Bone implant with gradient threads and dental implant assembly

Abstract

The invention relates to the technical field of bone implants, and provides a bone implant with a gradually-changed thread and a dental implant assembly, the bone implant comprises a gradually-changed thread section, the gradually-changed thread section is provided with a gradually-changed thread, and the gradually-changed thread extends from the top end side to the crown end side along the central longitudinal axis of the bone implant. The tapered thread includes a top side, a crown side, and a lateral surface connecting the top side and the crown side, the lateral surface defining a radially outer surface of the tapered thread, the tapered thread extending helically in a direction of the central longitudinal axis. The top side face comprises at least two slope faces, the width ratio of one slope face in the at least two slope faces to the top side face is gradually increased in the extending direction from the top end side to the crown end side, and the slope of the slope face is smaller than that of the other slope faces. According to the implant, bone attachment is easier, the expected mechanical effect is achieved through smaller bone extrusion on the unit area, damage to bone cells and blood vessels is reduced, and the initial stability and the bone combination speed after the implant is implanted are improved.

Description

Technical Field

[0001] The present application relates to the technical field of bone implants, and in particular to a bone implant with a gradual thread and a dental implant component. Background Art

[0002] Bone implants are medical devices used in the fields of orthopedics and dentistry that can replace or repair bone tissue lost due to disease, injury or congenital defects and are widely used in clinical medical operations.

[0003] After the implant is implanted, the rationality of the stress distribution on its surface directly affects the formation of bone integration and the success rate of repair. In other words, bone cells attach themselves to the surface of the implant, so that the implant is integrated with the bone tissue. The bone integration process usually takes 3-6 months to proceed. During this period, the implant must be firmly held in the bone by mechanical means. This mechanical fixation of the implant in the bone is called "primary stability". Most modern implants are provided with threads on the outer surface, which are used to screw and fix the implant in the preoperatively prepared drill hole. These threads provide initial stability during bone integration, and the rough wall provides a larger attachment surface area for bone cells compared to smooth-walled implants. After the implant is implanted, the implant does not loosen for a long time, and no peripheral inflammation and bone resorption occur, which is called long-term stability. The shape of the implant's external thread will not only have a great influence on the initial stability, but also on the speed and success rate of bone integration.

[0004] The existing implant external thread design is replaced by an implant with a tapered core top instead of the traditional "parallel wall" (cylindrical) implant. Usually the part of the implant that penetrates deep into the human bone is called the top, and the other end is called the coronal end. During the screwing-in process of the implant, due to the gradual increase of the thread groove, the implant will form a significant compression with the jawbone. However, the compression of the bone cannot be too high, because the greater the compression, the greater the friction, which will generate more heat during the screwing-in process and increase the pain of the recipient. In addition, excessive compression of the bone can also cause damage to bone cells and blood vessels in the bone, delay bone healing, and even implant failure.

[0005] Therefore, how to improve the initial stability and mechanical distribution of the implant while ensuring minimal damage to the bone, thereby reducing operation time and implant failure is a technical problem that needs to be solved urgently. Summary of the invention

[0006] In order to solve at least one of the above technical problems, the present application provides a bone implant and a dental implant assembly with a gradual thread, which improves the initial stability of the bone implant through a gradual thread segment. During the screwing process of the bone implant, the thread of the gradual thread segment extends from the top side to the crown side, and the proportion of the width of the top side of the gradient surface gradually increases. The gradual thread of the bone implant will squeeze the cortical bone and cancellous bone, and the lower thread will be screwed in along the trajectory of the upper thread in turn, gradually increasing the squeezing force, which can further improve the effect of the initial stability of the implant. Since the top side and the crown side of the gradual thread will squeeze the cartilage, and at the same time, like the traditional implant, its thread groove can also be gradually raised, so compared with the conventional implant that relies on the core to squeeze the bone, its bone squeezing area is significantly increased, it is easier to attach the bone, the force area is larger, and the expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirements can be achieved with less bone compression, which reduces the damage to bone cells and blood vessels, improves the initial stability of the implant after implantation and the speed of bone integration, making it very suitable for immediate implantation.

[0007] Therefore, in a first aspect, the present application provides a bone implant, comprising: a tapered thread segment, the tapered thread segment having a tapered thread, the tapered thread extending from the top side to the crown side along the central longitudinal axis of the bone implant. The tapered thread comprises: a top side surface, a crown side surface, and a lateral surface connecting the top side surface and the crown side surface, the lateral surface defining the radial outer surface of the tapered thread segment, and the tapered thread extending spirally along the direction of the central longitudinal axis. Wherein, the top side surface of the tapered thread comprises at least two slope surfaces, and along the direction extending from the top side surface to the crown side surface, one of the at least two slope surfaces gradually increases in proportion to the width of the top side surface, and the slope of the slope surface is smaller than that of the other slope surfaces.

[0008] The present implementation method can set a gradual thread segment on the surface of the bone implant, and improve the effect of the initial stability of the implant through the gradual thread segment. The gradual thread segment has a gradual thread. During the screwing process of the bone implant, due to the direction in which the thread of the gradual thread segment (i.e., the gradual thread) extends from the top side to the crown side, one of the slope surfaces gradually increases the width of the top side surface, and the gradual thread segment of the bone implant will squeeze the cortical bone and cancellous bone. At the same time, during the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. Since both the top side surface and the crown side surface of the gradual thread segment will squeeze the cartilage, the bone squeezing area is significantly increased, which is easier for bone attachment and has a larger force area. The expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirement can be achieved with less bone compression, which reduces the damage to bone cells and blood vessels, increases the speed of the implant combining with the bone after implantation, and can significantly improve the implantation success rate while reducing the pain of the recipient.

[0009] In combination with the above bone implant, along the direction extending from the top side to the coronal side, the proportion of the width of the top side surface occupied by one of the at least two slope surfaces is set to m, wherein the value range of m is 0%<m<100%.

[0010] In this implementation, the proportion of one of the at least two slope surfaces constituting the top side surface gradually increases from 0% to 100% along the direction extending from the top side to the crown side, that is, along the direction extending from the top side to the crown side, the proportion of one of the slope surfaces constituting the top side surface gradually increases from zero to one, until the entire top side surface is completely constituted by the above-mentioned one slope surface. Thus, the squeezing force is gradually increased during the screwing-in process of the bone implant until the squeezing force is maximum. This structure is easier for bone attachment, has a larger force-bearing area, and can achieve the expected mechanical effect with less bone squeezing per unit area, thereby meeting the requirements of initial stability.

[0011] In combination with the above-mentioned bone implant, along the direction extending from the top end to the crown end, the proportion of the width of one of the at least two slope surfaces to the width of the top side surface gradually increases at a constant variable.

[0012] In the present implementation, one of the slope surfaces constituting the top side surface gradually increases at a constant variable along the direction extending from the top side to the coronal side. This allows the force applied to the cortical bone and cancellous bone to increase steadily and evenly, thereby reducing the pain of the recipient and avoiding discomfort caused by too rapid an increase in the squeezing force.

[0013] In combination with the above-mentioned bone implant, the top side surface of the gradual thread segment includes N sequentially connected slope surfaces, wherein the first slope surface is connected to the tooth bottom, the Nth slope surface is connected to the tooth top, and the width proportion of the first slope surface gradually increases along the direction extending from the top side to the crown side.

