simulated by changes in the elas-ticity modulus of a callus-modelling element for thevalues of 2, 5, 10, 25, 50, 75, 100, 125, 150, 175 and200 MPa. Accepted values are approximate and aresome extrapolation between the range of 2 MPa, inthe early stages of healing and 200 MPa in the end,fed by Knets et al., because the literature does notprovide a more detailed description of the changes inthis value [8].

The second patient’s mandibular defect was recon-structed using the cancellous bone of the iliac crest.

Fig. 2. Patient 1: (a) photograph of the patient’s face; (b) intraoral image 2 years after reconstruction


Devising a model of such material is extremely difficultdue to the lack of the properties of solids. We ulti-mately decided to simulate mineralization changes as inthe case of callus, i.e., by changes in the elasticitymodulus. However, a greater range of values was takeninto consideration, i.e., from 2 MPa (corresponding tobone status immediately following surgery) and up to1000 MPa (final stage of treatment – complete bonemineralization). The models of bone fragments weredesigned to imitate the shape of bone stumps and theirpost-reconstruction status (Fig. 5a, b).

The models were exported to (FEM) ANSYS®,and subjected to loading. The load scheme was basedon the following assumptions:

• the actions of four muscles were considered, i.e.,of the temporal, masseter, medial and lateral pterygoidmuscles;

• force application was at the site of muscle inser-tion and consistent with the size of the respective in-sertion area; percentages and average directions of theforces were based on literature [9]–[11];

• the load model included typical bite forces; theresultant (total) muscle force was assumed to havea value of 100 [N] [12]. Since loads are considera-bly lower at initial stages of the healing process,load change simulations depending on the healingphase were carried out for Patient 2 (load range:10 N to 100 N).

Fig. 4. Patient 2: (a) photograph of the patient’s face; (b) intraoral image 2 years after reconstruction

Fig. 5. Numerical models of the cases under analysis: (a) Patient 1; (b) Patient 2

Table 1. Strain intensities corresponding to bone tissue response to particular loads

Load characteristics Strain intensityε [ × 10–4 ] Bone tissue response

Destructive loads >(150–200) Destruction of bone tissue

Pathological overload >40 (approx. 60) Resorption, microfractures(plastic deformations)

Increased load but stillwithin physiological range 20–40 Increase in bone mineralization

Physiological load 2–20 Bone tissue equilibriumUnderload < 2 Decrease in bone mineralization


As accepted by the majority of authors [5], [10],[13]–[15], the effort of reconstruction plates wasdefined using the values of the von Mises stress(σHMH). The effort of mandibular hard tissues andautogenous grafts was determined based on the val-ues of strain intensity εint (Table 1). Changes in straindistribution are the most important factor to stimu-late adaptive responses of the bone tissue associatedwith mechanical deformation field [9]. The analyseswere carried out for the proximal and distal osteot-omy lines.

3. Results

Bar graphs (Fig. 6a, b) present changes in strainintensity εint associated with the degree of bone miner-alization (i.e., healing phase) for a load of 100 N ap-plied in the incisor area (Patient 1).

The values of strain intensity εint are greater in theproximal segment due to the assumed incisor load andthe complex character of mandibular stresses. Themental and incisor areas, i.e., the proximal line area,are subject to bending and torsional stress whereas thearea towards the mandibular angle is subject to bend-ing stress only.

Strain intensity in the proximal area remainswithin the state of equilibrium and mineralizationincrease. Once callus elasticity modulus reaches thevalue of 5 MPa (initial healing phase), the systemcould be loaded, which probably increases the mineralphase and facilitates graft incorporation. As Patient 1did not have maxillomandibular fixation, she wascapable of mandibular abduction immediately fol-lowing surgery. Afterwards she started to graduallyload the system with dental soft diet which ultimatelyresulted in correct union.

The bar graph in Fig. 7 presents strain intensitiesfor proximal and distal parts of cancellous bone graft

Fig. 6. Patient 1: (a) mandibular bone: strain intensity in the proximal and distal bone/graft interface;(b) iliac crest graft: strain intensity in the proximal and distal graft/bone interface


in Patient 2. The loads were between 10 N and 100 Ndepending on the degree of bone mineralization (i.e.,healing phase).

