Bone implant and dental implant assembly

Abstract

A bone implant and a dental implant assembly. The bone implant comprises a tapered thread structure, wherein the tapered thread structure extends from a coronal end (110) to an apical end (160) along the central longitudinal axis of the implant; the tapered thread structure comprises a core portion (140) and a tapered thread extending radially outwards along the core portion (140); the tapered thread comprises an apical flank (262), a coronal flank (261), and a lateral surface (263) connecting the apical flank (262) and the coronal flank (261); the lateral surface (263) defines a radially outer surface of the thread; the thread helically extends in the direction of the central longitudinal axis; and on at least one section of the range of the central longitudinal axis, an included angle formed by the apical flank (262) and the coronal flank (261) gradually increases in a direction from the apical end (160) to the coronal end (110). The bone implant facilitates bone attachment, has a large load-bearing area, achieves an expected mechanical effect by means of small bone compression per unit area, reduces damage to bone cells and blood vessels, improves primary stability after implantation of the implant and accelerates osseointegration, and is suitable for immediate implantation.

Description

Bone implants and dental implant components Technical Field

[0001] This application relates to the field of bone implant technology, and more particularly to a bone implant 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] Existing implant thread designs have replaced traditional parallel-wall (cylindrical) implants with implants that taper at the tip 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 and a dental implant assembly. The implant employs a tapered thread structure to progressively compress bone tissue axially within the implant socket. Combined with radial compression of the bone tissue by the threads, this further enhances the initial stability of the implant. Since both the top and crown sides of the tapered thread compress the cartilage, and the height of the thread can be increased to control the compression area, the bone compression area is significantly increased, facilitating bone attachment. The larger force-bearing area allows for achieving the desired mechanical effect with less bone compression per unit area. Therefore, initial stability requirements can be met with less bone compression, reducing damage to bone cells and blood vessels, and 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 gradually tapered thread structure extending from the coronal end to the apex along a central longitudinal axis; the gradually tapered thread structure comprising a core and a gradually tapered thread extending radially outward along the core, the gradually tapered thread comprising a top side surface, a coronal side surface, and a lateral surface connecting the top side surface and the coronal side surface, the lateral surface defining a radially outer surface of the gradually tapered thread, the gradually tapered thread extending helically along the direction of the central longitudinal axis; wherein, in at least one segment within the range of the central longitudinal axis, the included angle formed by the top side surface and the coronal side surface gradually increases in the direction extending from the apex to the coronal end.

[0008] This implementation utilizes a gradient thread structure to enhance the initial stability of the implant. During insertion, the angle of the thread gradually increases from the tip to the coronal end, creating compression between the cortical and cancellous bone. Simultaneously, lower threads advance along the grooves of higher threads. Because both the top and coronal sides of the gradient 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, accelerates bone integration after implantation, and significantly improves implant success rates while minimizing patient discomfort.

[0009] In conjunction with the aforementioned bone implant, the gradually tapered thread structure is formed by sequentially arranged cylindrical and conical segments along the direction extending from the coronal end to the apex.

[0010] In this implementation, the depth of the threaded groove in the cylindrical section 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 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, reduced pain for the recipient, and easier installation.

[0011] In conjunction with the aforementioned bone implant, the core portion, extending from the coronal end to the apex, includes a second conical core segment, a cylindrical core segment, and a first conical core segment arranged sequentially.

[0012] 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.

[0013] 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.

[0014] 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.

[0015] 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.

[0016] 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.

[0017] Combined with the aforementioned bone implant, the length of the conical segment is equal to that of the first conical core segment.

[0018] 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.

[0019] In conjunction with the above-mentioned bone implant, the tapered thread structure is provided with at least one cutting groove, which extends spirally from the coronal end to the apex.

[0020] 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.

[0021] In conjunction with the aforementioned bone implant, at least one cutting groove forms at least one cutting surface on the gradient thread structure, and the at least one cutting surface is perpendicular to the tangential direction of the gradient thread helix.

[0022] 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.

