The purpose of this retrospective study was to evaluate the changes in computed tomography (CT) values of ramus bone and screws after sagittal split ramus osteotomy (SSRO) setback surgery. The subjects were 64 patients (128 sides) who underwent bilateral SSRO setback surgery. They were divided into six groups according to the fixation plate type used and the use or not of self-setting α-tricalcium phosphate (Biopex): group 1: titanium plate and screws; group 2: titanium plate and screws with Biopex; group 3: poly- l -lactic acid (PLLA) plate and screws; group 4: PLLA plate and screws with Biopex; group 5: uncalcined and unsintered hydroxyapatite particles and poly- l -lactic acid (uHA/PLLA) plate and screws; group 6: PLLA/uHA plate and screws with Biopex. CT values (pixel values) of the lateral cortex, medial cortex, osteotomy site, and screws were measured preoperatively, immediately after surgery, and 1 year postoperatively using horizontal CT images at the mandibular foramen taken parallel to the Frankfort horizontal plane. There were significant differences in the time-course change of pixel values for the lateral cortex ( P < 0.0001) and the osteotomy site ( P < 0.0001) among the six groups. This study suggests that the fixation plate type and use of bone alternative material may affect bone quality during the process of bone healing after SSRO.
One of the advantages of the sagittal split ramus osteotomy (SSRO) is that the large areas of bony contact that are made remain after either advancement or retrusion of the distal segment. However, making a wider bony contact without the step of the cortical bone surface between the proximal and distal segments can induce inward rotation of the condylar long axis in setback surgery.
In previous studies by this group, bent plates were used to secure the fragments without a positioning device and it was found that the bent plate increased the incidence of postoperative temporomandibular joint dysfunction (TMD) and did not change skeletal or occlusal stability. With this method, the gap between the proximal and distal segments is created by a bent plate, preventing the formation of a large bony contact. In setback surgery, especially with asymmetry, fixation between the segments can be performed without bony contact to prevent large changes in condylar position and angle.
More recently, absorbable plates and screws have been used with increasing frequency in our hospital. These absorbable plate and screw systems have been developed in Japan (poly- l -lactic acid (PLLA) and uncalcined and unsintered hydroxyapatite particles and poly- l -lactic acid (uHA/PLLA)). Although, it has been shown in animal studies that the strength of the plate and screws is reduced in a time-dependent manner, the plate and screw resorption process and the surrounding bone formation at the osteotomy site remain unclear. Furthermore, it has been considered that bone density or bone thickness in the ramus area could change because of the stress distribution changes resulting from SSRO (occlusion and skeletal change). The computed tomography (CT) value can be correlated to bone density, and bone strength can be expressed in terms of bone density and quality. CT value data can be useful for assessing bone formation.
A previous study by this group showed that the gap between the proximal and distal segments could be filled with new bone after SSRO using either titanium or absorbable plates, even if there were few bony contacts between the segments. Moreover, another study suggested that inserting self-setting α-tricalcium phosphate (α-TCP) (Biopex; Pentax Co., Tokyo, Japan) in the gap between the proximal and distal segments was useful for new bone formation after SSRO with bent plate fixation. However, that study assessed only the linear length and ramus square using CT at the osteotomy site.
It is still unclear whether the fixation device or the use of a bone alternative material can affect the healing process after SSRO. Furthermore, the CT values of ramus bone, titanium plate and screws, absorbable plate and screws, and bone alternative material following orthognathic surgery have not been reported. The purpose of this retrospective study was to evaluate changes in quality (CT value) of ramus bone and screws after SSRO using absorbable plates and titanium plates with and without self-setting α-TCP.
Patients and methods
This study included 64 Japanese adults (21 men and 43 women) who presented with jaw deformities diagnosed as mandibular prognathism with and without a maxillary deformity. At the time of orthognathic surgery, the patients ranged in age from 16 to 51 years, with a mean age of 29.2 years (standard deviation 10.9 years). For this retrospective study, informed consent was obtained from all patients in accordance with the Declaration of Helsinki; the study was approved by the ethics committee of Yamanashi University Hospital.