[0014] In this implementation, the top side surface is composed of N slope surfaces, and the N slope surfaces are connected in sequence, wherein the first slope surface is connected to the tooth bottom, and the Nth slope surface is connected to the tooth top. In the direction extending from the top side to the crown side, the first slope surface gradually increases in the width of the top side surface, and the gradual thread section of the bone implant will squeeze the cortical bone and cancellous bone. At the same time, during the screwing-in process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. As the proportion of the first slope surface continues to increase, the bone squeezing area is significantly increased, and the expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirements can be achieved with less bone compression.

[0015] In combination with the above bone implant, it also includes a core, and the tapered threads of the tapered thread segments extend radially outward along the core, wherein the core matches the implantation socket, and the inner diameter of the implantation socket is larger than the outer diameter of the core.

[0016] In this implementation, the core of the bone implant is the carrier of the gradual thread segment, and the gradual thread of the gradual thread segment extends radially outward along the core. Since the top side and the crown side of the gradual thread will form an extrusion with the cartilage, the bone extrusion area is significantly increased, which is easier for bone attachment. The expected mechanical effect can be achieved with less bone extrusion per unit area, and the initial stability requirements can be achieved with less bone compression, which reduces damage to bone cells and blood vessels and increases the speed of the implant combining with the bone after implantation. In addition, there is a certain gap between the implant socket and the core. When the bone implant is screwed into the implant socket, the bone chips generated will be discharged into this gap. These bone chips have a similar effect to bone powder, filling the gap to make the connection between the bone implant and the bone tissue more stable.

[0017] In combination with the above bone implant, along the direction extending from the top end to the coronal end, the core portion is formed by a cylindrical section and a conical section which are arranged successively.

[0018] In this implementation, the depth of the thread groove of the cylindrical section remains unchanged, that is, there is no taper on the upper part of the implant, which significantly improves the self-tapping property of the implant, making the implantation operation more convenient. When the implant is screwed into the implant socket, the thread of the set tapered section gradually squeezes the bone tissue along the direction from the top to the crown, so the force applied is smaller, the friction between the implant and the bone tissue is small, and the heat generation is also small, which reduces the pain of the recipient and is more convenient for installation.

[0019] In combination with the above-mentioned bone implant, along the direction extending from the top end to the coronal end, the core portion includes a first conical core portion segment, a cylindrical core portion segment, and a second conical core portion segment which are sequentially arranged.

[0020] The core part of this implementation is divided into three sub-parts. The first conical core section is conducive to the installation of the implant. Since the top of the threaded structure is first screwed into the implant socket in the recipient's mouth, the radial dimension of the gradual thread at the top is the smallest, which can play a positioning and guiding role in the narrow space of the recipient's mouth, and the implant can be aligned with the implant socket without applying force to the implant. The cylindrical core section can provide radial support for the bone tissue and improve the initial stability. The second conical core section makes the core diameter of this section gradually increase from the top to the crown end, forming an effective radial compression on the cartilage, thereby further improving the initial stability.

[0021] In combination with the above-mentioned bone implant, the included angle between the generatrix of the tapered section and the central longitudinal axis is set to α3, and the included angle between the generatrix of the first tapered core section and the central longitudinal axis is set to α1, and α1 is greater than α3.

[0022] In this implementation, at the conical section and the first conical core section, since the angle between the generatrix of the first conical core section and the central longitudinal axis is greater than the angle between the generatrix of the conical section and the central longitudinal axis, the thread height there gradually increases in the direction from the crown end to the top end, which can improve the self-tapping property and initial stability of the implant.

[0023] In combination with the above-mentioned bone implant, the outer contour of the cylindrical core segment and the outer contour of the cylindrical segment are parallel to a straight line formed by the intersection of the same cutting surface.

[0024] In this implementation, the outer contours of the cylindrical core section of the core part and the cylindrical section of the gradient thread structure are arranged parallel to the straight line formed by the intersection of the same cutting surface, so that the thread height of the cylindrical core section can be a constant value. During the process of screwing the implant into the implant socket, the lower thread of the cylindrical core section exerts less squeezing force on the upper thread, so the friction is smaller, the heat is less, and the pain of the recipient can be reduced.

[0025] In conjunction with the above-described bone implant, the tapered section is equal in length to the first tapered core section.

[0026] In this implementation, the tapered section of the gradual thread structure is equal to the length of the first tapered core section of the core, so that the thread height of this section gradually increases from the crown end to the top. Setting a higher height thread at the top can improve the self-tapping and initial stability of the implant.

[0027] In combination with the above-mentioned bone implant, at least one cutting groove is provided on the tapered thread, and the at least one cutting groove extends from the top end to the crown end in a spiral manner.

[0028] In this implementation, at least one cutting groove is provided for spirally transporting the bone tissue cut off by the thread, thereby avoiding the increase in cutting resistance caused by the accumulation of bone tissue, thereby reducing friction, generating less heat, alleviating the pain of the recipient, and improving the initial stability of the implant.

[0029] In combination with the above-mentioned bone implant, at least one cutting groove forms at least one cutting surface on the gradual thread structure, and the at least one cutting surface is perpendicular to the tangent direction of the gradual thread rotation direction.

[0030] This implementation method can significantly improve the cutting ability of the cutting edge surface. The cutting bottom surface at the bottom of the cutting groove is perpendicular to the cutting surface, so that the cutting bottom surface and the cutting surface form a spiral right-angle groove, thereby improving the chip guiding ability of the cutting groove.

[0031] In conjunction with the above-mentioned bone implant, the pitch of the tapered thread is 0.6-2.4 mm.

[0032] In connection with the above-described bone implant, the width of the lateral surface of the tapered thread on the cylindrical core segment is 0.2 mm.

[0033] In conjunction with the above-described bone implant, the cutting groove extends from the top end to 0 to 1 mm above the tapered section.

[0034] In combination with the above-mentioned bone implant, α1<20° and α3<15°.

[0035] In conjunction with the above-mentioned bone implant, the width of the lateral surface is set in the range of 0.05 mm to 0.5 mm.

[0036] In conjunction with the above-mentioned bone implant, the thread height of the tapered thread in the cylindrical core section is 0.3 mm.

[0037] In a second aspect, a bone implant is provided, comprising a non-gradient thread segment and the gradient thread segment as described above, wherein the threads of the non-gradient thread segment and the gradient thread segment are continuously connected.

[0038] In this implementation, the bone implant can combine the gradual thread structure and the non-gradient thread structure to improve the scope of application of the bone implant. The non-gradient section can adapt to the bone tissue environment of different recipients, and the thread structure can be flexibly adapted to different bone structures, shapes, and textures, which can meet biocompatibility and have a wider scope of application.

[0039] In a third aspect, a dental implant assembly is provided, comprising an abutment, a connecting screw, and the bone implant as described above, wherein the abutment is placed in the bone implant, and the connecting screw is fixed to the abutment.

[0040] In this implementation, the dental implant component is a split design, including a bone implant, an abutment and a denture, and the abutment is fixed in the bone implant. The abutment is connected to the denture and provides a mounting base for the denture. The bone implant can provide good initial stability and long-term stability for the dental implant component. The abutment can be selected with different structures or materials as needed to meet the needs of the gingival tissue of different recipients and improve biocompatibility. The denture can also be selected according to the actual oral environment of different recipients. It not only ensures the initial stability and long-term stability of the dental implant component, but also provides the best solution for different recipients to adapt to biocompatibility.

