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Characterization of a rat osteotomy model with impaired healing
© Kratzel et al; licensee BioMed Central Ltd. 2008
Received: 26 May 2008
Accepted: 08 October 2008
Published: 08 October 2008
Delayed union or nonunion are frequent and feared complications in fracture treatment. Animal models of impaired bone healing are rare. Moreover, specific descriptions are limited although understanding of the biological course of pathogenesis of fracture nonunion is essential for therapeutic approaches.
A rat tibial osteotomy model with subsequent intramedullary stabilization was performed. The healing progress of the osteotomy model was compared to a previously described closed fracture model. Histological analyses, biomechanical testing and radiological screening were undertaken during the observation period of 84 days (d) to verify the status of the healing process. In this context, particular attention was paid to a comparison of bone slices by histological and immunohistological (IHC) methods at early points in time, i.e. at 5 and 10 d post bone defect.
In contrast to the closed fracture technique osteotomy led to delayed union or nonunion until 84 d post intervention. The dimensions of whole reactive callus and the amounts of vessels in defined regions of the callus differed significantly between osteotomized and fractured animals at 10 d post surgery. A lower fraction of newly formed bone and cartilaginous tissue was obvious during this period in osteotomized animals and more inflammatory cells were observed in the callus. Newly formed bone tissue accumulated slowly on the anterior tibial side with both techniques. New formation of reparative cartilage was obviously inhibited on the anterior side, the surgical approach side, in osteotomized animals only.
Tibial osteotomy with intramedullary stabilisation in rats leads to pronounced delayed union and nonunion until 84 d post intervention. The early onset of this delay can already be detected histologically within 10 d post surgery. Moreover, the osteotomy technique is associated with cellular and vascular signs of persistent inflammation within the first 10 d after bone defect and may be a contributory factor to impaired healing. The model would be excellent to test agents to promote fracture healing.
Ten percent of all fractures require further surgical procedures because of impaired healing . Coles  reported up to 17 percent of nonunions after treatment of closed tibial shaft fractures. Impairment of fracture healing is linked to demographic changes in society e.g. the growing proportion of elderly people and causes not only individual but also economic damage . Hence, by means of in vitro and in vivo experiments, considerable efforts have been made in fracture research to develop therapeutic approaches. Before promising concepts can be used in humans, it is necessary to verify their efficacy and safety in a variety of animal models (for critical review and guidelines see ).
Models simulating impaired fracture healing in animals are not easy to conduct. Animal models of bony nonunion mainly utilize techniques with large segmental defects, thermic treatment of the defect region, instable fixation or combinations of these procedures [5–8].
Descriptions or comparative studies of the different methods used in fracture research are often limited in detail. However, understanding of the biological course of healing is essential for a therapeutic approach and the choice of an adequate animal model can be crucial for the experimental results. Furthermore, with respect to laboratory animal stress and avoiding recurrent failure, we believe that critical reports on an in vivo approach are essential.
The bone healing process is a special form of wound healing. According to Cruess and Simmons [9, 10] the regular course of fracture healing can be broken down into different phases: i the reactive phase, including fracture, haematoma and inflammation whereby the initial inflammation is regarded as an activator of fracture healing ; ii the reparative phase, characterized by callus formation and lamellar bone deposition, and iii the remodeling phase, creating the original bone contour. During this process two types of bone formation are possible: desmal with direct bone formation from mesenchymal progenitor cells and chondral with bone formation from cartilage intermediate.
Impairment of regular osseous healing can result in delayed union or nonunion (also called pseudarthroses). Classification of these cases in humans depends on whether nonconsolidation of bone fragments occurs within 4 or 6 months [12, 13]. Nonunions can be classified as hypertrophic and are termed as vital on the basis of radiological evidence of proliferative external callus formation on the fragment side; if callus formation does not occur, they are termed atrophic [14, 15]. Common reasons for the impaired healing are poor end-to-end contact of the bone fragments, excessive interfragmentary movement and poor blood supply due to insufficient vascularization at the site of the defect or the interaction of all factors [16, 17]. Infection is mentioned as another frequent cause of nonunion .
