Bone implants and dental implant components with tapered threads

Abstract

This application relates to the field of bone implant technology, providing a bone implant with a tapered thread and a dental implant assembly. The bone implant includes a tapered thread segment with a tapered thread extending from the apex side to the coronal side along the central longitudinal axis of the bone implant. The tapered thread includes a top surface, a coronal surface, and a lateral surface connecting the top surface and the coronal surface. The lateral surface defines a radially outer surface of the tapered thread, which extends helically along the central longitudinal axis. The top surface includes at least two sloped surfaces. In the direction extending from the apex side to the coronal side, one of the sloped surfaces gradually increases in proportion to the width of the top surface, and the slope of this sloped surface is smaller than that of the other sloped surfaces. This application facilitates bone attachment, achieves the desired mechanical effect with less bone compression per unit area, reduces damage to bone cells and blood vessels, and improves the initial stability and speed of bone integration after implantation.

Description

Technical Field

[0001] This application relates to the field of bone implant technology, and more particularly to a bone implant with tapered threads and a dental implant assembly. Background Technology

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

[0003] After implantation, the proper distribution of stress on its surface directly affects the success rate of osseointegration and repair. In other words, osteocytes attach to the implant surface, allowing the implant to integrate with the bone tissue. Osseointegration typically takes 3-6 months. During this period, the implant must be mechanically and firmly held within the bone. This mechanical fixation of the implant within the bone is called "initial stability." Most modern implants have threads on their outer surface for screwing the implant into and securing it within pre-prepared drill holes. These threads provide initial stability during osseointegration, and the rough walls provide a larger attachment surface area for osteocytes compared to smooth-walled implants. Long-term stability refers to the implant's ability to remain stable, without peri-inflammatory inflammation or bone resorption after implantation. The shape of the external threads significantly impacts not only initial stability but also the speed and success rate of osseointegration.

[0004] Current implant thread designs have replaced traditional parallel-wall (cylindrical) implants with implants that taper at the top of the core. Typically, the portion of the implant that penetrates the bone is called the tip, and the other end is called the coronal end. During insertion, the implant experiences significant compression against the jawbone due to the gradually rising thread grooves. However, this compression cannot be excessive, as greater compression increases friction, generating more heat during insertion and increasing patient discomfort. Furthermore, excessive compression can damage bone cells and blood vessels, delay bone healing, and even lead to implantation failure.

[0005] Therefore, how to improve the initial stability and biomechanical distribution of implants while ensuring minimal bone damage, thereby reducing surgical time and implant failure, is a pressing technical problem that needs to be solved. Summary of the Invention

[0006] To address at least one of the aforementioned technical problems, this application provides a bone implant with a tapered thread and a dental implant assembly. The tapered thread segment enhances the initial stability of the bone implant. During insertion, the tapered thread extends from the apical side to the coronal side, with one slope surface gradually increasing in width relative to the apical side. This tapered thread compresses the cortical and cancellous bone. Subsequent threads follow the trajectory of the preceding threads, gradually increasing the compressive force and further improving the initial stability of the implant. Since both the apical and coronal sides of the tapered thread compress the cartilage, and similar to conventional implants, the thread grooves gradually rise. Therefore, compared to conventional implants that rely on core compression, the bone compression area is significantly increased, facilitating bone attachment and resulting in a larger stress area. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability requirements with less bone compression. This reduces damage to bone cells and blood vessels, improving the initial stability and speed of bone integration after implantation, making it ideal for immediate implantation.

[0007] Therefore, in a first aspect, this application provides a bone implant, comprising: a tapered thread segment having tapered threads extending from a apex side to a coronal side along the central longitudinal axis of the bone implant. The tapered threads include: a top surface, a coronal surface, and a lateral surface connecting the top surface and the coronal surface, the lateral surface defining a radially outer surface of the tapered thread segment, the tapered threads extending helically along the central longitudinal axis. The top surface of the tapered thread includes at least two sloped surfaces, and along the direction extending from the apex side to the coronal side, one of the sloped surfaces gradually increases in proportion to the width of the top surface, and the slope of this sloped surface is smaller than the other sloped surfaces.

[0008] This implementation method incorporates a gradually tapered thread segment on the surface of the bone implant. This segment enhances the initial stability of the implant. The tapered thread segment, with its gradually tapering threads, compresses the cortical and cancellous bone during insertion. As the implant is screwed in, the threads (i.e., the tapered threads) extend from the apical side to the coronal side, with one slope gradually increasing in width relative to the apical side. Simultaneously, as the implant is screwed in, lower threads follow the trajectory of higher threads, gradually increasing the compressive force. Because both the apical and coronal sides of the tapered thread segment compress the cartilage, the bone compression area is significantly increased, facilitating bone attachment and resulting in a larger stress area. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability with less bone compression. This reduces damage to bone cells and blood vessels, accelerates bone integration after implantation, and significantly improves implant success rates while reducing patient discomfort.

[0009] Based on the above-mentioned bone implant, in the direction extending from the top side to the coronal side, the proportion of the width of one of the two slope planes to the top side is set as m, where the value of m ranges from 0% to m to 100%.

[0010] In this implementation, the proportion of one of the at least two sloped surfaces constituting the top side gradually increases from 0% to 100% along the direction extending from the apex to the coronal end. That is, along the direction extending from the apex to the coronal end, the proportion of one of the sloped surfaces constituting the top side gradually increases from none until the entire top side is completely composed of this single sloped surface. This allows for a gradual increase in compressive force during the insertion of the bone implant, until the compressive force reaches its maximum. This structure facilitates bone attachment, has a larger stress-bearing area, and achieves the desired mechanical effect with less bone compression per unit area, thus meeting the requirements for initial stability.

[0011] In conjunction with the aforementioned bone implants, along the direction extending from the apex to the coronal end, the proportion of the width of one of the at least two slope planes to the width of the apex side gradually increases with a constant variable.

[0012] In this implementation, one of the slope surfaces forming the top side gradually increases with a constant variable along the direction extending from the apex to the coronal end. This allows the force applied to the cortical and cancellous bone to increase steadily and evenly, reducing the recipient's pain and avoiding discomfort caused by too rapid an increase in compressive force.