Lateral, frontal, and submentovertex (SV) cephalograms were obtained before surgery, as described previously. All 64 patients underwent bilateral SSRO setback with the modified fixation. Of the 64 patients, 26 underwent SSRO with Le Fort I osteotomy to advance or impact the maxilla. At the time of fixation, the dental arch of the distal segment was secured to the maxillary arch with an interpositional splint and 0.4-mm wire.
For seven patients (14 sides), a titanium miniplate was used for internal fixation of the mandible (long miniplate (four holes/burr 8 mm, thickness 1.0 mm) and four screws (2 × 14 mm and 2 × 5 mm); Universal Mandible fixation module, Stryker Leibinger Co., Freiburg, Germany). These patients comprised group 1 (titanium group).
For three patients (six sides), a titanium miniplate (long miniplate (four holes/burr 8 mm, thickness 1.0 mm) and four screws (2 × 14 mm and 2 × 5 mm); Universal Mandible fixation module) was used for internal fixation of the mandible, and self-setting α-TCP (Biopex) was inserted in the anterior part of the gap between the segments after plate fixation. These patients comprised group 2 (titanium with α-TCP group).
For seven patients (14 sides), a PLLA miniplate (28 × 4.5 × 1.5 mm with four screws (2 × 8 mm); FIXSORB-MX, Takiron Co., Osaka, Japan) was used for internal fixation of the mandible. These patients comprised group 3 (PLLA group).
For 11 patients (22 sides), a PLLA miniplate (28 × 4.5 × 1.5 mm with four screws (2 × 8 mm); FIXSORB-MX) was used for internal fixation of the mandible, and self-setting α-TCP (Biopex) was inserted in the anterior part of the gap between the segments after plate fixation. These patients comprised group 4 (PLLA with α-TCP group).
For 19 patients (38 sides), a uHA/PLLA miniplate (28 × 4.5 × 1.5 mm with four screws (2 × 8 mm); SuperFIXSORB-MX; Takiron Co.) was used for internal fixation of the mandible. These patients comprised group 5 (uHA/PLLA group).
For 17 patients (34 sides), a uHA/PLLA miniplate (28 × 4.5 × 1.5 mm with four screws (2 × 8 mm); SuperFIXSORB-MX) was used for internal fixation of the mandible, and self-setting α-TCP (Biopex) was inserted in the anterior part of the gap between the segments after plate fixation. These patients comprised group 6 (uHA/PLLA with α-TCP group).
The groups were divided by time-frame, so the sample number was statistically variable.
To prevent intraoperative inward rotation of the condylar long axis, model surgery was performed preoperatively with reference to the SV projection. Before surgery, an SV cephalogram was obtained for all patients, followed by simulation. A distal segment including the lower dental arch was first set back according to the position of the upper dental arch on the SV cephalometric trace.
When the proximal and distal segments are fixed with straight plates after bilateral sagittal split osteotomy (BSSO), proximal segments containing the condylar head cause internal rotation ( Fig. 1 ). To prevent internal rotation of the proximal segments, the overlapping cortical bone at the anterior site of the proximal segment was not removed to keep the contact area between the proximal and distal segments, and was fixed with a bent plate and four screws on each side of the mandible. At the posterior part, a 3–7-mm gap was maintained between the proximal and distal segments.
After surgery, elastics were placed to maintain an ideal occlusion. All patients received orthodontic treatment before and after surgery. CT images were obtained for all patients preoperatively, immediately after surgery, and 1 year after surgery.
CT data acquisition
For CT scanning, the patients were placed in the gantry with the tragal–canthal line perpendicular to the floor. They were instructed to breathe normally and to avoid swallowing during the scanning process. CT scans were obtained in the radiology department by skilled radiology technicians using a high-speed, advantage-type CT generator (Light Speed Plus; GE Healthcare, Milwaukee, WI, USA) with each sequence taken 1.25 mm apart for three-dimensional (3D) reconstruction (120 kV, average 150 mA, 0.7 s/rotation, helical pitch 0.75). The resulting images were stored in the attached workstation computer (Advantage Workstation version 4.2; GE Healthcare, Milwaukee, WI, USA), and 3D reconstruction was performed using the volume-rendering method. ZedView version 7.0 (LEXI Co., Tokyo, Japan) medical imaging software was used for 3D morphological measurements.