Rats are the most widely used animal species in bone healing research and osteotomy and closed fracture of long bones are frequently used model techniques . Here we describe the course of delayed healing in an open rat tibial osteotomy model in comparison to a closed fracture model with regular healing in order to find a possible explanation for the impairment of healing.
The animal experiments complied with German legal regulations and were approved by the responsible authorities. Adult female Sprague-Dawley rats (Harlan-Winkelmann) weighing 250–280 g were anaesthetized with isoflurane and by an intraperitoneal injection of a ketamine/xylazine mixture (80 and 12 mg/kg body weight, respectively). After shaving and disinfection of the right lower leg, the medullary cavity of the tibia was opened at the level of the proximal metaphysis and prepared for stabilization using a 1 mm Kirschner steel wire. The steel wire was removed and osteotomy was performed at the midshaft level of tibia using a diamond disk (Horico). The fibula was fractured manually. Osteotomy was stabilized intramedullary with a titanium Kirschner wire coated with PDLLA [20, 21], a prospective carrier for therapeutics. After stabilization the wound was closed by a vicryl suture and gentamycin ointment was applied locally. For pain prophylaxis the animals received buprenorhine (0.05 mg/kg body weight s.c.) for the first 3 days after the intervention. Post mortem, in selected animals that underwent osteotomy, perifractural and titanium wire swabs (MWE) were taken for bacteriological examination. Bacterial growth was analyzed after 48 h of incubation in an external microbiological laboratory. The swabs were screened for anaerobic and aerobic bacteria.
The closed fracture of the tibia and fibula was produced in a standardized manner as published previously [21–23] and the stabilization of the fracture was performed in the same manner as described for the osteotomy model with a PDLLA-coated intramedullary nail.
Animals were regularly monitored radiographically. Mediolateral and anterior-posterior radiographs were taken postoperatively and at 28 d, 42 d and 84 d after surgery.
The animals were sacrificed under anaesthesia by intracardiac injection of calium chloride.
For biomechanical testing ipsilateral and contralateral tibiae of osteotomized animals (n = 18) killed at 28 d, 42 d and 84 d were dissected. The titanium wire was carefully removed under protection of the callus. Proximal and distal of the bone defect the tibia was Technovit-embedded into two moulds (Technovit 9100, Heraeus). Embedding of the contralateral tibia was performed analogous. Each mould was connected to a pivoted axis and the sample was preloaded with an axial force of 5 Newton. A constant linear propulsion (2 mm/min), generated by a material testing machine (Zwick 1455), was applied to a lever attached to one of the pivoted axis for transforming the translation of the material-testing machine to a uniform torsional movement. The other side was connected with a strain gauge (Fmax = 50 N, HBM) which recorded the torsional moment. Subsequently maximum load, torsional stiffness, and energy absorption were calculated. The data were expressed as percentages of those observed with the contralateral tibia not only to avoid interindividual differences in bone constitution, but also with respect to the curved anatomy and the varying cross section shape of the tibia at different levels. Biomechanical data of n = 25 animals, which had undergone the fracture technique , were compared to the open osteotomy model.
Histology and histomorphometry
At days 28, 42 and 84 after osteotomy (n = 6 each time point) tibiae were carefully removed under protection of the callus bone and fixed for 2 days in 10% buffered formaldehyde and dehydrated in ascending concentrations of ethanol and then embedded undecalcified in methylmethacrylate (Technovit 9100, Heraeus). Longitudinal 6 μm thick sections were performed with a Leica SM 2500s microtome and were stained using a combination of Safranin-O/von Kossa for microscopic visualization of mineralized bone matter. Acrylate-embedded bone preparations from earlier studies using the fracture device  were used for comparison.
At days 5 and 10 bone specimen preparations were fixed in formalin for 2–3 days, decalcified with EDTA, processed in ethanol and xylene and embedded in paraffin. Longitudinal 6 μm thick sections were prepared and histological standard staining was performed with Haematoxylin-Eosin (HE), Alcian blue  and Movat-Pentachrom .