[0013] In conjunction with the aforementioned bone implant, the top surface of the gradually threaded segment includes N sequentially connected slope surfaces, wherein the first slope surface connects to the tooth floor and the Nth slope surface connects to the tooth roof. Along the direction extending from the top side to the coronal side, the width of the first slope surface gradually increases.

[0014] In this implementation, the top surface is composed of N sloped surfaces, which are connected sequentially. The first sloped surface connects to the tooth floor, and the Nth sloped surface connects to the tooth crest. Extending from the apical side towards the coronal side, the proportion of the width of the first sloped surface gradually increases. The gradually tapering thread of the bone implant compresses the cortical and cancellous bone. Simultaneously, during implant insertion, lower threads follow the trajectory of higher threads, gradually increasing the compressive force. Because the proportion of the first sloped surface continuously increases, the bone compression area significantly increases. The desired mechanical effect can be achieved with less bone compression per unit area, thus achieving initial stability requirements with less bone compression.

[0015] In addition to the above-mentioned bone implant, it also includes a core, and the gradually tapered thread of the tapered thread section extends radially outward along the core, wherein the core matches the implant socket, and the inner diameter of the implant socket is larger than the outer diameter of the core.

[0016] In this implementation, the core of the bone implant serves as the carrier for the tapered thread segment, with the tapered thread extending radially outward along the core. Because both the top and coronal sides of the tapered thread compress the cartilage, the bone compression area is significantly increased, facilitating bone attachment. The desired mechanical effect can be achieved with less bone compression per unit area, and initial stability requirements can be met with less bone compression. This reduces damage to osteocytes and blood vessels, and accelerates the integration of the implant with bone after implantation. Furthermore, a gap exists between the implant socket and the core. When the bone implant is screwed into the implant socket, bone fragments are discharged into this gap. These bone fragments act similarly to bone powder, filling the gap and making the connection between the bone implant and bone tissue more stable.

[0017] In conjunction with the aforementioned bone implant, the gradually tapered section is formed by sequentially arranged cylindrical and conical sections along the direction extending from the coronal end to the apex.

[0018] In this implementation, the depth of the threaded groove in the cylindrical section remains unchanged, meaning the upper part of the implant has no taper. This significantly improves the self-tapping ability of the implant, making insertion easier. During the insertion of the implant into the implant socket, the tapered section, along the direction from the apex to the coronal end, gradually compresses the bone tissue with its threads. Therefore, the applied force is smaller, resulting in less friction between the implant and the bone tissue, less heat generation, reducing patient discomfort, and facilitating installation.

[0019] In conjunction with the aforementioned bone implant, the core portion extends from the apex to the coronal end, comprising a first conical core segment, a cylindrical core segment, and a second conical core segment arranged sequentially.

[0020] In this implementation, the core portion consists of three sub-parts. The first conical core section facilitates implant placement. Because the tip of the threaded structure is screwed into the implant socket in the recipient's mouth first, the radial dimension of the tapered thread at the tip is minimal. This allows for positioning and guidance within the confined space of the recipient's mouth, ensuring the implant is aligned with the socket without applying force. The cylindrical core section provides radial support to the bone tissue, improving initial stability. The second conical core section features a gradually increasing core diameter from the tip to the coronal end, effectively compressing the cartilage radially, further enhancing initial stability.

[0021] Based on the above-mentioned bone implants, the angle between the generatrix of the conical segment and the central longitudinal axis is set as α3, and the angle between the generatrix of the first conical core segment and the central longitudinal axis is set as α1, where 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 at this location gradually increases from the crown end to the top, which can improve the self-tapping ability 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 the straight line formed by the intersection of the same cross-section.

[0024] In this implementation, the outer contours of the cylindrical core section and the cylindrical section of the gradually tapering thread structure are set parallel to the straight line formed by the intersection of the same tangent. This allows the thread height of the cylindrical core section to be a fixed value. During the process of the implant being screwed into the implantation socket, the extrusion force of the lower thread of the cylindrical core section on the upper thread is small, resulting in less friction and less heat generation, which can reduce the pain of the recipient.

[0025] Combined with the aforementioned bone implant, the length of the conical segment is equal to that of the first conical core segment.

[0026] In this implementation, the tapered section of the gradually tapered thread structure has the same length as the first tapered core section of the core, which allows the thread height of the thread in this section to gradually increase from the crown end to the top end. Setting a higher thread height at the top end can improve the self-tapping ability and initial stability of the implant.

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

[0028] In this implementation, at least one cutting groove is provided to spirally transport the bone tissue cut off by the thread, avoiding the phenomenon of increased 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 conjunction with the aforementioned bone implant, at least one cutting groove forms at least one cutting surface on the tapered thread, and the at least one cutting surface is perpendicular to the tangential direction of the tapered thread's rotation.

[0030] This implementation can significantly improve the cutting capability of the cutting edge. 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 helical right-angle groove, which improves the chip guiding capability of the cutting groove.

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

[0032] In conjunction with the aforementioned bone implant, the width of the lateral surface of the tapered thread on the cylindrical core section is 0.2 mm.

[0033] In conjunction with the aforementioned bone implant, the cutting groove extends from the top to 0 to 1 mm above the conical section.

[0034] Based on the above-mentioned bone implants, α1 < 20°, α3 < 15°.

[0035] In conjunction with the above-mentioned bone implants, the width of the lateral surface is set between 0.05 mm and 0.5 mm.

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

[0037] In addition to the bone implants described above, there are also non-gradient threaded sections and threaded connections between the non-gradient threaded sections and the graded threaded sections.

[0038] In this implementation, the bone implant can be configured with a combination of gradient and non-gradient thread structures to improve its applicability. The non-gradient section can adapt to the bone tissue environment of different recipients. For different bone structures, shapes, and textures, the thread structure can be flexibly adapted to meet biocompatibility requirements and broaden its applicability.

[0039] Thirdly, a dental implant assembly is provided, including an abutment, a connecting screw, and a bone implant as described above, wherein the abutment is placed within the bone implant and the connecting screw is fixed to the abutment.

