In traumatic dental implant surgeries, connective tissue formation is seen around the implant during the healing process and this may cause failures in implant treatments. It is inevitable that the heat generated during implant drilling affects the living bone tissue in the implant placement area [8, 12]. It is thought that this heating occurs due to the friction between the bone tissue and the drill during drilling and the healing of the bone tissue is adversely affected at temperatures above 47 °C [13, 14]. The purpose of irrigation during drilling is to reduce the temperature increases that may occur in the bone [15]. When the temperature change graphs in the groups irrigated with 40 ml/min isotonic solution in our study were examined, it was observed that the temperature values on the bone surface were in the direction of decrease. On the other hand, it was observed that there would not be a significant temperature increase in the bone if irrigation was not applied at low cycles.Studies have shown that implant losses occur in the first year after implant placement at a high rate. It shows the importance of the surgical procedure to achieve success in implant applications [11]. Markovic et al. [16] placed a total of 288 self-tapping and non-self-tapping implants of Bredent and Straumann brands with torque forces of 30, 35 and 40 N in an in vitro study in porcine ribs. They measured the temperature changes observed at 1, 5 and 10 mm depths during placement. As a result of the study, they concluded that thermal effects would be observed less at low insertion torques in self-tapping implants. Trisi et al. [17] placed implants in the iliac crest of sheep at different temperatures in their in vivo study. They prepared a total of 15 implant sites in the study. During the opening of the implant socket, they kept the temperature of 5 of these sites at 50 °C for one minute and 5 of these sites at 60 °C for one minute. The remaining 5 implant sites were prepared without any temperature increase. No implant loss was observed in the study. However, they concluded that in the regions prepared at 60 °C for one minute, implant crestal bone loss increased in the later period after osteointegration and bone implant contact was less in this group. Sumer et al. [18] placed a total of 64 implants in bovine femur in their in vitro study. They divided 4.1 and 4.8 mm diameter implants into different groups and placed them manually at speeds of 30, 50 and 100 rpm. As a result of the study, they found that the highest temperature change (9.81 ± 2.29 °C) occurred in implants with a diameter of 4.1 mm and a speed of 100 rpm. As a result of the study, they argued that implant placement performed manually or at speeds of 30 and 50 rpm was safer than placement performed at 100 rpm. Allsobrook et al. [19] in an in vitro study on bovine head, Allsobrook et al. [19] examined the trauma caused by tungsten carbide and steel drills on the bone depending on the number of times they were used by SEM method. In all of their applications, they ensured that the temperature did not exceed 27.7 °C. After the study, they argued that the burs did not reach damaging temperature values even after 50 times of use. The data obtained from this study also showed that there was no significant change in the temperature increases in the bone after the first and 30th use of the burs. Chacon et al. [20] argued that the geometric structure of the burs and the wear caused by the use of the burs were effective in the temperature changes that occurred during the resurfacing process. In their study on cortical bone in bovine femur, they used a serum irrigated system with a speed of 2500 rpm and a constant force of 2.4 kg. Accordingly, they suggested that after 25 uses, the temperature value in the bone in triple twist drills without a relief angle can rise above 47 °C and healing may be impaired. This suggests that critical temperature increases may affect implant success. Matsuoka et al. [21] placed self-drill mini implants at speeds of 50, 100, 150, and 250 rpm into bone containing cortical layers of different thickness and observed the temperature change. They reported that the temperature increase was higher in the insertions made in the region where the cortical bone was thicker. At 250 rpm, they reported that temperature increases of more than 10 °C occurred, therefore, the instrument speed should be kept below 150 rpm in self-drilling miniscrew placements. In our study, the speed was set as 150 rpm in the groups without irrigation and it was observed that no significant temperature increase occurred in the bone when working at this speed.

Gaspar et al. [22] examined the temperature changes during the resurrection of a total of 36 implants placed in the rabbit tibia and the histologic changes observed in the early period. Accordingly, they reported that irrigation-free operation at 50 rpm and irrigated operation at 800 rpm gave approximate results in terms of temperature change. During osteotomy for implant applications, bone heating occurs due to the friction of the drill against the bone. To prevent this heating in the bone, the implant socket should be prepared by cooling with saline irrigation. Even if cooling is performed during bone preparation, some necrosis occurs around the implant socket. The size of the necrotic area depends on factors such as both heat and blood supply of the implanted area [23]. When necrosis occurs, the response of the bone to the necrotic area can be in 3 different ways:

1.

