Can changes in implant macrogeometry accelerate the osseointegration process?: An in vivo experimental biomechanical and histological evaluations.

OBJECTIVES: The propose was to compare this new implant macrogeometry with a control implant with a conventional macrogeometry.
MATERIALS AND METHODS: Eighty-six conical implants were divided in two groups (n = 43 per group): group control (group CON) that were used conical implants with a conventional macrogeometry and, group test (group TEST) that were used implants with the new macrogeometry. The new implant macrogeometry show several circular healing cambers between the threads, distributed in the implant body. Three implants of each group were used to scanning electronic microscopy (SEM) analysis and, other eighty samples (n = 40 per group) were inserted the tibia of ten rabbit (n = 2 per tibia), determined by randomization. The animals were sacrificed (n = 5 per time) at 3-weeks (Time 1) and at 4-weeks after the implantations (Time 2). The biomechanical evaluation proposed was the measurement of the implant stability quotient (ISQ) and the removal torque values (RTv). The microscopical analysis was a histomorphometric measurement of the bone to implant contact (%BIC) and the SEM evaluation of the bone adhered on the removed implants.
RESULTS: The results showed that the implants of the group TEST produced a significant enhancement in the osseointegration in comparison with the group CON. The ISQ and RTv tests showed superior values for the group TEST in the both measured times (3- and 4-weeks), with significant differences (p < 0.05). More residual bone in quantity and quality was observed in the samples of the group TEST on the surface of the removed implants. Moreover, the %BIC demonstrated an important increasing for the group TEST in both times, with statistical differences (in Time 1 p = 0.0103 and in Time 2 p < 0.0003).
CONCLUSIONS: Then, we can conclude that the alterations in the implant macrogeometry promote several benefits on the osseointegration process.

Introduction

Osseointegrated titanium implant is frequently used for rehabilitation of loss organs due different causes, mainly trauma or diseases. It has been shown that titanium has properties that stimulate its interaction with bone tissue [1,2], presenting mechanical characteristics that adequately support the physiological stimuli (loads) received when in masticatory function [3]. Moreover, titanium implants show a good degree of predictability and durability, which are demonstrated by clinical studies [4,5].

Even with the high success rates achieved by implants, studies have been made to accelerate the osseointegration with different technologies and manufactures methods. In this sense, alterations in the micro- and macrogeometry of the implant design are presented [6-8]. New surface treatments (micro topography), changing the physical and/or chemical characteristics [6,9,10], and new macrogeometries changing the implant design [11-13], are created by the researchers and, posteriorly, manufactured by the industry. These changes have resulted in better biological performance, as demonstrated in previous preclinical studies [14-16].

The surgical technique used to elaborate the osteotomy and the macrogeometry of the implant are also factors considered of great importance in the process of osseointegration [17]. Currently, different implant designs with varying topographies on their surface are industrialized and marketed worldwide [18-20], and each implant model follows specific recommendations determined by the manufacturer for its installation [21]. Surgically, the drilling step to prepare the site to install the implant utilizes an elaborate drill sequence system for implants to reach a high final insertion torque. However, depending on the bone density at the implant site, these high torque levels may cause an increased inflammatory response and, in some cases, necrosis in areas around the implant [22-24].

Taking these concepts into account, recent new studies have proposed changes in the relationship between the size of the osteotomy for implant placement, ie, a drilling where the bed size is closer to the outside diameter of the implant threads, thus, decreasing the insertion torque of the implant and, consequently, the compression of bone tissue around of the implant [25,26]. Recently, Jimbo et al. demonstrated in their studies in dogs, where they compared the osteotomy with conventional drilling with over-drilling, that high torque levels promoting, in some areas of contact between bone and implant, a formation of necrotic bone tissue; while in implants where a over-drilling for the osteotomy was performed, a larger formation of new bone was observed [26]. Overweight in this case provided less compression and free spaces, which functioned as healing chambers.

The new implant macrogeometry was developed with a healing chambers on their body in order to decrease the compression on the bone tissue without changing the drilling system sequence. Then, the propose of this preclinical study was to evaluate and compare, thought biomechanical and microscopical analysis, the behavior of this new implant macrogeometry using conventional commercialized implant macrogeometry as a control. The hypothesis was that this changes in the implant macrogeometry can accelerate the osseointegration process.