[0040] In this implementation, the dental implant assembly is a modular design, comprising a bone implant, an abutment, and a denture. The abutment is fixed within the bone implant. The abutment connects to the denture and provides a mounting base. The bone implant provides excellent initial and long-term stability for the dental implant assembly. Different structures or materials can be selected for the abutment to meet the needs of different recipients' gingival tissues and improve biocompatibility. The denture can also be selected based on the specific oral environment of each recipient. This approach ensures both initial and long-term stability of the dental implant assembly while providing optimal solutions for different recipients, thus maximizing biocompatibility.

[0041] Compared with existing technologies, the bone implant and dental implant assembly provided in this application with a gradually tapered thread have the following advantages: the bone implant achieves axial-level progressive compression of the bone tissue within the implant socket by setting a gradually tapered thread segment. During the insertion process, as the thread of the tapered thread segment extends from the apex side to the coronal side, the proportion of the width of one of the slope surfaces to the apex side gradually increases. The tapered thread of the bone implant compresses the cortical bone and cancellous bone. The lower thread advances along the trajectory of the upper thread, gradually increasing the compressive force. Combined with the radial compression of the bone tissue by the thread, the initial stability of the implant can be further improved. Because both the top and coronal sides of the tapered thread compress the cartilage, and similar to traditional implants, the thread grooves gradually rise. Therefore, compared to conventional implants that rely on core compression of bone, the bone compression area is significantly increased, facilitating bone attachment and resulting in a larger stress area. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability requirements with less bone compression. This reduces damage to bone cells and blood vessels, and increases the speed of implant integration with bone after implantation. This solves the technical problems of existing technologies, such as significant bone damage during bone implantation, a single mechanical distribution of the implant within the bone groove, poor initial stability, and high implantation failure rates.

[0042] Other features and advantages of this application will be described in detail in the following detailed embodiments section. Attached Figure Description

[0043] The accompanying drawings used in the description of the embodiments or prior art are briefly introduced below.

[0044] Figure 1 This is a schematic diagram of a gradient thread provided in an embodiment of this application;

[0045] Figure 2 This is a cross-sectional and partial structural schematic diagram of a bone implant provided in an embodiment of this application;

[0046] Figure 3 This is a bottom view of a bone implant provided in an embodiment of this application;

[0047] Figure 4 This is a schematic diagram of the structure of a bone implant provided in an embodiment of this application;

[0048] Figure 5 A schematic diagram of stress distribution during the fusion of a bone implant with bone tissue, provided as an embodiment of this application;

[0049] Figure 6 This is a schematic diagram of the structure of a gradually threaded section of a bone implant provided in an embodiment of this application;

[0050] Figure 7 This is a partial cross-sectional structural diagram of a gradient thread provided in an embodiment of this application.

[0051] Figure label:

[0052] 110. Crown end; 111. Crown bevel; 112. Neck section; 120. Standard thread section; 130. Gradient thread section; 140. Core; 150. Cutting groove; 151. Cutting edge; 152. Cutting groove tail; 153. Cutting bottom surface; 160. Top tip; 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 lateral surface; 262. Top lateral surface; 263. Lateral surface; 264. Thread root width; 265. Thread height; 2621. First slope surface; 2622. Second slope surface; 268. Tooth crest; 269. Tooth root. Detailed Implementation

[0054] The technical solutions in the embodiments of this application will now be described with reference to the accompanying drawings.

[0055] In the description of this application, the terms “center,” “upper,” “lower,” “front,” “rear,” “left,” “right,” “vertical,” “horizontal,” “top,” “bottom,” “inner,” and “outer,” etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are used only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0056] In the description of this application, it should be noted that, unless otherwise expressly specified and limited, the terms "installation", "connection" and "joining" should be interpreted broadly, for example, they can be fixed connections, detachable connections, mating connections or integral connections; those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

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

[0058] Bone implants are medical devices used in orthopedics and dentistry to replace or repair bone tissue lost due to disease, injury, or congenital defects. The optimal stress distribution on the implant surface directly affects osseointegration and the long-term success rate of implant restoration. However, the stress on the implant surface can be altered by designing the threads to change the mechanical transmission of the implant and the stress distribution at the bone interface. Furthermore, the shape of the surface threads not only significantly influences the speed of osseointegration but also improves initial implant stability, increases implant surface area, and optimizes stress distribution at the bone interface. Therefore, surface thread design plays a crucial role in the biomechanical optimization of implants.

[0059] Taking dental implants as an example, currently commonly used implants with a tapered core, during insertion, experience significant compression against the jawbone due to the rising thread grooves along the crown direction. Excessive compression means greater friction between the implant and the jawbone, generating more heat during insertion. Furthermore, excessive bone compression can damage bone cells and blood vessels, delay bone healing, and even lead to implantation failure. Increased friction and compression also increase resistance during insertion, requiring a larger insertion torque, which further increases the risk of mechanical damage. Conversely, the bone compression cannot be too small, as this reduces initial stability. However, due to significant differences in jawbone density and hardness among individuals, the compression effect of the same implant varies greatly when placed in different people's jaws, making it difficult to achieve a balanced implant design. Therefore, there is a need for implants with low bone compression but high initial stability.

[0060] Furthermore, since the strength of cortical bone in the jawbone is much greater than that of cancellous bone, the threads on the cortical bone should have sufficient strength. The tapered-end implant, due to its processing method, raises the groove between the coronal threads, which significantly increases the strength of the threads in the cortical bone. However, the contact area between the threads and the jawbone is significantly reduced, decreasing the bone attachment area and the stress area. Therefore, this type of implant is prone to loosening during repeated loading, leading to peri-implantitis and subsequent bone resorption, thus reducing long-term stability.

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

[0062] To facilitate understanding of this application, the following embodiments use dental implants applied in the field of dental implantology as examples.

[0063] like Figure 1-7As shown, the bone implant may include a tapered thread segment extending from the apex 160 side to the coronal end 110 side along the central longitudinal axis of the bone implant. The tapered thread segment includes a top surface 262, a coronal surface 261, and a lateral surface 263 connecting the top surface 262 and the coronal surface 261. The lateral surface 263 defines a radially outer surface of the tapered thread segment, and the thread of the tapered thread segment extends helically along the central longitudinal axis. The top surface 262 of the tapered thread segment includes at least two sloped surfaces. Along the direction extending from the apex 160 side to the coronal end 110 side, one of the sloped surfaces gradually increases in proportion to the width of the top surface 262, and the slope of this sloped surface is smaller than the other sloped surfaces.