[0023] In conjunction with the aforementioned bone implant, the pitch of the tapered thread is 0.6-2.4 mm.

[0024] In conjunction with the aforementioned bone implant, the angle formed by the top side and the coronal side gradually increases within the range of 0° to 90° along the direction extending from the top to the coronal end.

[0025] 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.

[0026] In conjunction with the aforementioned bone implant, the cutting groove extends from the top end to 0 to 1 mm above the tapered section.

[0027] In combination with the above-mentioned bone implants, α1 < 20° and α3 < 15°.

[0028] In conjunction with the aforementioned bone implant, the width of the lateral surface is set between 0.05 mm and 0.5 mm.

[0029] In conjunction with the aforementioned bone implant, the thread height of the tapered thread in the cylindrical core section is 0.3 mm.

[0030] Secondly, a bone implant is provided, including a non-gradient thread structure and a gradient thread structure as described above, wherein the non-gradient thread structure is provided with a standard thread, and the standard thread and the gradient thread are connected together.

[0031] 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.

[0032] 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.

[0033] 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.

[0034] Compared with existing technologies, the bone implant and dental implant assembly provided in this application offer the following advantages: The implant employs a gradually tapering thread structure to progressively compress the bone tissue within the implant socket along the axial direction. Combined with the radial compression of the bone tissue by the threads, this further enhances the initial stability of the implant. Since both the top and crown sides of the tapering thread compress the cartilage, and the height of the control thread can be increased to control the compression area, the bone compression area is significantly increased, facilitating bone attachment. The larger force-bearing area 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 in existing technologies, such as significant bone damage during implantation, a singular mechanical distribution of the implant within the implant socket, poor initial stability, and a high implantation failure rate.

[0035] Other features and advantages of this application will be described in detail in the following detailed embodiments section. Attached Figure Description

[0036] The accompanying drawings used in the description of the embodiments or prior art are briefly introduced below.

[0037] Figure 1 is a schematic diagram of a gradient thread structure provided in an embodiment of this application;

[0038] Figure 2 is a cross-sectional and partial structural schematic diagram of a dental implant provided in an embodiment of this application;

[0039] Figure 3 is a bottom view of a dental implant according to an embodiment of this application;

[0040] Figure 4 is a structural schematic diagram of a dental implant provided in an embodiment of this application;

[0041] Figure 5 is a schematic diagram of stress distribution when a dental implant fuses with bone tissue according to an embodiment of this application;

[0042] Figure 6 is a schematic diagram of a dental implant installation method according to an embodiment of this application;

[0043] Figure 7 is a schematic cross-sectional view of a dental implant installation process provided in an embodiment of this application.

[0044] Reference numerals: 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; 210, Cylindrical section; 220, Tapered section; 230, First tapered core section; 240, Cylindrical core section; 250, Second tapered core section; 260, Thread profile; 261, Crown side surface; 262, Top side surface; 263, Lateral surface; 264, Thread root width; 265, Thread height. Detailed Implementation

[0045] The technical solutions in the embodiments of this application will now be described with reference to the accompanying drawings.

[0046] 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.

[0047] 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.

[0048] In the description of this specification, specific features, structures, materials, or characteristics may be combined in any suitable manner in one or more embodiments.

[0049] 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.

[0050] 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.

[0051] 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.

[0052] 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.

[0053] To facilitate understanding of this application, the following embodiments use dental implants applied in the field of dental implantology as examples.

[0054] As shown in Figures 1-5, the bone implant may include: a gradually tapered thread structure extending from the coronal end 110 to the apex 160 along its own central longitudinal axis; the gradually tapered thread structure includes a core 140 and a gradually tapered thread extending radially outward along the core 140, the gradually tapered thread including a top side 262, a coronal side 261, and a lateral surface 263 connecting the top side 262 and the coronal side 261, the lateral surface 263 defining a radially outer surface of the gradually tapered thread, the gradually tapered thread extending helically along the direction of the central longitudinal axis; wherein, in at least one segment of the central longitudinal axis range, the included angle formed by the top side 262 and the coronal side 261 gradually increases in the direction extending from the apex 160 to the coronal end 110.

