Quantitative assessment of interradicular bone density in the maxilla and mandible: implications in clinical orthodontics

The phenomenon of tooth movement is dependent on concomitant resorption and deposition of the alveolar bone. Research on bone biology in recent years has changed our understanding about many concepts related to the clinical practice of orthodontics. However, the researchers have generally focused on tissue reactions occurring within the periodontal ligament and bone, with less attention being paid to the inherent bone density. The oft-repeated histologic descriptions of tooth movement do not always fully correlate with clinical observations. It has been shown that different bones as well as different regions of the same bone show variations in composition and therefore in density [1].

Knowledge of bone density in various areas of the maxilla and mandible may help the clinician to understand and correlate various observed clinical phenomenons. A close relationship exists between the bone density and anchorage potential, rate of tooth movement, and success of dental implants [2–4]. Studies have shown that dental implants placed in low-density areas have a higher failure rate [3]. Many studies have been done to evaluate the bone density in various regions of the maxilla and mandible prior to dental implant placement, but they have been mostly in relation to cancellous bone in edentulous areas [5–7]. Minimal research has been done to evaluate the bone density of the cortical bone in relation to the interradicular areas in the maxilla and mandible, which are the common sites for orthodontic mini-implant placement.

The present study was undertaken to quantitatively evaluate the density of the alveolar and basal bones of the maxilla and mandible in interradicular areas by computed tomography. The Hounsfield value of the alveolar and basal bones will provide guidelines for planning anchorage and placement of orthodontic mini-implants.

One hundred and nine computed tomographic (CT) scans were randomly obtained from Hubli Scan Centre, Hubli, Karnataka, India. The scans were of patients who had been investigated for trauma, and their history was negative for any metabolic disorder that could affect bone density.

The criteria for sample selection were as follows:

Bone density was measured at the alveolar and basal bone levels in Hounsfield units (HU) using bone mineral density software (Siemens VA20A_SP3A, Munich, Germany) incorporated in the CT machine. Scans were made according to the following technical protocol: 128-slice spiral CT scanner, 120 kV, 100 mAs, 188-mm field of view, 0.6-mm-thick slices, 0.4-mm increments, ultrahigh resolution, Kernel H60s sharp, window dental, 1.0 zoom (no zoom), and 0° gantry angulation. The scanner was calibrated daily before it was used for the first patient, according to the manufacturer’s guidelines. In addition to the axial tomograms, reconstructions were made in coronal and sagittal planes in order to easily locate the axial image at the required level of the alveolar and basal bones.

To measure the bone density of the alveolar bone, a CT section (axial image) was taken 5 to 7 mm from the alveolar crest area in the premolar and molar areas. To measure the bone density at the basal bone level, another section is selected at 2 to 5 mm above the root apex of the premolars and molars. The density of the bones was measured in HU in the following interradicular areas, namely between the two central incisors (1-1), between the central and lateral incisors (1-2), between the canine and first premolar (3-4), between the first and second premolars (4-5), between the second premolar and first molar (5-6), and between the first and second molars (6-7), the maxillary tuberosity (MT), and the retromolar area in the mandible (RM). At each area, the density of the buccal cortical, cancellous, and palatal or lingual cortical bones at the alveolar bone level was measured. Also, the density of the buccal cortical and cancellous bones at the basal bone level was measured. At the retromolar area of the mandible, the bone density at the buccal and lingual sides of the crest of the ridge was measured. While measuring the density of the cortical bone, its center point was taken. The density of the cancellous bone was measured at the trabeculae, located halfway buccolingually between the buccal and palatal or lingual cortical plates (Figure 1).

The examiner measured the bone density of each area three times on each of the axial images for both right and left sides. The mean of the six values was taken for each area. The data was subjected to statistical analysis. To analyze differences of the bone density at the incisor, canine, premolar, molar, and retromolar or tuberosity areas in the maxilla and mandible, the Newman-Keuls multiple post hoc procedure was performed. Student’s t-test was done to compare the bone density of the alveolar and basal bones and that of the maxilla and mandible.

Numerous approaches have been used to assess bone tissue density such as conventional radiography, dual-energy X-ray absorptiometry, digital image analysis, ultrasound, and CT. Most of these methods are impractical for routine clinical use. CT is an established non-invasive method for acquiring bone images prior to dental implant placement. Quantitative computed tomography (QCT) has the major advantage of enabling the trabecular and cortical bone densities to be evaluated separately. It allows precise three-dimensional anatomic localization and furnishes direct density measurements, expressed in HU [5].

The bone density in the midline area was found to be low in both the maxilla and mandible relative to other interradicular areas. It could be possibly due to development of the mandible in two halves (right and left bodies). This separation present at the midline symphysis menti is gradually eliminated between the 4th and 12th months after birth, when ossification converts the syndesmosis into a synostosis, uniting the two halves. The presence of the synostosis joint in this region could be the possible cause of a lesser density in this region [8]. The presence of less density in the midline area of the maxilla explains the splitting of the midpalatal suture during rapid maxillary expansion and creation of midline diastema. The same finding was observed by Moon et al [9] in their study. They compared the bone density in various regions of the palate and found the lowest density in the vicinity of the midpalatal suture.