HE-staining was used to quantify the dimensions of reactive callus, Alcian blue staining to measure the cartilaginous fraction in callus (zones of hypertrophic chondrocytes) and Movat-Pentachrom to stain for the purposes of visualizing the fraction of newly formed trabecular bone in callus.
The dimensions of specific regions were measured in micrographs of adjacent slices using the Axio-vision 4.0 software. With respect to interindividual varieties, a region of interest (ROI) was established for each preparation i.e. the zone of reactive callus distally and proximally from the centre of bone defect which extended in length 1.5 fold the individual diameter of the cortical bone.
For immunohistological staining of vessels, the slices were rehydrated, blocked with normal horse serum and incubated over night with a monoclonal antibody against α-smooth-muscle actine (α-sma, Daco, dilution 1:100). A rat-absorbed anti-mouse biotin-conjugated antibody (diluted 1:50, 30 min incubation time at room temperature, Vector) served as the secondary antibody. The avidin-biotin-complex detection system (ABC method), coupled with alkaline phosphatase and Vector® red as the chromogen, visualized the antibody binding (10 min incubation time at room temperature). The slices were counterstained with Mayers haemalaun solution (diluted 1:2). The morphology and amount of vessels in the callus were detected using an image analysis system (Zeiss KS 400). Slices from n = 6 animals each were evaluated 5 and 10 d post intervention (for osteotomy and fracture technique).
Biomechanical data of osteotomized and fractured tibiae (at 42 d and 84 d), dimension of whole callus, zones of reparative trabecular bone and zones of hypertrophic chondrocytes of ROI in both groups (at 5 d and 10 d) were compared using the Mann-Whitney U-test.
Surgical procedure and monitoring
The surgical intervention of osteotomy was tolerated by all animals. Up to 3 days after surgery they received pain prophylaxis. However, one undesirable effect observed was that some animals licked their wounds inducing dermal lesions. In two animals there was a slight cranial shift in intramedullary nails.
Biomechanical characterization of the osteotomized tibiae (torsional load and stiffness, as % of contralateral intact tibia, mean ± SD) compared to previously collected data for the fracture model.
15.1 ± 6.0
11.1 ± 9.1
69.0 ± 26.0
61.1 ± 44.5
29.3 ± 21.8
19.0 ± 15.8
129.3 ± 42.6 *
105.1 ± 38.6 *
48.0 ± 20.6
22.7 ± 12.9
173.9 ± 64.0 *
153.2 ± 53.8 *
Screening of the healing process during the observation period (Safranin O/von Kossa staining)
Early reactive callus, dimensions and cellular compartments (HE-staining)
Dimension of reactive callus (mm2) along the tibiae of osteotomized rats compared to fractured animals 5 and 10 days post surgery (mean ± SD).
16.7 ± 4.6
13.2 ± 4.7
3.6 ± 0.7
12.6 ± 1.7
10.3 ± 1.7
4.1 ± 1.4
27.1 ± 11.3
15.7 ± 8.3
11.4 ± 4.4
16.0 ± 3.4 *
8.9 ± 2.3
7.0 ± 2.6
The cellular composition of callus consisted mainly of reparative granular cells (fibroblasts), inflammatory cells, chondrocytes and osteocytes or their progenitors and of extracellular matrix in both groups.
Early angiogenesis (a-sma staining)
Amount of vessels per mm2 in the callus (ROI) of osteotomized rats compared to fractured animals (mean ± SD).
46.6 ± 11.4
46.2 ± 18.4
39.6 ± 23.6
43.6 ± 15.0
50.2 ± 22.8
35.6 ± 5.9
37.0 ± 15.6
57.7 ± 25.2
14.6 ± 6.8
15.0 ± 4.8 *
18.2 ± 4.1 *
11.5 ± 7.2
Early fraction of woven bone and cartilaginous tissue (Movat Pentachrom staining and Alcian blue staining)
Formation of newly formed bone in % of reactive callus (ROI) in osteomized rats compared to fractured animals 5 and 10 days post surgery (mean ± SD).