[0064] In this embodiment, a dental implant is used as an example. The dental implant consists of a tip 160 and a crown 110. The tip 160 is the end that penetrates deep into the alveolar bone. The radial dimension of the thread at the tip 160 is small, and the thread height 265 is high, resulting in strong cutting ability. The crown 110 is the end that is away from the alveolar bone. The radial dimension of the thread at the crown 110 is larger, and the thread height 265 is smaller. The direction from the tip 160 to the crown 110 is the direction away from the alveolar bone, and the direction from the crown 110 to the tip 160 is the direction towards the alveolar bone.

[0065] Specifically, the dental implant includes a tapered threaded section extending from the coronal end 110 to the apex 160 along its central longitudinal axis. This tapered threaded section includes radially outward-extending threads (i.e., tapered threads). For example... 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. The lateral surface 263 defines the outermost radial surface of the thread. The top side surface 262 of the tapered thread segment includes at least two sloped surfaces extending laterally from the top end 160 to the crown end 110. The proportion of the width of one of the sloped surfaces gradually increases. Since the slope of this sloped surface is smaller than that of the other sloped surfaces, the thread width becomes wider as the proportion of the width of this sloped surface gradually increases. During the insertion of the bone implant, this gradually increases the pressure on the bone tissue, achieving the effect of compressing the bone. It should be noted that the slope in this embodiment refers to the angle formed between the surface of the sloped surface and the central longitudinal axis of the bone implant.

[0066] During insertion, the bone implant extends from the apex 160 to the coronal 110, with one of its sloped surfaces gradually increasing in width relative to the apex 262. The tapered thread section of the implant compresses both the cortical and cancellous bone. Simultaneously, as the implant is inserted, lower threads follow the trajectory of higher threads, gradually increasing the compressive force. Because both the apex 262 and coronal 261 of the tapered thread section compress the cartilage, the bone compression area is significantly increased, facilitating bone attachment and resulting in a larger stress area. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving good initial stability.

[0067] In one embodiment, the tapered thread segment extends from the tip 160 to the crown 110, and one of the at least two sloped surfaces occupies a percentage of the width of the top side surface 262, denoted as m, where m ranges from 0% to 100%. The percentage of one of the sloped surfaces constituting the top side surface 262 gradually increases until the entire top side surface 262 is entirely composed of this single sloped surface. This gradually increases the compressive force during the insertion of the bone implant, until the compressive force reaches its maximum. This structure facilitates bone attachment, provides a larger stress-bearing area, and achieves the desired mechanical effect with less bone compression per unit area, thus meeting the initial stability requirements.

[0068] Of course, in the direction extending from the apex 160 to the coronal end 110, the proportion of the width of one of the two slope faces to the width of the apex 262 can be gradually increased with a constant variable. This allows the force applied to the cortical and cancellous bone to increase steadily and evenly, reducing the recipient's pain and avoiding discomfort caused by too rapid an increase in compressive force.

[0069] This embodiment ensures that the compression effect (compression force) on the bone in each implanted segment is consistent, resulting in a more uniform and reasonable distribution of mechanical forces and avoiding excessive compression. Simultaneously, the implantation torque can be adjusted by changing the incremental gradient angle to prevent implantation difficulties.

[0070] It should be noted that, in the direction extending from the apex 160 to the coronal end 110, the proportion of the width of at least one of the two slope planes to the width of the apex side 262 can be gradually increased with a constant variable, or it can be set to gradually increase with a non-constant variable. The increment of the aforementioned slope plane in different sections of the gradient thread segment can be determined according to the patient's actual bone quality. The increment can also be freely combined and set. For example, if the bone density in the recipient's implantation area is uniform in a certain section, then that section will have a constant increment. Conversely, if the bone density in the recipient's implantation area exhibits a gradient in a certain section, then that section will have a gradient increment.

[0071] Compared to existing technologies, the gradually increasing width of the sloped surface at the top side (262) means a significantly larger area for the threads used to compress bone tissue. This disperses the heat generated when the implant is screwed in with the same torque, reducing patient discomfort. Furthermore, the significantly increased compression area between the threads and cartilage allows for greater bone compression per unit area to achieve the desired stabilizing effect, reducing damage to bone cells and intraosseous blood vessels. This improves the speed of implant integration with bone after placement. Simultaneously, the wider threads at the core (140) significantly enhance the strength of the threads in the cortical bone, increasing the contact area between the threads and cartilage and further dispersing the force, thus improving the implant's ability to withstand axial compressive forces.

[0072] In this embodiment, the bone implant utilizes a gradually tapering thread section to progressively compress the bone tissue within the implant socket along the axial direction. During insertion, the tapering thread section extends from the top 160 side to the coronal 110 side, with one of the sloped surfaces gradually increasing in width relative to the top surface 262. This tapering thread compresses both the cortical and cancellous bone. Lower threads follow the trajectory of higher threads, gradually increasing the compressive force. Since both the top surface 262 and the coronal surface 261 of the tapering thread compress the cartilage, the bone compression area is significantly increased, facilitating bone attachment and resulting in a larger stress area. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability with less bone compression. This reduces damage to bone cells and blood vessels, increases the speed of bone integration after implantation, and significantly improves the implantation success rate while reducing patient discomfort. This technology solves the technical problems of high implant failure rates in existing dental implant techniques, such as significant bone damage, uniform mechanical distribution of the implant within the alveolar bone, and poor initial stability.

[0073] In one embodiment, the top surface of the tapered thread segment includes N sequentially connected sloped surfaces, where N ≥ 2. The first sloped surface connects to the tooth root, and the Nth sloped surface connects to the tooth crest. Along the direction extending from the apex to the coronal end, the width of the first sloped surface gradually increases. In this embodiment, the top surface can be composed of N sloped surfaces connected sequentially, with the first sloped surface connecting to the tooth root and the Nth sloped surface connecting to the tooth crest. Along the direction extending from the apex to the coronal end, the width of the first sloped surface gradually increases. The tapered thread segment of the bone implant compresses the cortical and cancellous bone. Simultaneously, during the insertion of the bone implant, the lower-level threads sequentially follow the trajectory of the upper-level threads, gradually increasing the compressive force. Because the proportion of the first sloped surface continuously increases, the bone compression area significantly increases. The desired mechanical effect can be achieved with less bone compression per unit area, thus achieving the initial stability requirements with less bone compression.