[0041] Compared with the prior art, the bone implant and dental implant assembly with a gradual thread provided by the present application have at least the following beneficial effects: the bone implant realizes the step-by-step axial extrusion of the bone tissue in the implant socket by setting the gradual thread segment. During the screwing-in process of the bone implant, since the thread of the gradual thread segment extends from the top side to the crown side, the proportion of the width of the top side surface occupied by one of the slope surfaces gradually increases, and the gradual thread of the bone implant will squeeze the cortical bone and cancellous bone, and the lower-level thread will be screwed in along the trajectory of the upper-level thread in turn, gradually increasing the extrusion force, and combined with the radial extrusion of the bone tissue by the thread, the effect of the initial stability of the implant can be further improved. Because the top and crown sides of the gradual thread will form compression with the cartilage, like traditional implants, the thread grooves can also gradually rise. Therefore, compared with conventional implants that rely on the core to squeeze the bone, the bone compression area is significantly increased, which is easier to attach to the bone and has a larger force-bearing area. The expected mechanical effect can be achieved with less bone compression per unit area, so the initial stability requirements can be achieved with less bone compression, which reduces damage to bone cells and blood vessels and increases the speed of the implant's integration with the bone after implantation. The technical problem of the existing technology that when implanting bone implants, the bone damage is large, the mechanical distribution of the implant in the alveolar bone is single, the initial stability is poor, and the high implant failure rate is caused.

[0042] Other features and advantages of the present application will be described in detail in the subsequent specific embodiments. BRIEF DESCRIPTION OF THE DRAWINGS

[0043] The following is a brief introduction to the drawings required for describing the embodiments or prior art.

[0044] Figure 1 A schematic diagram of the structure of a tapered thread provided in an embodiment of the present application;

[0045] Figure 2 A schematic diagram of a cross section and partial structure of a bone implant provided in an embodiment of the present application;

[0046] Figure 3 A bottom bottom view of a bone implant provided in an embodiment of the present application;

[0047] Figure 4 A schematic diagram of the structure of a bone implant provided in an embodiment of the present application;

[0048] Figure 5 A schematic diagram of stress distribution when a bone implant is fused with bone tissue provided in an embodiment of the present application;

[0049] Figure 6 A schematic structural diagram of a tapered thread segment of a bone implant provided in an embodiment of the present application;

[0050] Figure 7 A schematic diagram of the partial cross-sectional structure of a gradual thread provided in an embodiment of the present application.

[0051] Reference numerals:

[0052] 110, crown end; 111, crown bevel; 112, neck section; 120, standard thread section; 130, gradual thread section; 140, core; 150, cutting groove; 151, cutting edge surface; 152, cutting groove tail; 153, cutting bottom surface; 160, top; 170, pitch;

[0053] 210, cylindrical section; 220, conical section; 230, first conical core section; 240, cylindrical core section; 250, second conical core section; 261, crown side; 262, top side; 263, lateral surface; 264, thread bottom width; 265, thread height; 2621, first slope surface; 2622, second slope surface; 268, tooth top; 269, tooth bottom. DETAILED DESCRIPTION

[0054] The technical solutions in the embodiments of the present application will be described below in conjunction with the drawings in the embodiments of the present application.

[0055] In the description of the present application, the terms "center", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc., indicating orientations or positional relationships, are based on the orientations or positional relationships shown in the accompanying drawings and are only for the convenience of describing the present application and simplifying the description, and do not indicate or imply that the referred device or element must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be understood as a limitation on the present application.

[0056] In the description of the present application, it should be noted that, unless otherwise clearly specified and limited, the terms "installation", "connection" and "connection" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, a conflicting connection or an integrated connection. For ordinary technicians in this field, the specific meanings of the above terms in this application can be understood according to the specific circumstances.

[0057] In the description of this specification, specific features, structures, materials or characteristics may be combined in an appropriate manner in any one or more embodiments.

[0058] Bone implants are medical devices used in orthopedics and dentistry that can replace or repair bone tissue lost due to disease, injury or congenital defects. The rationality of stress distribution on the surface of the implanted part of the bone implant directly affects the formation of bone integration and the long-term success rate of implant restoration. However, the stress on the surface of the implanted part can be changed by designing the thread to change the mechanical transmission of the implant and the stress distribution at the bone interface. At the same time, the shape of the surface thread not only has a great influence on the speed of bone integration, but also can improve the initial stability of the implant, increase the surface area of ​​the implant, and improve the stress distribution at the bone interface. Therefore, the surface thread design occupies a very important position in the biomechanical optimization design of the implant.

[0059] Taking dental implants as an example, during the screwing process of the commonly used implants with tapered core tops, the thread grooves rise along the direction of the crown, which will form obvious extrusion with the jawbone. At the same time, excessive extrusion means that the friction between the implant and the jawbone is large, which generates more heat during the screwing process. In addition, excessive extrusion of the bone can also cause damage to bone cells and blood vessels in the bone, delayed bone healing, and even implant failure. At the same time, due to the increase in friction and extrusion force, the resistance of this implant during the screwing process will increase, that is, a larger screwing torque is required, which also increases the risk of mechanical damage to the implant. At the same time, the bone extrusion amount of the implant cannot be too small, which will lead to poor initial stability. However, due to the great difference in the density and hardness of different people's jaws, the same implant has a great difference in the extrusion effect when implanted in different people's jaws, which determines that it is difficult to balance this implant. Therefore, there is a need for an implant with small bone extrusion but high initial stability.

[0060] In addition, since the strength of the cortical bone in the jaw is much greater than that of the cancellous bone, the threads on the cortical bone should have sufficient strength. The processing method of the tapered implant results in an increase in the groove between the crown threads, which significantly improves the strength of the threads at the cortical bone. However, the contact area between the threads and the maxillary bone is significantly reduced, reducing the bone attachment area and the stress area. Therefore, this type of implant is prone to loosening during repeated loading, leading to peri-implantitis, which in turn causes bone absorption, thereby reducing long-term stability.

[0061] Based on this, the present application provides a bone implant having the characteristics of small bone compression force, high initial stability and long-term stability, and high thread strength at the cortical bone.

[0062] In order to facilitate the understanding of the present application, the following embodiments take a dental implant used in the field of dental implantation as an example.

[0063] like Figure 1-7As shown, the bone implant may include: a gradual thread segment, the gradual thread segment extends from the top 160 side to the crown end 110 side along the central longitudinal axis of the bone implant. The gradual thread segment includes: a top side surface 262, a crown side surface 261, and a lateral surface 263 connecting the top side surface 262 and the crown side surface 261, the lateral surface 263 defines the radial outer surface of the gradual thread segment, and the thread of the gradual thread segment extends spirally along the direction of the central longitudinal axis. Among them, the top side surface 262 of the gradual thread segment includes at least two slope surfaces, and along the direction extending from the top 160 side to the crown end 110 side, one of the at least two slope surfaces gradually increases the proportion of the width of the top side surface 262, and the slope of the slope surface is smaller than that of the other slope surfaces.

[0064] In this embodiment, the bone implant is taken as an example of a dental implant. The dental implant is divided into a top end 160 and a crown end 110. The top end 160 is the end that goes deep into the alveolar bone. The radial dimension of the thread at the top end 160 is small, the thread height 265 is high, and the cutting ability is strong. The crown end 110 is the end away from the alveolar bone. The radial dimension of the thread at the crown end 110 is large, and the thread height 265 is small. The direction from the top end 160 to the crown end 110 is the direction away from the alveolar bone, and the direction from the crown end 110 to the top end 160 is the direction toward the alveolar bone.