Materials and methods

Eighty-six titanium implants manufactured in commercially grade IV titanium were used in the present study. Forty-three implants with the conventional macrogeometry (Due Cone Implant) and 43 implants with a new macrogeometry (Maestro Implant), both manufactured by Implacil De Bortoli Ltda (São Paulo, Brazil) with 9-mm in length and 4-mm in diameter, forming the group CON and group TEST, respectively. The conventional macrogeometry (group CON) showed a conical implant body and trapezoidal threads design; whereas, the new implant macrogeometry (group TEST) showed a similar conical body and trapezoidal threads plus the creation of circular healing chambers between the threads. All implants presented surface treatment (rugosities) made by blasting with microparticles of titanium oxide (~150 μm) plus acid conditioning (maleic acid). All implant samples were prepared to commercialization. The Fig 1 show a representative image of both implants used.

Fig 1

Schematic image of the implant models evaluated: The conventional implant macrogeometry (Group CON) and the new implant macrogeometry (Group TEST).

Three samples of each group were evaluated using a scanning electronic microscopy (SEM, Philips XL30, Eindhoven, The Netherlands) to describe some morphological characteristics.

For this experimental animal study, twenty laboratorial rabbits (white New Zealand model), with weight between 4 and 5 Kg, were used. Previously, the study protocol was analyzed and approved by the animal committee of the University of Rio Verde (Rio Verde, Brazil) with the number 02-17/UnRV. All animals were care and management in accordance with our traditional protocol applied in other studies [14,15]. International guidelines for animal studies were followed. All titanium implants (n = 40 per group) were implanted in the rabbit tibias (n = 2 per tibia). The localization of the implants in each tibia (proximal or distal) was made using a website (www.randomization.com). Moreover, due to the difference between the proximal portion of the joint, where the bone tissue is much more medullary and of lower density, all implants were installed in a more central area of the tibia, which is schematically shown in the Fig 2.

Fig 2

Representative image of the position predeterminate to install the implants (between the red lines), avoiding the most proximal position where bone tissue is less dense.

For the intramuscular anesthesia were used 0.35 mg/kg of ketamine (Ketamina Agener®; Agener União Ltda., São Paulo, Brazil) plus 0.5 mg/kg of xylazine (Rompum® Bayer S.A., São Paulo, Brazil). The incision was made at ~10 mm from the proximal articulation to distal direction, totalizing of ~30 mm. The bone was acceded, and the perforations were proceed using a drilling sequence preconized for this implant system (2 mm, 3.5 mm and 4.0 mm conical drills). All osteotomies were performed under irrigation with distillate water at 20 ± 2 °C.

The implants were installed in the bone manually, with a torque of ~20 N. Approximately 10 mm of distance were observed between the implants. Then, the suture was performed using a simple point with Ethicon nylon 4–0 (Johnson & Johnson Medical, New Brunswick, USA). After the implantation, all animals received an intramuscularly injection with a single dose of 0.1 ml/kg of Benzetacil (Bayer, São Paulo, Brazil) plus three doses (one per day) of 3 mg/kg of ketoprofen (Ketoflex, Mundo Animal, São Paulo, Brazil). The sacrifice was made with an overdose of anesthesia at 3- and 4-weeks after the implantations. Both tibias with the implant samples were removed and immediately immersed in a 4% formaldehyde solution.

Implant Stability Quotient (ISQ) measurement

The measurement of the implant stability was performed thought the Osstell device (Osstell AB, Gothenburg, Sweden). The smartpeg magnetic sensor was positioned, screwed and torqued for each implant at 10 Ncm, as preconized in a recent study [27]. The measurements were performed in two directions (Fig 3): proximo-distal and antero-posterior; and, a mean was made for each implant sample. The ISQ analysis was performed in 3 times: immediately after the implant insertion (T1), in the sacrifice of the first animal lot 3 weeks after the implantations (T2) and, in the sacrifice of the second animal lot 4 weeks after the implantations (T3).

Fig 3

Schematic illustration of the implant stability quotient (ISQ) measurement in 2 directions: (A) disto-proximal and (B) antero-posterior.