[0055] In this embodiment, the bone implant is a dental implant, which is divided into 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.

[0056] Specifically, in this embodiment, the dental implant includes a tapered thread structure extending from the crown end 110 to the tip 160 along its own central longitudinal axis. The tapered thread structure includes a core 140 and threads extending radially outward from the core 140. As shown in Figure 2, the thread includes a top face 262, a crown face 261, and a lateral surface 263 connecting the top face 262 and the crown face 261. The lateral surface 263 defines the outermost radial surface of the thread. The thread extends along the length of the tapered thread structure in a helical manner, and the thread width narrows in the radially outward direction, such that the thread is widest at its contact core 140 and narrowest at the lateral surface 263. The diameter of the core 140 of the tapered thread structure is defined by the outer diameter of the core 140, and the outer diameter of the tapered thread structure is defined by the lateral surface 263 of the thread. A tapered thread is provided in the central axial range of at least one section of the tapered thread structure. The included angle between the top face 262 and the crown face 261 of the tapered thread gradually increases in the direction from the tip 160 to the crown end 110, such that the included angle between the top face 262 and the crown face 261 is smallest near the tip 160 and largest near the crown end 110. The cone angle formed between the top surface 262 and the coronal surface 261 of the threaded tip 160 is less than 30°, which helps improve the self-tapping ability of the implant tip 160. Simultaneously, because the included angle between the top surface 262 and the coronal surface 261 of the tapered thread gradually increases from the tip 160 to the coronal end 110, the thread width at the core 140 widens while the width of the tip 160 remains constant, ranging from 0.05 mm to 0.45 mm, preferably 0.2 mm. Therefore, during implant insertion, the top surface 262 and the coronal surface 261 gradually compress against the cartilage, thus achieving good initial stability.

[0057] In one embodiment, the included angle formed between the top side 262 and the crown side 261 of the tapered thread can gradually increase at a constant angle along the direction extending from the top end 160 to the crown end 110. This arrangement facilitates manufacturing and is more suitable for mass production.

[0058] Of course, the angle formed between the top side 262 and the crown side 261 of the tapered thread, extending from the top 160 to the crown 110, can also gradually increase at a non-constant angle. This setting can be used for personalized design to create tapered implants that match the patient's bone condition. For example, if the recipient's bone is loose at the top of the implant, a larger tapered angle change is needed to provide sufficient stability, while the bone becomes denser closer to the crown, the tapered angle change needs to be smaller closer to the crown.

[0059] 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.

[0060] It should be noted that, in this embodiment, the angle gradient between the top surface 262 and the coronal surface 261 of the gradient thread, extending from the top 160 to the coronal end 110, can also be achieved by setting different angle increments in different sections. That is, the gradient thread structure can include either gradient thread sections with a constant angle gradually increasing or gradient thread sections with a non-constant angle gradually increasing. The angle increments for different sections can be determined based on the patient's actual bone density. Gradient thread sections with a constant angle gradually increasing and gradient thread sections with a non-constant angle gradually increasing can be freely combined. 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.

[0061] In one embodiment, the included angle between the top surface 262 and the crown surface 261 of the tapered thread gradually increases along the direction extending from the tip 160 to the crown end 110. This gradual increase in the included angle can be achieved by gradually increasing the included angle between the crown surface 261 and the top surface 262, with the top surface 262 as a reference, or by gradually increasing the included angle between the top surface 262 and the crown surface 261, with the crown surface 261 as a reference. That is, during the process of gradually increasing the angle, either the top surface 262 or the crown surface 261 forming the included angle can remain unchanged as a base, and the gradual change in angle can be achieved by changing the included angle between the other surface and the top surface 262. Of course, in another embodiment, this gradual change in angle can also be achieved by simultaneously changing the tilt angle of the top surface 262 or the crown surface 261, and increasing the included angle between the top surface 262 or the crown surface 261.