[0065] Specifically, the dental implant includes a tapered thread section extending from the crown end 110 to the top end 160 along the central longitudinal axis of the dental implant, and the tapered thread section includes threads extending radially outward (i.e., tapered threads). Figure 2 As shown, the thread includes a top side surface 262, a crown side surface 261 and a lateral surface 263 connecting the top side surface 262 and the crown side surface 261, and the lateral surface 263 defines the radial outermost surface of the thread. The top side surface 262 of the gradual thread segment includes at least two slope surfaces, and along the direction extending from the top end 160 to the crown end 110, the width of the top side surface 262 is gradually increased by one of the at least two slope surfaces. Since the slope of the slope surface is smaller than that of the other slope surfaces, as the width of the slope surface gradually increases, the thread width will become wider and wider, and during the screwing process of the bone implant, the pressure on the bone tissue will gradually increase, achieving the effect of squeezing the bone. It should be noted that the slope in this embodiment refers to the angle formed between the surface of the slope surface and the central longitudinal axis of the bone implant.

[0066] During the screwing process of the bone implant, along the direction extending from the top 160 side to the coronal end 110 side, the proportion of the width of the top side 262 of one of the slope surfaces gradually increases, and the gradual thread section of the bone implant will squeeze the cortical bone and cancellous bone. At the same time, during the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. Since the top side 262 and the coronal side 261 of the gradual thread section will squeeze the cartilage, the bone squeezing area is significantly increased, which makes it easier for the bone to attach, and the force-bearing area is larger. The expected mechanical effect can be achieved with less bone squeezing per unit area, thereby achieving good initial stability.

[0067] In one embodiment, in the direction in which the gradual thread segment extends from the top 160 to the coronal end 110, the proportion of the width of the top side surface 262 occupied by one of the at least two slope surfaces is set to m, wherein the value range of m is 0%<m<100%. That is, the proportion of one of the slope surfaces constituting the top side surface 262 gradually increases from zero to one, until the entire top side surface 262 is completely constituted by the above-mentioned one slope surface. Thus, the squeezing force is gradually increased during the screwing-in process of the bone implant until the squeezing force is maximum. This structure is easier for bone attachment, has a larger force-bearing area, and can achieve the expected mechanical effect with less bone squeezing per unit area, thereby meeting the requirements of initial stability.

[0068] Of course, along the direction extending from the top 160 to the crown end 110, the width of at least one of the two sloped surfaces can gradually increase as a proportion of the width of the top side surface 262 at a constant variable, which allows the force applied to the cortical bone and cancellous bone to increase steadily and evenly, thereby reducing the pain of the recipient and avoiding discomfort caused by too rapid an increase in the squeezing force.

[0069] This embodiment can make the extrusion effect (extrusion force) of the bone in each implanted section consistent, make the mechanical distribution more uniform and reasonable, and avoid excessive extrusion. At the same time, the implantation torque of the implant can be adjusted by changing the gradual angle increment to avoid implantation difficulties.

[0070] It should be noted that, along the direction extending from the top 160 to the crown end 110, the proportion of the width of one of the at least two slope surfaces to the width of the top side surface 262 can be gradually increased with a constant variable, or can be set to gradually increase with a non-constant variable, and the increment of the above slope surface in different sections of the gradual thread segment can be determined according to the actual bone quality of the patient. The increment can also be freely combined and set, for example: if the bone density of the implantation area of ​​the recipient is uniform in a certain section, then the section changes with a constant increment, and when the bone density of the implantation area of ​​the recipient changes with a gradient in a certain section, then the section changes with a gradient increment.

[0071] Compared with the prior art, since the proportion of the slope surface width of the top side 262 gradually increases, this means that the area of ​​the thread used to squeeze the bone tissue here is significantly larger, which disperses the heat generated when the implant is screwed in with the same torque, and the pain of the recipient will be much less. In addition, since the squeezing area of ​​the thread and the cartilage is significantly larger, the expected stabilization effect can be achieved with less bone squeezing per unit area, which reduces the damage to bone cells and blood vessels in the bone. The speed of the implant combining with the bone after implantation is improved. At the same time, the thread width at the core 140 is widened, but the strength of the thread at the cortical bone is significantly enhanced, which will increase the contact area between the thread and the cartilage and make the force more dispersed, which increases the axial squeezing force that the implant can withstand.

[0072] In this embodiment, the bone implant realizes the step-by-step axial extrusion of the bone tissue in the implant socket by setting a gradual thread segment. During the screwing process of the bone implant, due to the direction in which the thread of the gradual thread segment extends from the top 160 side to the crown end 110 side, one of the slope surfaces gradually increases the width of the top side 262, and the gradual thread of the bone implant will form an extrusion on the cortical bone and cancellous bone, and the lower thread will be screwed in along the trajectory of the upper thread in turn, gradually increasing the extrusion force. Since the top side 262 and the crown side 261 of the gradual thread will form an extrusion with the cartilage, the bone extrusion area is significantly increased, which is easier to attach to the bone, and the force-bearing area is larger. The expected mechanical effect can be achieved with less bone extrusion per unit area, so the initial stability requirement can be achieved with less bone compression, which reduces the damage to bone cells and blood vessels, improves the speed of the implant combining with the bone after implantation, and can significantly improve the implantation success rate while reducing the pain of the recipient. The invention solves the technical problems in the prior art that when implanting a dental implant, the bone is severely damaged, the mechanical distribution of the implant in the alveolar bone is single, the initial stability is poor, and the high implant failure rate is caused.

[0073] In one embodiment, the top side surface of the gradual thread segment includes N slope surfaces connected in sequence, N≥2, wherein the first slope surface is connected to the tooth bottom, the Nth slope surface is connected to the tooth top, and the width of the first slope surface gradually increases along the direction extending from the top side to the crown side. In this embodiment, the top side surface can be composed of N slope surfaces, and the N slope surfaces are connected in sequence, wherein the first slope surface is connected to the tooth bottom, and the Nth slope surface is connected to the tooth top. Along the direction extending from the top side to the crown side, the first slope surface gradually increases in the width of the top side surface, and the gradual thread segment of the bone implant will squeeze the cortical bone and cancellous bone. At the same time, during the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. Since the proportion of the first slope surface continues to increase, the bone squeezing area is significantly increased, and the expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirement can be achieved with less bone compression.

[0074] Specifically, when N=2, the top side surface 262 of the gradual thread segment includes a first slope surface 2621 and a second slope surface 2622, wherein the first slope surface 2621 connects the tooth bottom 269, and the second slope surface 2622 connects the tooth top 268. In the direction extending from the top end 160 side to the crown end 110 side, the width proportion of the first slope surface 2621 gradually increases.

[0075] In this embodiment, the top side surface 262 is composed of two slope surfaces, and the two slope surfaces are connected in succession, wherein the first slope surface 2621 is connected to the tooth bottom 269, and the second slope surface 2622 is connected to the tooth top 268. In this embodiment, the angle between the first slope surface 2621 and the image line of the gradual thread can be set to 35°, and the angle between the second slope surface 2622 and the image line of the gradual thread can be set to 15°, that is, the first slope surface 2621 and the second slope surface 2622 have an angle at the intersection, and the size of this angle can be defined according to the size of the angle between the first slope surface 2621, the second slope surface 2622 and the image line of the gradual thread. In some examples, the angle between the first slope surface 2621, the second slope surface 2622 and the image line of the gradual thread can also be set according to actual conditions, and this application does not give examples one by one.