7.2 ± 9.6
8.2 ± 14.5
8.7 ± 9.8
8.9 ± 7.2
4.6 ± 5.7
16.4 ± 11.3
17.2 ± 8.4
7.5 ± 7.3
26.2 ± 9.1
34.8 ± 8.0 *
24.9 ± 7.8 *
48.8 ± 16.2 *
Formation of cartilaginous tissue in % of the callus (ROI) in osteomized rats compared to fractured animals 5 and 10 days post surgery (mean ± SD).
0.2 ± 0.3
0.3 ± 0.5
2.25 ± 1.4
2.4 ± 2.2
1.9 ± 2.0
9.9 ± 7.7
2.8 ± 2.9
16.7 ± 13.7
22.1 ± 8.0 *
25.0 ± 9.0 *
17.6 ± 9.8
Spot check sampling and analyses of sterile swab tests from 18 animals at different time points after open osteotomy (i.e. at 29, 42 and 84 d) revealed positive results for S. aureus in 4 animals. Sample collection for these positive swabs was performed twice around the callus and twice intramedullary. In this context, it should be pointed out, that the animals with positive bacteriological results for S. aureus showed no macroscopic signs of purulence and must therefore be deemed to be subclinically infected.
In order to evaluate an applicable in vivo model for local therapeutical targeting, we investigated the impaired healing course of a rat tibial osteotomy with intramedullary stabilization compared to a previously described closed fracture model with regular healing.
Surgical procedure of rat tibiae osteotomy as performed in this study or applied in other studies [27, 28] generates a unique phenotype of bone defect according to the AO-classification for fractures (42A3). Hence, it provides consistent preconditions for further investigations. In contrast, the use of a fracture device could lead to inconsistent fracture types .
Radiological, biomechanical and histological screening during the observation showed a clear course of impaired bone healing. Even after 84 d the osteotomized tibiae were far from the stage of remodeling the original bone structure. At best, defect bridging occurred periosteally but not interfragmentary as seen in the fracture model . Primary periosteal bridging is an integral part of the approximately 5 week bone healing process in rats and has been described as species-specific . On the other hand, a contributory factor may be the use of the intramedullary stabilisation technique.
The development of delayed healing after tibial osteotomy in direct comparison to the closed fracture technique was previously documented in a rabbit model by Park et al.  using an external fixator for stabilization of the bone defect. These authors showed respective differences two weeks post bone defect, but these had disappeared at later observation time points. In a study with rats Kokubu et al.  developed a femoral model with 100% nonunion up to 56 d post surgery. However, as an effect of cauterization on each side of the fracture, the radiographical appearance of nonunions was atrophic.
Compared to our previously reported study in rats which underwent closed tibial fracture with the same intramedullary stabilization, clear differences in the biomechanical properties of the osteotomized tibiae could be observed in contrast to the fractured tibia. The osteotomized tibiae showed significant lower values for maximum torque and torsional stiffness after 42 and also 84 days as compared to the fractured tibiae. Even though sample preparation for biomechanical testing at an earlier time point (28 d) was not possible for all osteotomized bone samples, mainly due to the very instable callus, the results were in accordance with those in a study from Shefelbine et al.  demonstrating also very low biomechanical data 21 d after rat tibial osteotomy.
Although our results can only be interpreted cautiously because of the small sample size investigated, the comparative examination of osteotomized and fractured bones in the present study gave evidence, that the course of delayed healing in osteomized animals is determined already before day 28 after surgery.
Histological investigations comparing the two different techniques even in earlier healing phases, at 10 d post bone defect, also revealed differences: The histomorphometric analyses showed that the amounts of accumulated desmal formed reparative bone tissue and of differentiated cartilaginous tissue were retarded in the region of the osteotomy defect compared to the fracture.
Less deposition of trabecular bone could be found on the anterior tibial side for both groups. One compounding parameter may be the weakly developed soft tissue envelope on the anterior tibial side. Moreover, comparison of the regional accumulation of differentiated cartilage revealed that osteotomized animals accumulate lower amounts of differentiated cartilaginous cells on the anterior side where the surgical approach was located. We therefore conclude that the choice of surgical approach can influence the local formation of reparative cartilaginous tissue.