Removal torque measurement

Ten implants of each group at each proposal period (3- and 4-weeks) were used to measure the removal torque value (RTv). The analysis was performed in a computed torquimeter machine (Torque BioPDI, São Paulo, Brazil). All block samples (bone and implant) were positioned in the apparatus and the maximum RTv was measured and registered.

Scanning Electronic Microscopy (SEM) analysis

All removed implants in the torque removal test were care packaged, dried and prepared for the SEM analysis. Initially the samples were metalized by a sputtering machine (Emitech K 550, Emitech Ltd, Ashford, Kent, UK). Then, a sequence of image with different increases were obtained using a SEM apparatus (Philips XL30, Eindhoven, The Netherlands). The characteristic of the residual bone founds on the implant surface was analyzed and described.

Histomorphometric and histological analysis

After one week, all samples that were fixed in the formaldehyde solution were subjected to treatment with an alcohol sequence for dehydration of these pieces, which followed a progressive increase from 50 to 100% ethanol. After the dehydration, the sample blocks with the bone plus implant, were inserted in historesin (Technovit 7200 VLC, Kultzer & Co, Wehrhein, Germany). After the polymerization, the pieces were cut on the centre of the implants using a metallographic machine (Isomet 1000; Buehler, Germany). Then, the slices obtained were fixed and submitted to a polishing treatment with a sequence of abrasive paper (180 to 1200 mesh) in a polishing machine (Polipan-U, Panambra Zwick, São Paulo, Brazil). All slices were stained with picrosirus hematoxylin staining technique [28]. A sequential series of images were obtained in a light optical microscopy (Nykon E200, Tokyo, Japan) of the contact between the bone and implant (%BIC) and, these images were analyzed. The measurements were performed using the ImageJ program (National Institute of Health, Bethesda, USA). The total perimeter of the implant was considered 100% and, with the values of the areas where contact was found, the percentage of BIC was determined for each sample.

Descriptive analysis of the findings found in the histological sections was performed separately from the cortical and medullary portion of the bone, as shown schematically in the Fig 4.

Fig 4

Schematic image to demonstrate the areas analyzed separately in the descriptive histologic analysis: The cortical portion corresponding to the yellow square and the medullar portion corresponding to the green square.

Morphological analysis

The measure of new bone formed, osteoid matrix and medullary spaces were performed on the histological image of each sample. Initially, was used an area of 2 mm2 (1 mm from the implant towards the bone and 2 mm on the long axis of the implant) of the tissues around of the implant in the cortical and medullar portion separately (Fig 5) and, considerate as 100%. Then, the area of each parameter was measured and the percentual calculated proportionally the total area, the native bone present in the images was not computed. These measurements were performed using the ImageJ program (National Institute of Health, Bethesda, USA).

Fig 5

Representative images showing the area of 2 mm2 (1 mm from the implant towards the bone and 2 mm on the long axis of the implant) used for measure the parameters of new bone formed (●), osteoid matrix (*) and medullary spaces (#).

(a) cortical portion and (b) medullary portion.

Statistical analysis

The ANOVA one-way statistical test was used to determine difference among three times of the ISQ in the same group. Moreover, the t-test was used for evaluating statistical differences of ISQ values collected between both groups in the same time. For the RTv, %BIC and morphologic parameters (New bone formation, osteoid matrix and medullary spaces) analysis was used the t-test to evaluate the statistical differences between the groups in each time. Moreover, a descriptive analysis using the percentual of ISQ and RT values increase between the groups and inside of each group between each time of evaluation was calculated. All analyzes were made in the GraphPad Prism program in the version 5.01 (GraphPad Software, San Diego, California, USA). In all analysis was considered significative when p < 0.05.

Results

The SEM analysis of both implant macrogeometry showed the differences made in the TEST group, that present circular healing chambers made between the threads. The sequence of images in different increases of the Fig 6 demonstrate the characteristics of each implant. As expected, the topography of the implant surface not present differences between the groups.

Fig 6

Sequence of SEM images of the two implant macrogeometries used.

(a-c) implant of the CON group and (d-f) implant of the new macrogeometry of the TEST group.

In both times proposed for the evaluation (3- and 4-weeks after the implantations), all implants presented clinically good signal of osseointegration, without mobility. Moreover, no inflammation or infection signals were observed in any sample. Then, the 80 implant samples could be analyzed (n = 40 implants per group).