CT image analysis software (DIANA DICOM free version 220.127.116.11; Luke-System, Chiba, Japan) was used to measure the CT value (pixel value). CT values of the lateral cortex, medial cortex, and osteotomy site were measured preoperatively, immediately after surgery, and at 1 year postoperative using horizontal CT images with the mandibular foramen parallel to the Frankfort horizontal (FH) plane. For each CT image, three randomly selected points at the anterolateral site of the lateral cortex, three at the anteromedial site of the medial cortex, and three at the anterolateral site of the mandibular canal were assessed. The mean pixel value in the region of interest (ROI; approximately 1.0 mm 2 circle) was measured automatically. The mean value for the three points was then calculated and assigned as the pixel value for each part. Measurement of the screws was performed for just one screw on each side for all patients. The measurement area for the screw was very small for determining the ROI. Therefore, the distance between the long axis line of the screw and the outline of the lateral cortical surface was measured three times using another horizontal CT image without artefacts. The mean value was calculated and determined as the pixel value for the screw ( Figs. 2–4 ).
Measurement of pixel values of unused absorbable screws (in vitro)
The pixel value of the unused absorbable screws was unknown. Therefore, six unused PLLA screws and five uHA/PLLA screws were implanted in impression paste and their CT image taken under the same conditions. The pixel value was then measured three times at the centre of the screw head. The mean value was calculated and determined as the pixel value of the screw.
Data were analyzed statistically with Dr. SPSSII for Windows (SPSS Japan Inc., Tokyo, Japan). The time-course changes were compared using repeated measures analysis of variance (ANOVA). The data from each period were compared by a paired comparison method using the Student’s t -test. Differences were considered significant at P < 0.05.
No patient had a post-surgical wound infection. There was no dehiscence, bone instability, bone non-union, or long-term malocclusion. The mean setback was 7.4 ± 2.9 mm on the right side and 7.1 ± 3.3 mm on the left side. There was no significant difference among the groups.
When the pixel values were compared between men and women, no significant difference was found for any measurement. Therefore, the data of men and women were not separated in this study.
Using repeated measures ANOVA, there were significant differences in the time-course change in pixel values for the lateral cortex (between-subject P = 0.0002, within-subject P < 0.0001), in the time-course change in pixel values for the osteotomy site (between-subject P < 0.0001, within-subject P < 0.0001), and in the time-course change in pixel values of the screw type (between-subject P < 0.0001, within-subject P = 0.0207) among the six groups.
|Preoperative||Immediately postoperative||1 Year postoperative|
|Titanium with α-TCP||1775.9 * ,**||247.2||1587.5 *||132.2||1558.9 **||170.2|
|PLLA||1593.4 *||139.7||1581.3||214.6||1491.5 **||204.8|
|PLLA with α-TCP||1662.9||132.4||1666.9||79.8||1649.0||114.7|
|uHA/PLLA||1716.4 * ,**||95.2||1652.4 *||120.5||1579.8 **||187.3|
|uHA/PLLA with α-TCP||1639.5||114.1||1644.1||105.2||1611.8||139.4|
|Preoperative||Immediately postoperative||1 Year postoperative|
|Titanium||1388.0 *||118.6||1336.8 *||115.0||1304.7||175.5|
|Titanium with α-TCP||1529.5||235.5||1462.3||248.0||1454.6||130.0|
|PLLA with α-TCP||1460.3||176.6||1371.7||262.1||1438.9||157.7|
|uHA/PLLA||1463.6 *||180.9||1415.1||203.3||1419.8 *||168.8|
|uHA/PLLA with α-TCP||1415.4||128.9||1398.8||151.3||1425.6||139.0|
|Preoperative||Immediately postoperative||1 Year postoperative|
|Titanium||390.2 *||214.9||67.8 * ,**||19.4||390.8 **||182.1|
|Titanium with α-TCP||321.6 * ,**||131.7||2037.3 *||99.2||2057.9 **||91.4|
|PLLA||362.3 *||241.4||73.3 * ,**||23.3||406.4 **||231.4|
|PLLA with α-TCP||371.1 * ,**||325.3||1957.7 *||234.6||2025.9 **||146.5|
|uHA/PLLA||408.2 *||255.8||86.8 * ,**||34.6||381.6 **||319.7|
|uHA/PLLA with α-TCP||376.3 * ,**||230.7||1977.0 *||323.4||2014.5 **||372.9|