Fibrous tissue formation: A certain amount of fibrous tissue forms in the bone, especially in cases of high trauma. The formation of fibrous tissue around the implant is easier than the formation of bone tissue.

2.

Sequestration formation: If the blood supply to the tissue is insufficient and the surgery is traumatic, the bone necrosizes and does not heal.

3.

New bone formation: Cortical bone formation around the implant is achieved with atraumatic surgery and adequate revascularization [24].

After implantation, remodeling around the implant is desired. Bone repair of necrotic implant cortex depends on the presence of sufficient number of cells in the area, adequate nutrition of these cells and sufficient stimulus for bone repair [25]. Many researchers have reported different opinions regarding the drilling speed during implant osteotomy. Albreksston et al. Albreksston et al. reported that the maximum drill speed should be 2000 revolutions during bone cavity preparation, whereas Babush et al. They reported 1500–1600 revolutions per minute in internally cooled milling systems, a maximum of 500 revolutions per minute in externally cooled systems and no more than 20 revolutions per minute during implant placement [7]. During implant osteotomy, if the bone tissue is exposed to a temperature higher than 43°C in one minute, a temperature that can cause denaturation of bone cells is reached. Since the high temperature causes alkaline phosphatase destruction in the bone and prevents calcium synthesis, new bone formation around the implant does not occur. Thus necrotic tissue forms around the implant. This situation prevents the formation of osteointegration and causes fibroosteosis integration [26].

Sandalli, on the other hand, stated that the quality of bone in different anatomical regions is different and a standard milling application cannot be sufficient, and the lowest speed that can cut the bone is the most appropriate speed [27]. It has been reported that when resistance is encountered while preparing the implant cavity, the pressure on the milling increases the heat generated in the bone and causes an increase in the amount of necrotic area. Other methods to reduce the high temperature that may occur during osteotomy include using a drill suitable for the implant system, using the drills sequentially, working under abundant irrigation, using a torque-adjustable physiodispenser and the sharpness of the drills used [26].As in bone, it is important that soft tissue surgery is atraumatic. The incision should be sharp and properly limited, and the mucoperiosteal flap should be lifted precisely. Maximum effort should be made not to damage the periosteum [28].

In the literature, bovine ribs were used in a significant number of in vitro studies in which temperature changes in bone were measured. In this study, bovine rib was used [29, 30]. In the studies, the similarity of the density of bovine ribs with the implanted bones was reported. In this study, it was macroscopically observed that the cortical/cancellous bone ratios in the bovine rib were similar to the mandible. On the other hand, in our study, it was seen that bovine ribs are easily obtainable at low costs and can also be made ready to work quickly.

There are also studies in the literature in which a device that applies constant force during drilling is used. Karaca et al. [31] prepared a device similar to the device in our study in their study in which they measured the effect of the drill diameter, speed of the drill and applied forces on temperature changes. As a result of their study, they reported that the temperature increased the most at the depth value between 4.5 mm and 6.5 mm and that the temperature increased more in titanium coated drills. In their study, they performed the drills in dry and extracellular tissue fluid-containing environments and reported that the environment in which the drills were made did not significantly affect the temperature changes. Oliveira et al. [32]. used bovine ribs in an in-vitro study in which they prepared an implant socket. They reported that there was no difference in temperature change between the first and 30th use of implant drills. In this study, they also observed a greater temperature increase in steel drills. In our study, the results obtained for the number of uses of the drills were similar to the results of this study. In cases where the amount of cortical bone is high, it is expected that the temperature increase during drilling will also be high. In their study, Abboud et al. [33] reported that the temperature increase is higher in cases with increased cortical bone density; on the other hand, the temperature will increase more with the prolongation of the drilling time. Based on this study, it should be kept in mind that the temperature increase may also increase in bones with high cortical thickness (Type 1 and Type 2).