Implant Stability Quotient (ISQ) results

The stability measurement of each implant could be performed in the 80 implant samples and at the three predetermined moments. The measured values for each group in each time period are presented in the Table 1. In the Time 1, the mean of the ISQ values measured for both groups do not show statistical difference. Whereas, in the Times 2 and 3 were found statistical differences between the 2 groups. The group TEST showed an average of 13.5% higher at 3 weeks and 14.3% bigger at 4 weeks in comparison to the samples of the group CON. When the evolution within the same group was evaluated, the implants of the TEST group increased the ISQ values by 12.5% for time T1 to T2 and, on average, 35% of time T1 to T3, while in the CON group, 1% and 20% of ISQ increased, respectively, for the same comparison parameters. The line graph of the Fig 7 showed the ISQ evolution on the time for both groups.

Table 1

Implant stability quotient mean values, standard deviation and statistical comparison between the groups in each time of the evaluation.

Time	Group CON	Group TEST	p-value (t-test)
T1	47.8 ± 3.49 ISQ	48.5 ± 3.63 ISQ	0.6483
T2	48.2 ± 3.43 ISQ	54.7 ± 3.65 ISQ	0.0019*
T3	57.3 ± 3.65 ISQ	65.5 ± 3.37 ISQ	0.0010*
p-value (ANOVA)	0.0001*	< 0.0001*

*statistically significative (P < 0.05).

Fig 7

Line graph presenting the ISQ progression on the three times: T1 = immediately after the installation; T2 = 3 weeks; T3 = 4 weeks.

*statistically significative (P < 0.05).

Removal torque results

The data of the measured values showed differences in the RTv values of the groups for the same period were in the CON group at 37.9 ± 3.70 Newtons (N) for 3 weeks and 48.3 ± 3.43 N for 4 weeks, whereas in the TEST group was 45.3 ± 3.80 N for 3 weeks and 65.1 ± 3.45 N for 4 weeks, with a statistical difference between them (p <0.05). The bar graph of Fig 8 shows the values of RTv, standard deviation and statistical comparison between groups at both times. Still, comparing the mean values of CON group and TEST group, the latter presented a mean value 19.5% higher after 3 weeks and 34.8% higher after 4 weeks. In the same group, the implants of CON group increased the RTv between the measured time (from 3 to 4 weeks) at 27.4% and, the TEST group the increase in this period was of 43.7%.

Fig 8

Bar graph showing the RTv values, standard deviation and statistical comparison on the two times of both groups.

Scanning Electronic Microscopy (SEM) results

SEM images of both groups clearly showed residual bone adherence on the implants examined. In the samples evaluated after 3 weeks, the group CON showed the presence of a thin layer of bone tissue present on the surface in some areas of the implant (Fig 9), while in the group TEST it covered the entire implant surface with a very thin layer (Fig 10). In addition, larger bone quantities were found in the healing chambers present in the group TEST implants, suggesting that a bone rupture occurred during reverse torque to removal of the implant, probably due to a strong connection between this area of new bone and bone tissue.

Fig 9

In (a) an image of low magnification of the implant showing the deposition of a thin layer of bone tissue over the entire surface. In (b) an image with more increase showing the bone tissue is deposited on the implant surface. In (c) an image with great increase showing the deposition of bone tissue on the surface, but with spaces between the lumps of bone tissue.

Fig 10

In (a) an image of low magnification of the implant showing the deposition of bone tissue over the entire surface and the presence of larger lumps of bone tissue in several areas of the implant body. In (b) an image with more increase showing the bone tissue is deposited on the implant surface and the big quantity of bone tissue. In (c) an image with great increase showing the deposition of bone tissue on the implant with signs of consistent and even layer on the surface.

In the samples evaluated after 4 weeks, the group CON showed the presence of a more uniform and consistent thin layer (in comparison with the samples of this same group with 3 weeks) of bone tissue present on the surface in all areas of the implant (Fig 11). While in the TEST group it covered the entire implant surface with a larger quantity and a thicker layer (Fig 12), the visual observation of the images shows a bone layer with larger bone quantities, a good organization and with characteristics of a very consistent tissue compared to the CON group shown in the previous figure.