Furthermore, in the callus of osteotomized rat tibiae we found numerous amounts of inflammatory cells. Additionally the number of vessels in callus was significantly higher than in the callus of fractured tibiae, where the amount decreased between 5 and 10 d post intervention. Comparable results i.e. an initial relatively constant number of vessels in the callus of tibiae with induced impaired healing in contrast to a decreased number in the regular healing group were shown in osteotomized sheep . We would interpret these observations in the present study as a prolonged and pronounced inflammatory reaction occurring in all osteotomized rats. In fact, microbiological screening revealed persistent subclinical infection in a subset of the osteotomized animals. This can hardly be avoided given the keeping conditions and activities of the laboratory animals. For a rabbit model, Melcher and colleagues  showed even higher infection rates. Therefore, adjuvant systemic antimicrobial prophylaxis should be considered in future animal studies. Thus, tibial osteotomy has a higher chance of infection than closed fracture, something that also occurs in surgical treated closed tibial fractures in humans .
What could be a reasonable explanation for the delayed bone healing in all osteotomized animals in this study? Radiologically, we could rule out poor end-to-end contact of osteotomy gap. Another frequently quoted cause could be a high degree of instability in the osteotomized bone, concerning the rotation movement . But all animals were stabilized in the same manner as described for the healing fracture model and breed, weight and sex were analogous. Although this was not examined in any comparative measurements, differences in instability were not obvious in either group. However, variations within minimal interfragmentary movements cannot be ruled out. In fractured animals we observed the deposition of more defect-associated cartilage, pointing to a possible higher degree of instability capable of modulating the healing process [35, 36]. The comparative analysis of tibia and fibula in osteomized animals may support this hypothesis as more cartilaginous tissue formation was detected around the fractured and unstabilized fibula than around the stabilized tibial gap in histological bone slices from the same individual. However, the fibula was broken manually and the tibia by osteotomy. Both of these parameters can influence the outcome.
Poor vascularization would be an implausible reason for non-union. The calluses appeared hypertrophical radiologically and well vascularised histologically. Bone necroses at the fragment sides were not observed and severe injuries of the bone's nutrient vessels were not conspicuous during surgery.
Furthermore, proliferating mesenchymal stem cells from bone marrow are though to play a key role in bone repair [37, 38]. Primarily used for cooling purposes, open techniques require irrigation and it cannot be ruled out that progenitor cells were washed out. However, haematoma removal within the first hour was shown to be of no relevance for the healing progress .
The most plausible explanation for nonunions in this study may be an extended spatio-temporal inflammation and granulation phase, identifiable by dimensions, prolonged inflammatory cell composition and initial vascularization. Local infection as detected in a subset of animals may be a contributory factor but aseptic inflammation leading to nonunion  could be assumed to play a main role in our model.
As known from in vitro cell culture systems, environmental changes have the potential to influence the differentiation and functioning of cells. Regardless of the importance of inflammation for initializing the healing process, severe soft tissue trauma and the linked excessive release of inflammatory mediators can be discussed as factors to have a negative impact on bone healing .
Irrespective of the initial trigger, consideration should be given to whether persistent early inflammation could be a basic principle for nonunions.
The open tibial osteotomy technique combined with intramedullary stabilization in rats leads to pronounced impairment of bone healing. Prolonged local initial inflammation is suggested as a causative mechanism.
We conclude that the reported osteotomy model is not suitable to provide insight into normal bone healing. Nevertheless, it could be used as a delayed healing model. As known from previous studies, PDLLA coating of the titanium implant has no negative effect on bone healing (21,24). Thus, further investigations with therapeutic application of pharmaceutical agents (e.g. growth factors) via the PDLLA-coated implant should allow evaluation of the potency of locoregionally administered drugs for nonunion therapy.
We thank Alexander Schill, Martin Wolny and Mario Thiele for excellent technical assistance. C K like to thank Dr. Stephan Pauly and is particularly grateful for sustained support to the Berlin Center of regenerative Medicine (BCRT), and BW and GS would like to acknowledge the Deutsche Forschungsgemeinschaft (DFG, SFB 760) for funding this study.
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