[0074] Specifically, when N=2, the top surface 262 of the tapered thread segment includes a first slope surface 2621 and a second slope surface 2622. The first slope surface 2621 connects to the root of the tooth 269, and the second slope surface 2622 connects to the crest of the tooth 268. Along the direction extending from the tip 160 side to the crown 110 side, the width of the first slope surface 2621 gradually increases.

[0075] In this embodiment, the top side surface 262 is composed of two sloped surfaces connected sequentially. The first sloped surface 2621 connects to the root of the thread 269, and the second sloped surface 2622 connects to the crest of the thread 268. In this embodiment, the angle between the first sloped surface 2621 and the mirror line of the gradient thread can be set to 35°, and the angle between the second sloped surface 2622 and the mirror line of the gradient thread can be set to 15°. That is, the first sloped surface 2621 and the second sloped surface 2622 have an angle at their intersection. The size of this angle can be limited according to the angle between the first sloped surface 2621, the second sloped surface 2622 and the mirror line of the gradient thread. In some examples, the angles between the first sloped surface 2621, the second sloped surface 2622 and the mirror line of the gradient thread can also be set according to actual conditions. This application does not provide examples of all such examples.

[0076] Extending from the apex 160 to the coronal end 110, the first slope surface 2621 gradually increases in proportion to the width of the apex side 262. The gradually tapering section of the bone implant compresses the cortical and cancellous bone. Simultaneously, during implant insertion, lower threads follow the trajectory of higher threads, gradually increasing the compressive force. Because the proportion of the first slope surface 2621 continuously increases, the bone compression area significantly increases. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability requirements with less bone compression.

[0077] Specifically, when N=3, the top surface 262 of the tapered thread segment includes a third slope surface, a fourth slope surface, and a fifth slope surface. The third slope surface connects to the root of the tooth 269, the fifth slope surface connects to the crest of the tooth 268, and the fourth slope surface is located between the third and fifth slope surfaces. Along the direction extending from the tip 160 to the crown 110, the width of the third slope surface gradually increases.

[0078] In this embodiment, the top side 262 is composed of three sloped surfaces, with the fourth sloped surface located between the third and fifth sloped surfaces. The angle between the third sloped surface and the mirror image line of the gradient thread can be set to 15°, the angle between the fourth sloped surface and the mirror image line of the gradient thread can be set to 35°, and the angle between the fifth sloped surface and the mirror image line of the gradient thread can be set to 15°. The third, fourth, and fifth sloped surfaces also have angles between themselves. In one example, the intersections of the third, fourth, and fifth sloped surfaces can be rounded.

[0079] Extending from the apex 160° to the coronal 110°, the third slope surface gradually increases in width relative to the apex 262°. The gradually tapering thread of the bone implant compresses the cortical and cancellous bone. Simultaneously, during implant insertion, lower threads follow the trajectory of higher threads, gradually increasing the compressive force. Because the proportion of the fourth slope surface continuously increases, the bone compression area significantly increases. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability requirements with less bone compression.

[0080] In one embodiment, the width proportions of both the fourth and fifth slope surfaces gradually decrease along the direction extending from the apex 160 to the coronal end 110. During the screwing-in of the bone implant, the lower-level threads advance sequentially along the trajectory of the upper-level threads, gradually increasing the compressive force. Because the increased width proportion of the fourth slope surface facilitates bone attachment and results in a larger force-bearing area, the desired mechanical effect can be achieved with less bone compression per unit area. Therefore, initial stability requirements can be met with less bone compression.

[0081] When N=4, the top surface 262 of the tapered thread segment includes a sixth, seventh, eighth, and ninth slope surface connected in sequence. The sixth slope surface connects to the root 269, and the ninth slope surface connects to the crest 268. The width of the seventh slope surface gradually increases in the direction extending from the tip 160 to the crown 110.

[0082] Specifically, in this embodiment, the top side surface 262 is composed of four sloped surfaces, which are connected sequentially. The sixth sloped surface connects to the root 269, and the ninth sloped surface connects to the crest 268. That is, the sixth sloped surface connects to the root 269, the two ends of the seventh sloped surface connect to the sixth sloped surface and the eighth sloped surface respectively, the other end of the eighth sloped surface connects to the ninth sloped surface, and the ninth sloped surface connects to the crest 268. In this embodiment, the angle between the sixth sloped surface and the mirror line of the gradient thread can be set to 15°, the angle between the seventh sloped surface and the mirror line of the gradient thread can be set to 35°, the angle between the eighth sloped surface and the mirror line of the gradient thread can be set to 15°, and the angle between the ninth sloped surface and the mirror line of the gradient thread can be set to 35°.

[0083] Extending from the apex 160° to the coronal 110°, the sixth slope surface gradually increases in width as a percentage of the apex 262°, while the width percentages of the remaining slope surfaces gradually decrease. The gradually tapering sections of the bone implant compress the cortical and cancellous bone. Simultaneously, during implant insertion, lower threads sequentially follow the trajectory of higher threads, gradually increasing the compressive force. Because the proportion of the seventh slope surface continuously increases, the bone compression area of ​​the seventh slope surface significantly increases. This allows for achieving the desired mechanical effect with less bone compression per unit area, thus achieving initial stability requirements with less bone compression.

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

[0085] In one embodiment, the bone implant further includes a core 140, the tapered threads of which extend radially outward along the core 140, wherein the core matches an implantation socket with an inner diameter larger than the outer diameter of the core.

[0086] In this embodiment, the implant socket is used to accommodate the bone implant. Typically, an implant socket is created at the implantation site before implantation to facilitate implantation. The inner diameter of the implant socket is usually set according to the dimensions of the core 140, ensuring a good connection with the threads. The core 140 of the bone implant is the carrier of a tapered thread segment, whose tapered threads extend radially outward along the core 140. The tapered threads extend helically along the length of the tapered thread segment, and the width of the tapered threads narrows radially outward, making the tapered threads widest at their contact point with the core 140 and narrowest on the lateral surface 263. The diameter of the core 140 of the tapered thread segment is defined by the outer diameter of the core 140, and the outer diameter of the tapered thread segment is defined by the lateral surface 263 of the thread.