Fig 11

In (a) an image of low magnification of the implant showing the bone tissue deposition over the entire surface. In (b) an image with more increase showing the presence of bone tissue deposited on the implant surface with a uniform and consistent thick layer. In (c) an image with great increase showing that the bone tissue deposition with a more consistent layer.

Fig 12

In (a) an image of low magnification of the implant showing great quantity of bone tissue deposition over the entire surface. In (b) an image with more increase showing the presence of bone tissue deposited on the implant surface with a thick layer. In (c) an image with great increase showing that the bone tissue deposition.

Histomorphological results

After the period predeterminate at 3- and 4-weeks, all implants showed a good stability and all signals of osseointegration. Ten implants of each groups and times were analyzed regards to the bone-to-implant contact (%BIC). In the group CON, the images demonstrate an initial process of neoformation of the bone, showing no signs of formation within the medullar portion. Representative histological section images of the implant after 3- and 4-weeks for both groups are showed in the Fig 13.

Fig 13

Representative images of the CON group.

(a) cortical portion with 3-weeks, (b) medullar portion with 3-weeks, (c) cortical portion with 4-weeks, (d) medullar portion with 4-weeks. Images obtained by light microscopy. New bone formed (●), osteoid matrix (*), medullary spaces (#), implant (Imp) and native bone (Nat).

However, in the group TEST, the images demonstrate a more advanced healing process and some areas in the medullar bone portion showing a new bone formation. Representative histological section images of the implant after 3- and 4-weeks for both groups are showed in the Fig 14.

Fig 14

Representative images of the TEST group.

(a) cortical portion with 3-weeks, (b) medullar portion with 3-weeks, (c) cortical portion with 4-weeks, (d) medullar portion with 4-weeks. Images obtained by light microscopy. New bone formed (●), osteoid matrix (*), medullary spaces (#), implant (Imp) and native bone (Nat).

Significant difference in the %BIC were observed between the both groups in the two times analyzed at 3- and 4-weeks after the implantations. The mean, standard deviation and statistical analysis of measured values are summarized in the Table 2.

Table 2

%BIC mean values, standard deviation and statistical analysis between the groups in the two times proposed.

	3-weeks	4-weeks	p-value
Group CON	34.7 ± 3.36	40.4 ± 4.06	0.0103
Group TEST	40.1 ± 3.19	54.0 ± 4.09	0.0003

Morphological results

The morphological parameters measured of the organization of the healing bone tissue showed a different quantities of new bone formation, osteoid matrix and medullary spaces for the both groups in the two times proposed, are present in the graphs of the Figs 15 and 16. The group TEST showed a higher areas of new bone formation in both times and in both portions examined (cortical and medullary portions), with significant statistical difference (p < 0.05).

Fig 15

Bar graphs of the morphological parameters analysis of new bone formation (Nb), osteoid matrix (Ost) and medullary spaces (Ms) for both groups and in the two portions analyzed (cortical and medullary) at 3 weeks after the implantations.

*statistically significative (P < 0.05).

Fig 16

Bar graphs of the morphological parameters analysis of new bone formation (Nb), osteoid matrix (Ost) and medullary spaces (Ms) for both groups and in the two portions analyzed (cortical and medullary) at 4 weeks after the implantations.

*statistically significative (P < 0.05).

Discussion

In the present study a new implant macrogeometry was evaluated and compared with a conventional commercialized implant regarding its osseointegration potential in early healing periods (3- and 4-weeks). The results demonstrated that this new implant promotes an acceleration in the osseointegration process compared to the conventional implant. The development of this new macrogeometry was based on recent studies that demonstrated that the presence of healing chamber and non-compression of bone tissue during implant installation benefit and accelerate the osseointegration [25,26]. However, the topic of ideal and/or adequate insertion torque, high or low, during implant installation is still a controversial topic in the literature [29]. Furthermore, the possible deleterious effects that could be caused by the high degree of bone compression from the high insertion torque, such as bone resorption, have not been confirmed in the literature [30]. In this sense, Aldahlawi and Collaborates published that implants inserted with high insertion torque (>55 Ncm) showed more peri-implant bone loss than implants inserted with a less assertive insertion torque (<55 Ncm) [29]. Whereas, Bidgoli and collaborates related that the high insertion torques (up to 70 Ncm) did not generate a significant increase in periimplant bone resorption [31]. However, in our present study, the analysis of the influence regarding the value of insertion torque refers to its effects on cellular events during bone tissue healing around the implant surface (osseointegration phase) and, most of the articles above, relate the effects of torque degree on already integrated implants.