[0076] In the direction extending from the top 160 side to the coronal end 110 side, the first slope surface 2621 gradually increases in the width of the top side surface 262, and the gradual thread section of the bone implant will squeeze the cortical bone and the cancellous bone. At the same time, during the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. As the proportion of the first slope surface 2621 continues to increase, the bone squeezing area is significantly increased, and the expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirement can be achieved with less bone compression.

[0077] Specifically, when N=3, the top side surface 262 of the gradual thread segment includes a third slope surface, a fourth slope surface and a fifth slope surface, the third slope surface connects the tooth bottom 269, the fifth slope surface connects the tooth top 268, and the fourth slope surface is located between the third slope surface and the fifth slope surface. Along the direction extending from the top end 160 side to the crown end 110 side, the width proportion of the third slope surface gradually increases.

[0078] In this embodiment, the top side surface 262 is composed of three slope surfaces, and the fourth slope surface is located between the third slope surface and the fifth slope surface. The angle between the third slope surface and the image line of the gradual thread can be set to 15°, the angle between the fourth slope surface and the image line of the gradual thread can be set to 35°, and the angle between the fifth slope surface and the image line of the gradual thread can be set to 15°. The third slope surface, the fourth slope surface, and the fifth slope surface also have angles between them. In one example, the third slope surface, the fourth slope surface, and the fifth slope surface can be rounded at their intersection.

[0079] In the direction extending from the top 160 side to the coronal end 110 side, the third slope surface gradually increases in the width of the top side surface 262, and the gradual thread section of the bone implant will squeeze the cortical bone and the cancellous bone. At the same time, during the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. As the proportion of the fourth slope surface continues to increase, the bone squeezing area is significantly increased, and the expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirement can be achieved with less bone compression.

[0080] In one embodiment, along the direction extending from the top 160 side to the coronal end 110 side, the width ratios of the fourth slope surface and the fifth slope surface gradually decrease. During the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the extrusion force. Since the width ratio of the fourth slope surface increases, it is easier to attach the bone, the force-bearing area is larger, and the expected mechanical effect can be achieved with less bone extrusion per unit area, so the initial stability requirement can be achieved with less bone compression.

[0081] When N=4, the top side surface 262 of the gradual thread segment includes a sixth slope surface, a seventh slope surface, an eighth slope surface and a ninth slope surface connected in sequence, wherein the sixth slope surface is connected to the tooth bottom 269, and the ninth slope surface is connected to the tooth top 268. In the direction extending from the top end 160 side to the crown end 110 side, the width proportion of the seventh slope surface gradually increases.

[0082] Specifically, in this embodiment, the top side surface 262 is composed of four slope surfaces, and the four slope surfaces are connected in sequence, wherein the sixth slope surface is connected to the tooth bottom 269, and the ninth slope surface is connected to the tooth top 268. That is, the sixth slope surface is connected to the tooth bottom 269, the two ends of the seventh slope surface are respectively connected to the sixth slope surface and the eighth slope surface, the other end of the eighth slope surface is connected to the ninth slope surface, and the ninth slope surface is connected to the tooth top 268. In this embodiment, the angle between the sixth slope surface and the gradual thread mirror line can be set to 15°, the angle between the seventh slope surface and the gradual thread mirror line can be set to 35°, the angle between the eighth slope surface and the gradual thread mirror line can be set to 15°, and the angle between the ninth slope surface and the gradual thread mirror line can be set to 35°.

[0083] In the direction extending from the top 160 side to the crown end 110 side, the width proportion of the sixth slope surface to the top side surface 262 gradually increases, and the width proportions of the other slope surfaces gradually decrease. The gradual thread section of the bone implant will squeeze the cortical bone and cancellous bone. At the same time, during the screwing process of the bone implant, the lower thread is screwed in along the trajectory of the upper thread in sequence, gradually increasing the squeezing force. Since the proportion of the seventh slope surface continues to increase, the bone squeezing area of ​​the seventh slope surface can be significantly increased, and the expected mechanical effect can be achieved with less bone squeezing per unit area, so the initial stability requirements can be achieved with less bone compression.

[0084] In other embodiments, the top side surface 262 can also be composed of five or more slope surfaces, wherein the first slope surface is configured to gradually increase the width of the direction extending from the top end 160 side to the crown end 110 side, which is the same as the principle of the above embodiment and will not be repeated here.

[0085] In one embodiment, the bone implant further includes a core 140, and the tapered threads of the tapered thread segments extend radially outward along the core 140, wherein the core matches the implant socket, and the inner diameter of the implant socket is larger than the outer diameter of the core.

[0086] In the present embodiment, the implantation socket is used to accommodate the bone implant, and the bone implant is usually provided with a implantation socket at the implantation site before implantation to facilitate the implantation of the bone implant. The inner diameter of the implantation socket is usually set according to the size of the core 140, and is ensured to be well combined with the thread. The core 140 of the bone implant is the carrier of the tapered thread segment, and the tapered thread of the tapered thread segment extends radially outward along the core 140. The tapered thread extends along the length of the tapered thread segment in a spiral manner, and the tapered thread width narrows in a radially outward direction, so that the tapered thread is widest at the position where it contacts the core 140, and the lateral surface 263 is narrowest, and the core 140 diameter of the tapered thread segment is limited by the outer diameter of the core 140, and the outer diameter of the tapered thread segment is limited by the lateral surface 263 of the thread.

[0087] Since the top side 262 and the coronal side 261 of the tapered thread will form compression with the cartilage, the bone compression area is significantly increased, making it easier for bone to attach. The expected mechanical effect can be achieved with less bone compression per unit area, and the initial stability requirement can be achieved with less bone compression, which reduces damage to bone cells and blood vessels and increases the speed of implant integration with bone after implantation.

[0088] There is a certain gap between the implant socket and the core 140. When the bone implant is screwed into the implant socket, bone chips generated will be discharged into the gap. These bone chips have a similar effect to bone powder, filling the gap to make the connection between the bone implant and the bone tissue more stable.

[0089] In a preferred embodiment, the diameter of the implant socket is 0.1 mm larger than the core diameter of the bone implant, that is, the gap between the implant socket and the core 140 is set to 0.1 mm, so that the bone chips can be fully filled into the gap and maintain good connection stability with the implant and the implant socket. It should be noted that the inner diameter of the implant socket is matched with the outer contour of the core, and the gap is always kept consistent.

[0090] In one embodiment, the pitch 170 of the gradual thread is constant along the axial direction, preferably 0.6 mm to 2.4 mm. The distance between the tooth bottom and the passive surface of the gradual thread is preferably 0.5 mm.

[0091] like Figure 2 As shown, along the direction extending from the coronal end 110 to the top end 160, the tapered thread segment is formed by a cylindrical segment 210 and a conical segment 220 which are arranged successively. Figure 2 A cross-sectional view of a preferred embodiment of the present application is shown in FIG. Figure 2 The dotted lines in the central cylindrical section 210 and the conical section 220 show the shape of the implant blank before thread processing, and clearly show the outer contour shape formed by the lateral surface 263 of the thread.