[0087] Since both the top side 262 and the crown side 261 of the tapered thread will compress 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 requirements can be achieved with less bone compression. This reduces damage to bone cells and blood vessels and improves the speed of bone integration after implantation.

[0088] There is a certain gap between the implantation socket and the core 140. When the bone implant is screwed into the implantation socket, the bone fragments produced will be discharged into this gap. These bone fragments have a similar function 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 diameter of the core of the bone implant, meaning the gap between the implant socket and the core 140 is set to 0.1 mm. This allows bone fragments to fully fill the gap and maintains good connection stability with the implant and the implant socket. It should be noted that the inner diameter of the implant socket matches the outer contour of the core, and the gap remains consistent throughout.

[0090] In one embodiment, the pitch 170 of the tapered thread remains constant along the axial direction, preferably from 0.6 mm to 2.4 mm. The distance between the root of the tapered thread and the driven surface is preferably 0.5 mm.

[0091] like Figure 2 As shown, along the direction extending from the crown end 110 to the top end 160, the gradually tapered thread segment is formed by a cylindrical section 210 and a tapered section 220 arranged sequentially. Figure 2 A cross-sectional view of a preferred embodiment of this application is shown in the figure; Figure 2 The dashed lines in the cylindrical section 210 and the tapered section 220 show the shape of the implant blank before the threads are machined, and clearly show the outer contour shape formed by the lateral surface 263 of the threads.

[0092] The tapered thread profile consists of a crown lateral surface 261, a top lateral surface 262, a lateral surface 263, a thread root width 264, and a thread height 265. The thread height 265 is defined by the outer diameter of the profile formed by the lateral surface 263 and the diameter of the core 140. The crown lateral surface 261 and the top lateral surface 262 extend radially outward from the core 140 and gradually narrow, resulting in the widest thread root width 264 and the narrowest lateral surface 263. Simultaneously, the thread spirals along its axis L from the tip 160 to the crown tip 110 with this profile shape, thus forming the tapered thread segment of the dental implant. The thread pitch 170 is a fixed value, preferably 0.6 mm to 2.4 mm. Furthermore, in each implant, the tapered thread can also be a double-ended thread.

[0093] In this embodiment, the depth of the threaded groove in the cylindrical section 210 remains unchanged, meaning there is no taper in the upper part of the implant. This significantly improves the self-tapping ability of the implant, thereby increasing initial stability. During the process of screwing the implant into the implantation socket, the tapered section 220, along the direction from the tip 160 to the crown 110, gradually compresses the bone tissue with its threads. Therefore, the applied force is smaller, the friction between the implant and the bone tissue is less, and the heat generation is also less, reducing the pain for the recipient and making installation easier.

[0094] See Figure 2 Along the direction extending from the crown end 110 to the top end 160, the core 140 includes a second conical core section 250, a cylindrical core section 240, and a first conical core section 230 arranged sequentially.

[0095] In this embodiment, the core 140 is divided into three sub-parts. The first conical core section 230 facilitates implant placement. Because the tip 160 of the threaded structure is first screwed into the implant socket in the recipient's oral cavity, the radial dimension of the tapered thread at the tip 160 is the smallest. This allows it to act as a positioning guide within the confined space of the recipient's oral cavity, ensuring the implant is aligned with the implant socket without applying force. The cylindrical core section 240 provides radial support to the bone tissue, improving initial stability. The second conical core section 250 causes the diameter of the core 140 to gradually increase from the tip 160 to the coronal tip 110, effectively compressing the cartilage radially, thereby further improving initial stability.

[0096] See Figure 2 The angle between the generatrix of the conical section 220 and the central longitudinal axis is set as α3, and the angle between the generatrix of the first conical core section 230 and the central longitudinal axis is set as α1, where 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 threading. The blank shape includes a cylindrical section 210 and a tapered section 220, wherein the generatrix of the tapered section 220 has a cone angle of α3 relative to the central longitudinal axis L. The core 140 has the following shape: a first tapered core section 230, a cylindrical core section 240, and a second tapered core section 250, wherein the generatrix of the first tapered core section 230 has a cone angle of α1 relative to the central longitudinal axis L, and the generatrix of the second tapered core section 250 has a cone angle of α2 relative to the central longitudinal axis L.

[0098] In one embodiment, the angle α3 between the generatrix of the tapered segment 220 and the central longitudinal axis is always less than 15°, and the cone angle α1 between the generatrix of the first tapered core segment 230 and the central longitudinal axis L, and the cone angle α2 between the generatrix of the second tapered core segment 250 and the central longitudinal axis L, are always less than 20°. This is beneficial for improving the self-tapping ability of the implant. Because the cone angle design with α2 always less than 20° provides stronger initial stability, the small cone angle can more evenly distribute pressure during implant placement. It enhances the implant insertion force, making it suitable for scenarios requiring strong surgical guidance. It also improves the implant's bone penetration performance during screwing. The cone angle design with α3 always less than 15° provides stronger initial stability, because the small cone angle can more evenly distribute pressure during implant placement. It enhances the implant insertion force, making it suitable for scenarios requiring strong surgical guidance. It also improves the implant's bone penetration performance during screwing.

[0099] The conical segment 220 and the first conical core segment 230 are of equal length, and α1 is greater than α3. This causes the thread height 265 of this segment to gradually increase from the coronal end 110 to the apex 160. Having a thread with a large thread height of 265 at the apex 160 is advantageous, as it improves the implant's self-tapping ability and initial stability. Furthermore, the cylindrical segment 210 has no conical angle on its outer contour, which increases initial stability because, when the implant is screwed into a hole (implant socket) of a given diameter, numerous thread peaks can cut into the hole wall. Simultaneously, the gradual threading allows for axial compression of the cartilage within the hole wall, which helps compress the cartilage radially, thus increasing initial stability. Simultaneously, the presence of the second conical core segment 250 causes the core diameter 140 of this segment to gradually increase along the coronal end 110, which creates radial compression of the cartilage, further enhancing initial stability.