The search for reduction in lead times for osseointegration of implants has received much attention from researchers and industry worldwide. In this sense, different micro- and macro-changes in implant design were studied and proposed. On the other hand, there is the patient, with his biology and physiological individualities, which are a fundamental part of obtaining osseointegration of implants. When implants are inserted using high torque values, the physiological limit to absorb this excessive trauma may be exceeded and may cause a higher than expected inflammatory reaction, which may lead to necrosis of the bone tissue [23,32,33]. Other authors have described that high implant insertion torque can compress and/or alter (damage) the peri-implant bone tissue. They also note that this induces deleterious effects on local microcirculation, possibly leading to bone necrosis and possibly implant failure. To achieve good primary stability without causing excessive compression in the peri-implant bone tissue, it was suggested that the implants be installed with a torque of approximately 30 Ncm [34,35].

Events related to implant installation, such as milling and implant insertion, promote different intensities of bone tissue trauma, which affect the inflammatory reaction. This intensity of the inflammatory response, promoted during the implant implantation surgery, was measured by the expression of the transcription factor NF-kB in previous studies performed by our group [36]. Other studies on the same theme have also shown that the excess trauma caused during milling or bone compression during implant insertion can negatively interfere with the healing process of this tissue [23,32,33]. Bone tissue density is determinant for its elasticity limit and, consequently, for the dissipation of the forces generated (stress) during implant placement in its bed [37]. Thus, it is possible to state that the bone can withstand a certain compression limit, which varies depending on its conditions. The high insertion torque generates a strong compression and distortion in the peri-implant bone tissue. When this applied torque is greater than 40–45 Ncm there is a disturbance in the local microcirculation, which can lead to osteocyte necrosis and, consequently, generate bone resorption [38-40]. However, even if this hypothesis has been reported in several other studies, there is no scientific evidence [30]. In our present study, the hypothesis presented was that the new implant macrogeometry can accelerate the osseointegration process. The results confirmed that this hypothesis is true.

Several studies had proposed that the morphological alterations on the implant surface characteristics can improving and accelerating the osseointegration process (healing of bone around the implant) [7-10]. Thus, the present study had the aim of evaluated both implant models (regular and new implant mcrogeometry) with the same surface treatment, to verify the importance of this factor (the macrogeometry) in the early time period of osseointegration. Primary stability is a prerequisite for achieving osseointegration of implants [1,12,13,21,25,26]. This results from the mechanical union between the bone and the implant that minimizes micromovements between the two structures and prevents the formation of fibrous tissue at its interface. When micromovements are greater than 50–150 μm, osteoblast activity may be affected and therefore compromised osteointegration [3,14]. Primary stability essentially depends on surgical technique, implant geometry and bone characteristics [11-13], and can be assessed by frequency resonance analysis or insertion torque. In the present study, primary stability was measured only by frequency resonance analysis (using the Osstell device), considering that the animal model used does not allow the installation of implants with high insertion torque.

Moreover, the results obtained of the secondary stability measured showed that the new implant macrogeometry (group TEST) presented higher values in the two times (3- and 4-weeks) after the implantation, in comparison with the control group (group CON). Regarding implant stability (ISQ) measured by the Osstell device, the TEST group showed a significant increase in relation to the implants of the CON group, ie, at 3 weeks in the general average 13.5% higher and at 4 weeks 14.3% bigger. When the evolution within the same group was evaluated, the implants of the TEST group increased the ISQ values by 12.5% of the time T1 to T2 and, on average 35% of the time T1 to T3, while in the CON group, it was 1% and 20% of ISQ increase respectively for the same comparison parameters. These results clearly demonstrate the benefit of the new implant macrogeometry with healing chambers.