The density in the maxilla and mandible increased progressively from the midline towards the posterior region, which could be explained by distribution of occlusal force during mastication. The maximum biting forces are found to increase from the anterior towards the posterior teeth [10]. The highest density between the first and second molars in the basal bone could be explained by the presence of the zygomatic buttress. The zygomatic buttress is a strong bony pillar that provides pressure absorption and transduction in the facial skeleton [11]. The increased bone density in this area could be responsible for a stronger bone structure. The presence of least density at the tuberosity region could be due to the absence of direct mechanical stimulation in that region. The highest density at the retromolar area could also be explained by the presence of thick oblique ridges in that area as well as attachment of the muscles of mastication in that area. Furthermore, cortical bone thickness in the mandible showed a gradual increase from the anterior to the posterior region [12, 13]. Thus, the results suggest that the mandibular posterior area contains denser and thicker cortical bone.

The basal bone was found to be denser than the alveolar bone for both the maxilla and mandible (Additional file 1: Graphs 1 and 2). This difference can be attributed to the transmission of masticatory forces to the basal bone through the teeth. However, the bone density at the retromolar bone was found to be significantly higher at the alveolar region compared to the basal region, which could be because of the presence of thick oblique ridges in that region. The mandible was found to have higher density values than the maxilla (Additional file 1: Graphs 3 and 4), which could be explained by the difference in loads (compression, tension, and torsion) to which the maxilla and mandible are exposed [2]. Functional loading dictates the osseous anatomy of opposing jaws. The mandible is subjected to substantial torsion and flexion caused by muscle pull and masticatory function. Thick and dense mandibular cortices are needed to resist the torsional and bending strain. The maxilla, however, is loaded predominately in compression. It has no major muscle attachments and transfers much of its load to the rest of the cranium. Because of the entirely different functional role, the maxilla ispredominantly trabecular with thin cortices.

The sample in the present study showed almost a similar bone density value pattern in the maxilla and mandible as observed by Park et al [14] in a Korean population, except that they found the highest bone density in the canine premolar region of the maxilla. In general, bone density values were found to be higher in an Indian population than in a Korean population [14, 15]. Differences in metabolic or lifestyle factors account for a larger share of the racial differences in bone mass. Lifestyle factors such as dietary calcium intake, physical activity, smoking, and alcohol intake have been found to influence bone density [16]. Another reason which could be possible for the variation in the observed bone mineral density values is the difference in methodological approach such as the use of different slice thickness, software, CT machines, etc. [17].

When a pairwise comparison of density at the seven interradicular areas was done, differences between bone densities of any two areas were found to be very highly significant. This makes knowledge of site-specific bone density important prior to planning anchorage strategies and placement of mini-implants.

In general, the rate of tooth movement is inversely related to the bone density. As the bone density decreases, the rate of tooth movement increases [2]. In the current investigation, the alveolar process supporting the mandibular molars has been found to be denser than that supporting the maxillary molars, thereby offering more resistance to tooth movement. This could explain as one of the reasons for mandibular molars having a higher anchorage value than the maxillary molars. The high-density bone is formed as the leading roots are moved mesially. After a few months of mesial translation, the trailing roots engage the high-density bone formed by the leading root and the rate of tooth movement declines [2]. In the areas of low bone density, it is necessary to augment the anchorage using transpalatal arch, implants, etc. as per requirement.

Bone mineral density has been also used to establish a treatment plan to ensure thestability of implants in dentistry. During early stages, bone density appears to be the key determinant for stationary anchorage of mini-implants in the sites with inadequate cortical bone thickness because primary retention of mini-implants is achieved by mechanical means rather than through osseointegration [15]. The mechanical distribution of stress occurs primarily where the bone is in contact with the implant [18]. The smaller the area of the bone contacting the implant body, the greater is the overall stress, when all other factors are equal. The bone density influences the amount of bone in contact with the implant surface. Since less dense bone is found in the posterior maxilla, it will offer less area of contact with the body of the implant. Consequently, a greater implant surface area is required to obtain a similar amount of bone-implant contact in soft bone compared with denser bone quality. In the present study, the bone density at the maxillary tuberosity was approximately 950 HU and comparatively weak. Therefore, when placing microscrew implants in the maxillary tuberosity, longer implants should be used.

Whenever the mini-implants are placed in the thick, dense cortical bone, insertion torque increases and thereby chances of fracture or breakage of implant increases and more amount of bone is damaged [19]. Therefore, while placing the mini-implants in the thick and dense cortical bone area, it is advisable to use pre-drilling method.

The presence of the thick cortical bone in the posterior mandible and the high bone density as observed in this study might show that bone damage is possible from overheating during drilling. Tehemar stated that heat generation increases during drilling in dense bone. The success of a dental implant can be affected adversely if greater than 47°C of heat is generated as it is known to cause bone necrosis. Bone necrosis is found to be the result in proportion with increase in temperature and exposure time to heat [20]. Therefore, when placing the mini-implants into the retromolar and posterior areas in the mandible, clinicians must be careful not to generate heat. Heat generation can be prevented by irrigating abundantly with a saline solution, not applying too much pressure on the bone, and not using a worn drill. Also, a large-diameter drill can be used instead of a small-diameter drill.

Knowledge of bone density in the maxilla and mandible may help correlate many of the clinical findings as well as allow the clinician to plan anchorage strategies and placement of implants with necessary precautions accordingly.

Further studies can be done to evaluate the bone density at various levels of alveolar and basal bones as well as to compare the bone density at the mini-implant recipient site using the standard radiographic method and CT in the same region of interest. A long-term clinical study of the prognostic success of CT evaluation on the longevity of the implants can be done.