[0100] In the embodiment, the outer contours of the cylindrical core section 240 and the outer contours of the cylindrical section 210 are arranged parallel to the straight line formed by the intersection of the same sectional surface, so that the thread height 265 of the cylindrical core section 240 is a fixed value, preferably 0.3mm.

[0101] The width of the threaded lateral surface 263 can be controlled by combining the outer diameter of the core 140, the threaded lateral surface 263, and the pitch 170. In the illustrated embodiment, the width of the threaded lateral surface 263 within the first tapered core section 230 and the cylindrical core section 240 is no less than 0.05 mm and no more than 0.5 mm. This is because a width that is too narrow will cause thread breakage or deformation at the thread tip 160, while a width that is too wide will result in loss of thread cutting function and excessive insertion torque. Therefore, a width of 0.2 mm for the lateral surface 263 is preferred to improve the self-tapping ability of the implant and keep the insertion torque within an acceptable level.

[0102] In one embodiment, the included angle β between the coronal side 261 and the apical side 262 of the thread in the tapered thread section 130 gradually increases from 0° to 90° along the coronal direction. Therefore, compared to the thread near the coronal end 110, the thread base width 264 near the apical end 160 is smaller, making it sharper and improving self-tapping ability. Simultaneously, during implant insertion, the thread base width 264 at the cartilage widens, creating axial compression with the cartilage, which improves initial stability. Preferably, the included angle β gradually increases from 35° to 50° along the coronal end 110 direction. Since the size of the included angle β determines the size of the thread base width 264, if the thread base width 264 is too small during implant insertion, the thread is prone to deformation and damage. Conversely, if the thread base width 264 is too large, it will increase the implant insertion torque and generate excessive heat through friction, also causing excessive compression of the cartilage, both of which can damage bone cells and blood vessels within 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 at this location gradually increases from the crown end 110 to the top end 160, which can improve the self-tapping ability and initial stability of the implant.

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

[0105] The diameters of the two conical core segments 140 that make up the core 140 gradually decrease along the direction from the crown end 110 to the apex 160. In a given implantation socket, the characteristics of the gradually tapering threads can achieve axial compression of the bone tissue, and combined with the radial compression of the bone tissue by the threads, this increases initial stability. The diameter of the second conical core segment 250 is larger than that of the first conical core segment 230 to ensure that the core 140 has a conical profile.

[0106] In the embodiment, the cylindrical core section 240 of the core 140 and the cylindrical section 210 of the tapered thread section are arranged in parallel so that the thread height 265 of the cylindrical core section 240 is a fixed value. During the process of the implant being screwed into the implantation socket, the extrusion force of the lower thread of the cylindrical core section 240 on the upper thread is small, so the friction is small and the heat generation is small, which can reduce the pain of the recipient.

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

[0108] See Figure 1 , 4 Or 5, at least one cutting groove 150 is provided on the tapered thread section, the at least one cutting groove 150 extending spirally from the crown end 110 to the top end 160.

[0109] In this embodiment, the cutting groove 150 is machined on a tapered thread. At least one cutting groove 150 is provided to spirally transport the bone tissue cut from the thread, avoiding increased cutting resistance caused by bone tissue accumulation, thereby reducing friction, minimizing heat generation, alleviating patient discomfort, and improving the initial stability of the implant.

[0110] Preferably, the thread may have two cutting grooves 150, and most preferably three cutting grooves 150. The cutting grooves 150 extend spirally from the top to the coronal portion, allowing the spiral cutting grooves 150 to cut cartilage and transport bone fragments spirally upwards during implantation. The end of the cutting groove 150, i.e., the cutting groove tail 152, extends 0 to 1 mm above the conical section 220. Because the top of the implant is generally a self-tapping section, the cutting grooves 150 extending above the conical section 220 can continuously perform bone tissue cutting functions throughout the entire length of the implant thread. In addition, the cutting grooves 150 can effectively guide the bone fragments generated during cutting out of the conical section 220. The cutting grooves 150 extending from the top to above the conical section 220 can effectively discharge bone fragments into the straight section of the implant. This accelerates bone healing. If the extension distance is too long, bone fragments may not be fully discharged into the 0.1 mm gap of the straight section. Therefore, in this preferred embodiment, the cutting grooves 150 extend from the top to 0 to 1 mm above the conical section 220.

[0111] See Figure 3 At least one cutting groove 150 forms at least one cutting surface on the tapered thread section, and the at least one cutting surface is perpendicular to the tangential direction of the tapered thread direction.

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

[0113] This embodiment can significantly improve the cutting ability of the cutting edge 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 implants provided in this application can be roughened using any known surface roughening method, with sandblasting and acid etching being preferred.

[0115] The dental implants provided in this application can be made from any known material suitable for implant preparation, with titanium, zirconium, tantalum, titanium alloys, or zirconium oxide being preferred.

[0116] The dental implants provided in this application can be bone-level implants or tissue-level implants.

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

[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 between 0.05 mm and 0.5 mm. The thread height of the tapered thread in the cylindrical core section is 0.3 mm.

[0119] A tapered thread with a thread height of 265mm in the range of 0.1mm-0.2mm can reduce neck bone resorption. A tapered thread with a thread height of 265mm in the range of 0.25mm-0.35mm can provide primary initial stability. A tapered thread with a thread height of 265mm in the range of 0.35mm-0.5mm can enhance self-tapping capability.

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

[0121] In addition, a bone implant is provided, including a non-gradient threaded segment and a graded threaded segment as described above, wherein the non-gradient threaded segment and the graded threaded segment are connected together.

[0122] In this embodiment, the thread structure of the non-gradient thread segment refers to the thread other than the pitch of the aforementioned gradient thread. The thread of the non-gradient thread segment does not have a gradual change trend; that is, the pitch of the non-gradient thread segment can be constant, such as a standard thread. Taking dental implants as an example, non-gradient threads are used in combination with gradient threads. The non-gradient thread segment is usually located at or near the coronal end of the dental implant. During the process of the dental implant being screwed into the bone tissue, the non-gradient thread advances along the trajectory of the gradient thread. Due to the different thread structure, the outer surface of the non-gradient thread will misalign and compress the bone tissue, increasing the friction between the thread and the bone tissue, thus forming a stable connection between the implant and the bone tissue and improving initial stability.