Higher loads applied in the initial phases of heal-ing resulted in strain intensities corresponding topathological overloads that might lead to microfrac-tures and resorption.

Following mandibular reconstruction, the forceacting on the stomatognatic system will be below 100 N.However, it should not be too low. The graphs repre-

senting strain intensity changes associated with thechanges in the total force values indicate that althoughlower loads evoke physiological bone tissue responsein the proximal segment, the distal fragment revealsa decrease in bone mineralization

A load of approximately 30 N could be safely ap-plied in a patient already in the initial phase of heal-ing. Higher loads (e.g., 60 N) should be postponeduntil later time when the graft elasticity modulus in-creases to around 100 MPa (Fig. 8).

Fig. 7. Patient 2: The graft – mineralization stage dependent strain intensities at particular load values(proximal and distal areas)

Fig. 8. Patient 2: Proximal graft area – strain intensity at the loads of 30 and 60 N


Figure 9a, b presents the distributions of the vonMises stress in both reconstruction plates (Patients 1and 2) under analysis. The distributions are similar,the greatest effort being observed in the proximalsegment of the mandible–graft system.

4. Discussion

The authors of numerous reports published duringthe last few years have been trying to elucidate thebiomechanical causes of mandibular reconstructionfailures. The evaluation of reconstruction techniquesincluding graft type and size as well as the type of sta-bilizing elements is carried out using computer-generated models, which are, of necessity, simplifica-tions of real phenomena [5], [6], [14], [16]–[21]. Themost significant thereof is treating the mandibular boneas an isotropic material, characterized by two materialconstants only, i.e., the elasticity modulus and Pois-son’s ratio [5], [16], [20]. The load of 100 N assignedin our investigations was used exclusively for simula-tion; its value is nevertheless consistent with that ap-plied by other investigators [5], [14], [18], [21].

In maxillofacial surgery there are no clear-cut sug-gestions regarding the magnitude of mandibular hardtissues and graft effort. Therefore the effort of recon-struction plates was defined using the values of thevon Mises stress while the effort of bones was deter-mined based on the values of strain intensity εint,which is in accordance with available literature on thesubject [5], [10], [13], [22].

Literature reports enumerate several mechanicalstimulators of the bone tissue remodeling process. Themost popular is the theory of functional adaptation ofthe bone to strain distribution. Changes in strain dis-tribution are the most important factor to stimulate

adaptive responses of the bone tissue associated withmechanical deformation field [20], [22].

Our analysis along with literature data seems toindicate that correct healing of reconstruction plate-fixed grafts depends on many factors. For example,the initial load on the stomatognatic system should notexceed magnitudes which induce strain intensity of20–40 [×10–4]. As long as strain intensity remainswithin this range, the mineral phase increases.

The biomechanical analysis suggests that Patient2’s mandibulomaxillary fixation should have beenremoved before week 8 after surgery. Prolongedplacement could have resulted in stomatognatic sys-tem underloading, mineralization decrease and de-layed healing. It should be emphasized that the check-up did not reveal any inflammatory complications thatcould also lead to graft bone resorption. Eight weeksfollowing the procedure the patient started rehabilita-tion of masticatory function, which resulted in correctmineralization of union site and autogenous cancel-lous bone graft remodeling.

The evaluation of mandibular reconstruction is ad-ditionally hindered by the adaptation of the graft tothe surrounding tissue. Graft incorporation is associ-ated with both bone resorption and bone formationprocesses followed by bone remodeling. Correct un-ion between the graft and mandibular bone is deter-mined by the type of material used for reconstruction.Nagasao et al. observed that greater mastication-related stresses were transferred onto the recon-structed system in the case of a thinner bone beingused for reconstruction (the fibula or rib) [18]. Thewidely preferred, most advantageous from the biome-chanical point of view and therefore also used in ouranalysis, is the iliac crest. This bone also providesa larger contact surface with the recipient site [3],[19]. Tie et al. found that the von Mises stress distri-bution in mandibles repaired with iliac crest grafts

Fig. 9. The von Mises stress distribution σHMH [MPa] in reconstruction plates: (a) Patient 1; (b) Patient 2


was more similar to the normal mandible when com-pared with mandibles repaired using the fibula [19].Unfortunately, the authors did not stabilize the graftswith reconstruction plates.