[0092] The contour of the gradual thread segment is composed of a crown side surface 261, a top side surface 262, a lateral surface 263, a thread bottom width 264 and a thread height 265. The thread height 265 is defined by the outer diameter of the contour formed by the lateral surface 263 of the thread and the diameter of the core 140. The crown side surface 261 and the top side surface 262 of the thread extend from the core 140 in the radially outer direction thereof and gradually narrow, so that the thread bottom width 264 of the thread is the widest and the lateral surface 263 is the narrowest. At the same time, the thread spirally extends from the top end 160 to the crown end 110 along its axis L in the contour shape, thereby forming a gradual thread segment of the dental implant. The thread pitch 170 is a fixed value, preferably 0.6 mm to 2.4 mm. In addition, in each implant, the gradual thread can also be a double-start thread.

[0093] In this embodiment, the depth of the thread groove of the cylindrical section 210 remains unchanged, that is, the upper part of the implant has no taper, which significantly improves the self-tapping property of the implant, thereby increasing the initial stability. When the implant is screwed into the implant socket, the thread of the tapered section 220 gradually squeezes the bone tissue along the direction from the top 160 to the coronal end 110, so the force applied is smaller, the friction between the implant and the bone tissue is small, and the heat generation is also small, which reduces the pain of the recipient and is more convenient for installation.

[0094] See also Figure 2 , along the direction extending from the crown end 110 to the top end 160, the core 140 includes a second tapered core segment 250, a cylindrical core segment 240, and a first tapered core segment 230 which are arranged successively.

[0095] In this embodiment, the core 140 is divided into three sub-parts. The first conical core section 230 is conducive to the installation of the implant. Since the top 160 of the threaded structure is first screwed into the implant socket in the recipient's mouth, the radial dimension of the gradual thread at the top 160 is the smallest, which can play a positioning and guiding role in the narrow space of the recipient's mouth, and the implant can be aligned with the implant socket without applying force to the implant. The cylindrical core section 240 can provide radial support for the bone tissue and improve the initial stability. The second conical core section 250 makes the diameter of the core 140 of this section gradually increase from the top 160 to the crown end 110, forming an effective radial compression on the cartilage, thereby further improving the initial stability.

[0096] See also Figure 2 The included angle between the generatrix of the conical section 220 and the central longitudinal axis is set to α3, and the included angle between the generatrix of the first conical core section 230 and the central longitudinal axis is set to α1, and α1 is greater than α3.

[0097] The outer diameter of the lateral surface 263 is defined by the outer diameter of the implant blank before thread processing, and the blank shape includes a cylindrical section 210 and a conical section 220, wherein the taper angle of the generatrix of the conical section 220 relative to the central longitudinal axis L is α3. The shape of the core 140 includes: a first conical core section 230, a cylindrical core section 240, and a second conical core section 250, wherein the taper angle of the generatrix of the first conical core section 230 relative to the central longitudinal axis L is α1, and the taper angle of the generatrix of the second conical core section 250 relative to the central longitudinal axis L is α2.

[0098] In one embodiment, the angle α3 between the generatrix of the conical section 220 and the central longitudinal axis is always less than 15°, and the cone angle α1 of the generatrix of the first conical core section 230 relative to the central longitudinal axis L and the cone angle α2 of the generatrix of the second conical core section 250 relative to the central longitudinal axis L are always less than 20°, which is conducive to improving the self-tapping property of the implant. Because the cone angle design in which α2 is always less than 20° can provide stronger initial stability, because the small cone angle can disperse the pressure more evenly when the implant is implanted. Enhance the implant insertion force, which is suitable for scenes with strong surgical guidance. Improve the implant's penetration performance in the bone during the screw-in process. The cone angle design in which α3 is always less than 15° can provide stronger initial stability, because the small cone angle can disperse the pressure more evenly when the implant is implanted. Enhance the implant insertion force, which is suitable for scenes with strong surgical guidance. Improve the implant's penetration performance in the bone during the screw-in process.

[0099] The lengths of the conical section 220 and the first conical core section 230 are equal, and α1 is greater than α3, which makes the thread height 265 of the thread of this section gradually increase in the direction from the crown end 110 to the top 160, because it is advantageous to have a thread with a large thread height 265 at the top 160, which can improve the self-tapping and initial stability of the implant. In addition, there is no taper angle on the outer contour of the implant in the cylindrical section 210, which can increase the initial stability, because when the implant is screwed into a drill hole (implantation socket) of a given diameter, a large number of thread peaks can be cut into the hole wall. At the same time, by virtue of the characteristics of the gradual thread, the cartilage in the hole wall can be squeezed step by step in the axial direction, which helps to compress the cartilage in the radial direction, thereby increasing the initial stability. At the same time, due to the presence of the second conical core section 250, the diameter of the core 140 of this section gradually increases in the direction of the crown end 110, which can form radial squeezing on the cartilage, thereby further improving the initial stability.

[0100] In the embodiment, the outer contour of the cylindrical core segment 240, the outer contour of the cylindrical segment 210 and the straight line formed by the intersection of the same tangent plane are arranged in parallel, so that the thread height 265 of the cylindrical core segment 240 is a constant value, preferably 0.3 mm.

[0101] The width of the threaded lateral surface 263 can be controlled by combining the core 140, the outer diameter of the threaded lateral surface 263 and the pitch 170. In the illustrated embodiment, the width of the threaded lateral surface 263 in the first conical core section 230 and the cylindrical core section 240 is never less than 0.05 mm and no more than 0.5 mm. Because too narrow a width of the lateral surface 263 will cause the thread to break or deform at the top 160 of the thread, while too wide a width will lose the cutting function of the thread and make the screw-in torque too large. Therefore, it is preferred that the width of the lateral surface 263 is 0.2 mm to improve the self-tapping ability of the implant and keep the insertion torque within an acceptable level.

[0102] In one embodiment, the angle β between the coronal side 261 and the top side 262 of the thread of the gradual thread section 130 gradually increases from 0° to 90° along the coronal direction. Therefore, compared with the thread near the coronal end 110, the thread bottom width 264 near the top 160 is smaller and therefore sharper, which improves the self-tapping property. At the same time, during the screwing process of the implant, the thread bottom width 264 at the cartilage becomes wider, thereby forming axial compression with the cartilage at this location, which improves the initial stability. As a preferred embodiment, the angle β gradually increases from 35° to 50° along the coronal end 110 direction, because the size of the angle β determines the size of the thread bottom width 264. Therefore, if the thread bottom width 264 is too small during the screwing process of the implant, the thread is easily deformed and damaged. At the same time, the thread bottom width 264 cannot be too large. Too large will increase the screwing torque of the implant and generate a lot of heat due to friction, and will also cause excessive compression of the cartilage, which will cause damage to bone cells and blood vessels in the bone.

[0103] In the embodiment, at the conical section 220 and the first conical core section 230, since the angle between the generatrix of the first conical core section 230 and the central longitudinal axis is greater than the angle between the generatrix of the conical section 220 and the central longitudinal axis, the thread height 265 there gradually increases in the direction from the crown end 110 to the top end 160, which can improve the self-tapping property and initial stability of the implant.

[0104] In one embodiment, the diameter of the second conical core segment 250 and the diameter of the first conical core segment 230 gradually decrease along the direction extending from the crown end 110 to the top end 160; wherein the diameter of the second conical core segment 250 is greater than the diameter of the first conical core segment 230.