[0123] Specifically, in this embodiment, a standard thread is a thread whose tooth profile, diameter, and pitch all conform to relevant standards, and is a conventional thread. Standard threads can be equidistant threads with the same pitch, employing mature technology, facilitating processing, and effectively controlling manufacturing costs. See also... Figure 1 The non-gradient thread section and the graded thread section are located on the same core, while the graded thread section 130 is located on the core. The graded thread section of a dental implant includes the graded thread section 130 and the standard thread section 120. (See also...) Figure 2 The tapered thread section 130, where the included angle β between the threaded crown side 261 and top side 262 varies along its axial direction, is a standard thread section 120, where the included angle β between the threaded crown side 261 and top side 262 remains constant along its axial direction. The outermost end of the crown tip 110 is the crown bevel 111, below which is the neck section 112, which is continuously connected to the standard thread section 120. Furthermore, multiple tapered thread sections 130 or multiple standard thread sections 120 can be provided in the threads of each implant. In a preferred embodiment of this application, all implant threads use tapered thread sections 130.

[0124] In this embodiment, the dental implant can be configured with a combination of tapered and non-tapered thread sections to improve its applicability. The non-tapered section can adapt to the oral environment of different recipients, flexibly adapting the thread structure to different alveolar bone structures, shapes, and textures, thus meeting biocompatibility requirements and broadening its applicability.

[0125] It should be noted that the above embodiments are also applicable to other orthopedic implant fields, which will not be described in detail in this application.

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

[0127] In this implementation, the dental implant assembly is a modular design, including the dental implant, abutment, and connecting screws. The abutment is fixed within the dental implant. The abutment connects to the connecting screws and provides a mounting base for the screws. It should be noted that the connecting screws can be fixed to the abutment and can be used to fix the denture; in some embodiments, the connecting screws can also be part of the denture. The dental implant provides good initial 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 different recipient gingival tissues and improve biocompatibility. The connecting screws can also be selected based on the actual oral environment of different recipients. This design ensures both the initial and long-term stability of the dental implant assembly and provides an optimal solution for different recipients, adapting to biocompatibility requirements.

[0128] In other embodiments, the implant assembly may also include two basic parts: an implant portion and an abutment portion. The implant portion is the dental implant described above, and the abutment portion is the abutment described above. The implant portion is primarily used to embed into the bone and integrate with the bone tissue, thereby providing a firm anchorage for the abutment. The abutment can be fixed to the implant portion by bonding, threading, or inlaying. In the latter case, the implant portion and the abutment effectively form a single component, and future advancements may allow the abutment and implant portion to be integrally formed, for example, through 3D printing, powder injection molding, and compression molding. Furthermore, the abutment extends outward from the implant portion to support the connecting screw, so that at least a portion of the abutment is accommodated within the connecting screw.

[0129] Modern implants are typically constructed as two or more parts. In this case, the implant consists of at least an implantation component and a separate abutment. The implantation component is often referred to as the implant itself, while the separate abutment is sometimes called a separator. Here, the implantation component can be completely embedded in the bone, that is, embedded at the height of the alveolar ridge, or 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 abutments can be adapted to individual requirements. In particular, the appropriate abutment shape and angle can be selected after the implant components are inserted. This provides surgeons with greater flexibility and less room for error. Another advantage of multi-piece implants is that the abutments and implant portions can be made of different materials, thus offering more options for meeting biocompatibility requirements.

[0131] In this embodiment, the implantation part is the same as the dental implant described above, and its specific structural settings are as described above and will not be repeated here. The abutment part can be an existing abutment, as long as it matches the implantation part and ensures its implantation stability; this application does not impose any specific limitations.

[0132] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this application and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of this application.

Claims

1. A bone implant, characterized in that, include: A tapered thread segment having tapered threads that extend from the apex side to the coronal side along the central longitudinal axis of the bone implant; The tapered thread includes: 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 a radially outer surface of the tapered thread, the tapered thread extending helically along the direction of the central longitudinal axis; The top side surface includes at least two sloped surfaces extending from the top side to the coronal side. The width of one of the sloped surfaces gradually increases, and the slope of this sloped surface is smaller than that of the other sloped surfaces. The slope refers to the angle formed between the surface of the sloped surface and the central longitudinal axis of the bone implant.

2. The bone implant according to claim 1, characterized in that, In the direction extending from the top side to the crown side, the width ratio of one of the at least two slope surfaces to the top side surface is set as m, where the value of m ranges from 0% to m to 100%.

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

4. The bone implant according to any one of claims 1-3, characterized in that, The top side of the gradually tapered thread segment includes N sequentially connected slope surfaces, wherein the first slope surface connects to the root of the tooth, the Nth slope surface connects to the crest of the tooth, and the width of the first slope surface gradually increases along the direction extending from the top side to the crown side.

5. The bone implant according to claim 1, characterized in that, It also includes a core, wherein the tapered thread of the tapered thread section extends radially outward along the core, wherein the core matches the planting groove, and the inner diameter of the planting groove is larger than the outer diameter of the core.

6. The bone implant according to claim 5, characterized in that, Along the direction extending from the crown end to the apex, the tapered thread segment is formed by a series of sequentially arranged cylindrical and conical segments.

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

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

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

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

11. The bone implant according to claim 6, characterized in that, The tapered thread is provided with at least one cutting groove, which extends spirally from the top end to the crown end.

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 gradient thread, and the at least one cutting surface is perpendicular to the tangential direction of the spiral direction of the gradient thread.

13. The bone implant according to claim 6, characterized in that, The pitch of the gradient 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 to 0 to 1 mm above the tapered section.

16. The bone implant according to claim 8, characterized in that, α1 < 20°, and α3 < 15°.

17. The bone implant according to claim 7, characterized in that, The width of the lateral surface is set 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. The bone implant according to claim 1, characterized in that, It also includes a non-gradient thread section, which is connected to the threaded section of the gradient thread section.

20. A dental implant assembly, characterized in that, The device includes a base, a connecting screw, and a bone implant as described in any one of claims 1-19, wherein the base is placed within the bone implant and the connecting screw is fixed to the base.

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