During the initial phase of the incorporation proc-ess, the graft is not stabilized relative to mandibularfragments. Numerous authors have emphasized theneed for a reinforcing element that would take overa part of the functional load in the initial phase oftreatment thus reducing the stress resulting from themasticatory forces and facilitating the union betweenmandibular bone and the graft [3], [16]. Mandibularplating allows more rapid resumption of oral functionsand secures the graft to the mandibular segments evenin the case of large sized grafts. It also allows betterreconstruction of facial contours.

The results of Kimura et al. suggest that adequatefixation with a reconstruction plate requires avoidanceof stress concentration in some parts of the plate andscrews [23]. Uniform stress distribution, dependent onthe site and size of bone defects, helps avoid compli-cations including screw loosening, plate exposure ormastication-induced fractures [9], [23].

Our patients presented mandibular body defects(lateral defects). Patient 1 had an 8-cm defect recon-structed with a free cortico-cancellous graft. Patient 2had a 1 cm partial thickness defect repaired with can-cellous bone chips. In both patients, iliac crest bonewas used for reconstruction. The difference betweenthe graft and mandibular bone was simulated bychanges in material constants.

There are discrepancies in literature reports re-garding the number of screws to be used to secure thereconstruction plate on both mandibular stumps. Pre-viously it was believed that longer plates and morescrews increased stability and prevented complica-tions such as titanium elements loosening and non-union [2], [3]. Mariani et al. argue that a reconstruc-tion plate should be well aligned on the adjacent sur-face of the mandible and fixed with at least 3 screwson each side of the reconstructed segment [2].

Schuller-Götzburg et al. carried out biomechanicalanalyses on a three-dimensional finite element modelof a mandible following resection and reconstructionusing different methods. The aim of their investiga-tions was to determine stress distribution differencesbetween the bone, graft and reconstruction plate. Theyconfirmed the stabilizing role of a reconstructionplate. However, they also remarked that such platesshould not be too rigid so as not to delay graft unionand incorporation [14].

Kimura et al. notice that, in the case of lateral de-fects, adding a third screw for fixation in each man-

dibular stump increases stress due to system over-loading [23]. This can result in screw loosening andloss.

We did not observe screw loosening during a two-year observation period. Therefore we believe that thedecision to secure the reconstruction plate with twoUniLock screws was the right one.

The results of numerical simulations indicate thatthe most intense stress occurred around plate holes atthe proximal graft/bone interface, which is consistentwith other authors’ observations [18]. Hard mandibu-lar tissue necrosis develops relatively frequently in thearea of graft/bone interface while inflammatory com-plications are observed in contact areas betweenplate/screws and tissues [13]. This is confirmed bystrain intensity values associated with greater loadingforces and bone effort at the site of screw insertion.Post-reconstruction patients should therefore be care-fully monitored with special attention to radiologicalcheck-up of screw position.

Mandible plating allows the implementation offunctional therapy immediately after surgery andthereby avoiding problems related to the predomi-nance of bone resorption over bone formation. How-ever, X-rays still reveal predominance of bone forma-tion in the proximal end of the graft compared to itsdistal part [24]. Patient 1 also had higher strain inten-sities at the proximal graft/bone interface.

Our analyses concerned two extreme cases andtechniques of reconstruction plate placement, size,position relative to the lower margin of mandibularbody, method and duration of mandibular fixation.Also, although harvested from the hip bone, the twografts had different tissue composition. The use ofnumerical analysis can pre-assess the extent to whichadvanced technology allows satisfactory long termoutcome of reconstruction and restore biomechanicalfunction of the mandible reconstructed.

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