[0105] The diameters of the two tapered core 140 sections constituting the core 140 gradually decrease in the direction extending from the coronal end 110 to the top end 160. In a given implant socket, the characteristics of the gradual thread can be used to achieve step-by-step compression of the bone tissue in the axial direction, and the thread can be combined with the radial compression of the bone tissue to increase the initial stability. The diameter of the second tapered core section 250 is greater than the diameter of the first tapered core section 230 to ensure that the core 140 profile is tapered.

[0106] In the embodiment, the cylindrical core section 240 of the core 140 is arranged parallel to the cylindrical section 210 of the gradient thread section so that the thread height 265 of the cylindrical core section 240 can be a constant value. During the process of screwing the implant into the implant socket, the lower thread of the cylindrical core section 240 exerts less squeezing force on the upper thread, so the friction is smaller, the heat is less, and the pain of the recipient can be reduced.

[0107] In the embodiment, the tapered section 220 of the tapered thread segment is equal to the length of the first tapered core section 230 of the core 140, so that the thread height 265 of the thread in this section gradually increases in the direction from the coronal end 110 to the top 160. Setting a higher height thread at the top 160 can improve the self-tapping property and initial stability of the implant.

[0108] See also Figure 1 , 4 Or 5, at least one cutting groove 150 is provided on the gradual thread segment, and the at least one cutting groove 150 extends from the crown end 110 to the top end 160 in a spiral manner.

[0109] In this embodiment, the cutting groove 150 is processed on the gradual thread. At least one cutting groove 150 is provided to spirally transport the bone tissue cut by the thread, so as to avoid the phenomenon of increasing cutting resistance caused by the accumulation of bone tissue, thereby reducing friction, generating less heat, alleviating the pain of the recipient, and improving the initial stability of the implant.

[0110] Preferably, two cutting grooves 150 can be provided on the thread, and three cutting grooves 150 are most preferably provided. The cutting groove 150 extends from the top to the crown in a spiral manner, so that the spiral cutting groove 150 of the implant can cut cartilage and transport bone chips spirally upward during implantation. The end of the cutting groove 150, i.e., the cutting groove tail 152, extends to 0 to 1 mm above the tapered section 220. Because the top of the implant is generally a self-tapping section, the cutting groove 150 extending to above the tapered section 220 can continuously play the function of bone tissue cutting within the full length of the implant thread. In addition, the cutting groove 150 can effectively guide the bone chips generated by cutting to be discharged from the tapered section 220, and the cutting groove 150 extending from the top to above the tapered section 220 can effectively discharge the bone chips into the implant vertical section. Thereby accelerating the bone healing speed, the extension distance is too long so that the bone chips cannot be fully discharged into the 0.1mm gap of the vertical section, so the preferred solution is that the cutting groove 150 extends from the top to 0 to 1 mm above the tapered section 220.

[0111] See also Figure 3 At least one cutting groove 150 forms at least one cutting surface on the gradual thread segment, and at least one cutting surface is perpendicular to the tangent direction of the gradual thread rotation direction.

[0112] The cutting edge surface 151 on the cutting groove 150 should be perpendicular to the tangential direction of the thread rotation direction directly above it, because this can significantly improve the cutting ability of the cutting edge surface 151. At the same time, the cutting bottom surface 153 at the bottom of the cutting groove 150 is perpendicular to the cutting edge surface 151, so that the bottom surface of the cutting groove 150 and the cutting edge surface 151 cooperate to form a spiral groove, thereby realizing the chip guiding function, that is, during the process of screwing the implant into place, the bone chips cut by the cutting edge surface 151 can be transported upward by the groove spiral and distributed to the gap between the implant and the cartilage, which is beneficial to improving the initial stability and the speed of bone healing.

[0113] This embodiment can significantly improve the cutting ability of the cutting edge surface 151 . The cutting bottom surface 153 at the bottom of the cutting groove 150 is perpendicular to the cutting surface, so that the cutting bottom surface 153 and the cutting surface form a spiral right-angle groove, thereby improving the chip guiding ability of the cutting groove 150 .

[0114] The dental implant provided in the present application can be roughened using any known surface roughening method, preferably using sandblasting and acid etching.

[0115] The dental implant provided in the present application can be made of any known material suitable for preparing an implant, preferably titanium, zirconium, tantalum, titanium alloy or zirconium oxide.

[0116] The dental implant provided in the present application may be a bone-level implant or a tissue-level implant.

[0117] The tapered thread segment provided in the present application can be used for a single-piece, two-piece, or multi-piece implant. In a preferred embodiment, the implant is an anchoring portion of a two-piece implant, wherein the tapered thread extends helically along the central longitudinal axis L thereof.

[0118] In one embodiment, the pitch of the tapered thread can be set to 0.6-2.4 mm. The width of the lateral surface is set in the range of 0.05 mm to 0.5 mm. The thread height of the tapered thread in the cylindrical core section is 0.3 mm.

[0119] The thread height 265 of the gradual thread is set in the range of 0.1mm-0.2mm to reduce the bone absorption of the neck. The thread height 265 of the gradual thread is set in the range of 0.25mm-0.35mm to provide the main initial stability. The thread height 265 of the gradual thread is set in the range of 0.35mm-0.5mm to enhance the self-tapping ability.

[0120] In this embodiment, the design of the dental implant is mainly biased towards stability and increasing the versatility of the dental implant, so a thread height 265 of 0.3 mm is preferred.

[0121] In addition, a bone implant is provided, comprising a non-gradient thread segment and the gradient thread segment as described above, wherein the non-gradient thread segment is continuously connected to the gradient thread segment.

[0122] In this embodiment, the thread structure of the non-gradient thread segment refers to a thread other than the above-mentioned gradual thread pitch. The thread of the non-gradient thread segment does not have a tendency to change gradually, that is, the pitch of the thread of the non-gradient thread segment can be constant, such as a standard thread. Taking the dental implant as an example, the non-gradient thread is used in combination with the gradual thread, and the non-gradient thread segment is usually arranged at the crown end of the dental implant, or close to the crown end. In the process of the dental implant being screwed into the bone tissue, the non-gradient thread is screwed in along the trajectory of the gradual thread. Due to the different thread structures, the outer surface of the non-gradient thread will perform dislocation compression on the bone tissue, thereby increasing the friction between the thread and the bone tissue, so that the implant and the bone tissue form a stable connection, and the initial stability is improved.

[0123] Specifically, in this embodiment, the standard thread is a thread whose tooth profile, diameter and pitch all meet relevant standards and is a conventional thread. The standard thread can be an equidistant thread with the same pitch, using mature technology, easy to process, and can effectively control the production cost. Figure 1 The non-gradient thread segment includes a core and a gradient thread segment 130. The non-gradient thread segment and the gradient thread segment are arranged on the same core, and the gradient thread segment 130 is arranged on the core. The gradient thread segment of the dental implant includes the gradient thread segment 130 and the standard thread segment 120. Figure 2 , the gradient thread segment 130, that is, the angle β between the thread crown side 261 and the top side 262 in this segment changes along its axial direction. The standard thread segment 120, that is, the angle β between the thread crown side 261 and the top side 262 in this segment remains constant along its axial direction. The end of the crown end 110 is the crown bevel 111, below which is the neck segment 112, and the neck segment 112 is continuously connected to the standard thread segment 120. In addition, in the thread of each implant, multiple gradient thread segments 130 or multiple standard thread segments 120 can be set. In the preferred embodiment of the present application, the threads of the implant all use gradient thread segments 130.