Another biomechanical assay to assess implant osseointegration is the removal torque value (RTv), which provides values on the joint force between bone and implant [1,12,13]. Although this type of test is little used for destroying the sample, it is impossible to perform histology of these pieces, these higher measured values are indicative of a good bone-implant interaction [1], and are also indicative of whether or not mineralization of the newly formed bone occurred on the implant surface. We compare the both groups proposed based on the two time points (3- and 4-weeks) after implantation, with a highly significant and it is thus concluded that there is an important effect between the groups (p < 0.05). Thus, as in the comparison made to RTv, when comparing the mean values of the CON group with the TEST group, the latter presented a mean value 19.5% higher after 3 weeks and 34.8% higher after 4 weeks. When the evolution within the same group was evaluated, the implants of the CON group increased the RTv between the measured time (from 3 to 4 weeks) at 27.4% and, in the TEST group the increase in this period was of 43.7%. Again, the values indicate an acceleration in the process of osseointegration of the implants with the new implant macrogeometry. These implants removed in the removal torque test were evaluated by scanning electronic microscopy to verify the residual adhered bone on the surface. The results of this visual comparative analysis confirmed higher amounts of residual adhered bone on the TEST group implants compared with the CON group implants. In addition, the bone tissue quality observed on the TEST group samples was superior to the CON group at both times evaluated. The higher RTv value observed in the TEST group could be also a consequence of the bone growth within the healing chambers that improve the implant stability. As reported by other authors, the chamber significantly alters the biological healing pattern, compared to it in the case of the traditional screw root shape implants [41,42]. Furthermore, the healing chambers have been regarded as a key contributor to secondary implant stability [42,43]. Moreover, the data collected in the morphological analysis showed a higher new bone formation values for the group TEST, demonstrating an acceleration of bone formation and corroborating the results found in the removal torque test.

Initially, it was hypothesized that the new implant design presented would not alter the initial stability values, as evidenced by the results obtained. Moreover, we observed an increase in torque removal and %BIC values for samples of the group TEST, showing that this new macrogeometry promotes a positive effect for osseointegration, especially in the initial tested period of 3 and 4 weeks after implantation and, in comparison with the group CON. The efficiency of elaborating healing chambers has been demonstrated in other previous studies, which reported a lower primary implant stability due to the technique used for the elaboration of these free spaces, ie, an oversized perforation that creates these spaces (healing chambers) between the implant and the bone tissue [25,26]. In our study, the initial stability values measured with Osstell showed no statistical differences (p <0.05) immediately after the installation of both implant designs used. However, after 3 and 4 weeks, significantly higher values were observed for implants of the group TEST, in comparison to the group CON.

As reported in other studies [11-13], changes in implant morphology (micro- or macro-geometry) may alter the osseointegration pattern. To measure the amount of osseointegration, the most frequently used assessment is the measurement of the percentage of contact between the bone and the implant to the total implant area (%BIC). The results found in our study showed higher values for TEST implants at both times tested (3 and 4 weeks), with a statistically significant difference when compared to the values obtained for the CON group (p <0.05). Implants with new macrogeometry (TEST group) showed a significant increase in %BIC values, especially within 4 weeks after implantation. A similar study in the same animal model (rabbit tibia) but with a longer follow-up period (2 months) showed that the healed bone did not increase the %BIC values, but increased the biomechanical test values (ISQ and RTv) in compared to the conventional implant design [12]. The results obtained demonstrated that changes in implant design may be a new alternative for stimulation and acceleration of the healing process during the early stages of implant osseointegration, even though the implants received the same surface treatment. However, further in vivo research should be conducted to substantiate these results.

There are some limitations to the present animal study. First of all, the results of studies with animal models cannot be directly translated to human models, because even among rodent species, correlations of only 70% are generally found [44]. On the other hand, there is a limitation on the number of animals used and, consequently, the amount of samples tested for each implant model. Still, the conditions of the place where they were implanted, which are completely different from the conditions of use in humans (oral cavity). Thus, other studies using animal models (dogs, for example), as well as, in humans, it is essential to evaluate the effects of this new implant model and, also, its behavior after the application of functional loads.

Conclusions

Within the limitations of the present study, the results found showed that changes in implant macro-design can produce a significant increase for the acceleration of the bone healing process around the implants (osseointegration). Higher bone-to-implant contact, primary stability and torque removal values, as well as greater quantity and quality in bone adhered to the surface of the implants with new macro-design, corroborate the importance of implant macrogeometry in the osseointegration process.