[0124] In this embodiment, the dental implant can be provided with a combination of a gradual thread section and a non-gradient thread section to improve the application range of the dental implant. The non-gradient section can be provided to adapt to the oral environment of different recipients, and the thread structure can be flexibly adapted to different alveolar bone structures, shapes, and textures, thereby meeting biocompatibility and having a wider application range.

[0125] It should be noted that the above embodiments are also applicable to other orthopedic implant fields, and this application will not go into details one by one.

[0126] In addition, the present application also provides a dental implant assembly, including an abutment, a connecting screw, and the dental implant as described above, wherein the abutment is placed in the dental implant, and the connecting screw is fixed to the abutment.

[0127] In the present implementation, the dental implant assembly is a split design, including a dental implant, an abutment and a connecting screw, and the abutment is fixed in the dental implant. The abutment is connected to the connecting screw and provides a mounting base for the connecting screw. It should be noted that the connecting screw can be fixed on the abutment, and the connecting screw can be used to fix the denture. In some embodiments, the connecting screw can also be a part of the denture. The dental implant can provide good initial stability and long-term stability for the dental implant assembly. The abutment can be selected with different structures or materials as needed to meet the needs of the gingival tissue of different recipients and improve biocompatibility. The connecting screw can also be selected according to the actual selection of different recipients' oral environments. It not only ensures the initial stability and long-term stability of the dental implant assembly, but also provides the best solution for different recipients to adapt to biocompatibility.

[0128] In other embodiments, the implant assembly may also include two basic parts: an implant portion and a base portion. The implant portion is the dental implant mentioned above, and the base portion is the base mentioned above. The implant portion is mainly used to be embedded in the bone and integrated with the bone tissue, thereby providing a firm anchor for the base. The base can be fixed to the implant portion by bonding, threading or inlaying. In the latter case, the implant portion and the base effectively form a single component, and future advances may enable the base and the implant portion to be formed as one piece, such as by 3D printing, powder injection molding, and compression molding. In addition, a portion of the base extends outward from the implant portion to support the connecting screw, which allows at least a portion of the base to be accommodated in the connecting screw.

[0129] Commonly used implants today are usually constructed in two or more parts, in which case the implant consists of at least an implant component, which is often referred to as an implant alone, and a separate abutment, which is sometimes referred to as a spacer. The implant component can be completely embedded in the bone, that is, at the height of the alveolar ridge, or it can protrude a few millimeters from the alveolar ridge into the soft tissue.

[0130] Compared to single-piece implants, multi-piece implants are more versatile because the implant components and the abutment can be adapted to individual requirements. In particular, the appropriate abutment shape and angle can be selected after the implant components have been inserted. This provides the surgeon with greater flexibility and room for error. A further advantage of multi-piece implants is that the abutment and the implant part can be made of different materials, which in turn provides more options for biocompatibility.

[0131] The implant part in this embodiment is the same as the above-mentioned dental implant, and its specific structural configuration is referred to above, and will not be described in detail. The base part can use an existing base, which only needs to match the implant part and ensure its implant stability, and this application does not make specific limitations.

[0132] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, and do not limit it. Although the present application has been described in detail with reference to the aforementioned embodiments, ordinary technicians in this field should understand that they can still modify the technical solutions recorded in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present application.

Claims

1. A bone implant, characterized in that: include: a tapered thread segment having tapered threads extending from the apical end side to the coronal end side along the central longitudinal axis of the bone implant; The tapered thread comprises: a top side surface, a crown side surface, and a lateral surface connecting the top side surface and the crown side surface, wherein the lateral surface defines a radially outer surface of the tapered thread, and the tapered thread extends helically in the direction of the central longitudinal axis; Wherein, the top side surface includes at least two slope surfaces, and along the direction extending from the top end side to the crown end side, one of the at least two slope surfaces gradually increases in proportion to the width of the top side surface, and the slope of the slope surface is smaller than that of the other slope surfaces.

2. The bone implant according to claim 1, characterized in that Along the direction extending from the top end side to the crown end side, a proportion of the width of the top side surface occupied by one of the at least two slope surfaces is set to m, wherein the value range of m is 0%<m<100%.

3. The bone implant according to claim 2, characterized in that Along the direction extending from the top end to the crown end, the proportion of the width of one of the at least two slope surfaces to the width of the top side surface gradually increases at a constant variable.

4. The bone implant according to any one of claims 1 to 3, characterized in that: The top side surface of the gradual thread segment includes N slope surfaces connected in sequence, wherein the first slope surface is connected to the tooth bottom, and the Nth slope surface is connected to the tooth top, and along the direction extending from the top end side to the crown end side, the width proportion of the first slope surface gradually increases.

5. The bone implant according to claim 1, characterized in that It also includes a core part, and the gradual thread of the gradual thread segment extends radially outward along the core part, wherein the core part matches the implantation socket, and the inner diameter of the implantation socket is larger than the outer diameter of the core part.

6. The bone implant according to claim 5, characterized in that Along the direction extending from the top end to the crown end, the core is formed by a cylindrical section and a conical section which are arranged successively.

7. The bone implant according to claim 6, characterized in that Along the direction extending from the top end to the crown end, the core includes a first conical core section, a cylindrical core section, and a second conical core section which are arranged successively.

8. The bone implant according to claim 7, characterized in that The included angle between the generatrix of the tapered section and the central longitudinal axis is set to α3, and the included angle between the generatrix of the first tapered core section and the central longitudinal axis is set to α1, and α1 is greater than α3.

9. The bone implant according to claim 7, characterized in that The outer contour of the cylindrical core segment is parallel to a straight line formed by the intersection of the outer contour of the cylindrical segment and the same tangent plane.

10. The bone implant according to claim 9, characterized in that The tapered section is equal in length to the first tapered core section.

11. The bone implant according to claim 6, characterized in that At least one cutting groove is arranged on the gradual thread, and the at least one cutting groove extends from the top end to the crown end in a spiral manner.

12. The bone implant according to claim 11, characterized in that The at least one cutting groove forms at least one cutting surface on the gradual thread structure, and the at least one cutting surface is perpendicular to the tangent direction of the gradual thread rotation direction.

13. The bone implant according to claim 6, characterized in that The pitch of the gradual thread is 0.6-2.4 mm.

14. The bone implant according to claim 7, characterized in that The width of the lateral surface of the tapered thread on the cylindrical core section is 0.2 mm.

15. The bone implant according to claim 12, characterized in that The cutting groove extends from the top end to 0 to 1 mm above the tapered section.

16. The bone implant according to claim 8, characterized in that The α1 is less than 20°, and the α3 is less than 15°.

17. The bone implant according to claim 7, characterized in that The width of the lateral surface is set in a range between 0.05 mm and 0.5 mm.

18. The bone implant according to claim 9, characterized in that The thread height of the tapered thread in the cylindrical core section is 0.3 mm.

19. A bone implant, characterized in that: It comprises a non-gradually changing thread segment and a gradually changing thread segment as described in any one of claims 1 to 18, wherein the threads of the non-gradually changing thread segment are continuously connected with the gradually changing thread segment.

20. A dental implant assembly, characterized in that: The invention comprises a base, a connecting screw, and the bone implant according to any one of claims 1 to 19, wherein the base is placed in the bone implant, and the connecting screw is fixed to the base.

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