[0062] It is understandable that there is an angle between the top lateral surface 262 or the crown lateral surface 261 and the plane containing the central axis of the dental implant. When the angle between the crown lateral surface 261 and the top lateral surface 262 is gradually increased, with the top lateral surface 262 as a reference, the angle between the top lateral surface 262 and the plane containing the central axis of the dental implant remains unchanged. The angle is gradually increased by changing the angle between the crown lateral surface 261 and the plane containing the central axis of the dental implant. Similarly, when the angle between the top lateral surface 262 and the crown lateral surface 261 is gradually increased, with the crown lateral surface 261 as a reference, the angle between the crown lateral surface 261 and the plane containing the central axis of the dental implant remains unchanged. The angle is gradually increased by changing the angle between the top lateral surface 262 and the plane containing the central axis of the dental implant. Similarly, when this angle is gradually changed by simultaneously varying the inclination angle of the top surface 262 or the crown surface 261, and increasing the angle between the top surface 262 or the crown surface 261, the angle between the top surface 262, the crown surface 261 and the plane containing the central axis of the dental implant is changed, and the angle between the top surface 262 or the crown surface 261 is increased.

[0063] In this embodiment, different angle gradients as described above can be set for different sections of the dental implant to adapt to different implantation environments and meet the requirements of biocompatibility and initial implantation stability.

[0064] 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.

[0065] Compared to existing technologies, the wider base width between the threads means a significantly larger thread area. This allows for better heat dispersion when the implant is screwed in with the same torque, resulting in much less pain for the recipient. Furthermore, the significantly increased compression area between the threads and cartilage allows for achieving the desired stability with less bone compression per unit area, reducing damage to bone cells and intraosseous blood vessels. This also improves the speed of implant integration with bone after placement. Simultaneously, the wider thread width at the 140mm core significantly enhances the strength of the threads in the cortical bone, increasing the contact area between the threads and cartilage and further dispersing force, thus improving the axial compressive force the implant can withstand.

[0066] This embodiment utilizes a gradient thread structure to improve the initial stability of the implant. During insertion, the thread angle gradually increases from the tip (160°) to the crown (110°), causing compression of the cortical and cancellous bone. Simultaneously, lower threads sequentially compress the grooves of higher threads, gradually increasing pressure. Since both the top surface (262) and crown surface (261) of the gradient 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 implant integration after placement, and significantly improves the success rate while reducing patient discomfort. This addresses the technical problems of existing implant techniques, such as significant bone damage, a single mechanical distribution of the implant within the alveolar bone, poor initial stability, and high implant failure rates.

[0067] In other embodiments, the aforementioned beneficial effects can also be achieved through a gradual change in the width of the lateral surface 263 or through a gradual change in the width of the tooth root (thread root width 264). This is because a gradual change in the angle between the crown lateral surface 261 and the top lateral surface 262 usually means a gradual change in the thread root, and similarly, a gradual change in the lateral surface 263. Therefore, a gradual thread can be achieved not only through a gradual change in the angle between the crown lateral surface 261 and the top lateral surface 262, but also through a gradual change in the width of the lateral surface 263 or the width of the tooth root. Both rely on the lateral surface of the tooth to compress bone tissue, forming a compressive force along the longitudinal axis of the implant's center to fix the implant, unlike existing radial compression. Generally, the lateral surface area of ​​a dental implant is much larger than the tooth top area or core surface area; therefore, a gradually changing lateral surface provides better compression, stronger stability, and better mechanical distribution. The embodiments of this application can also achieve implant stability by combining axial and radial compressive forces, significantly improving the initial stability and implantation success rate of the dental implant.

[0068] As shown in Figure 2, the tapered thread structure is formed by sequentially arranged cylindrical sections 210 and tapered sections 220 along the direction extending from the crown end 110 to the top end 160. The figure shows a cross-sectional view of a preferred embodiment of this application; the dashed lines in the cylindrical section 210 and tapered section 220 show the shape of the implant blank before the thread is processed, and clearly show the outer contour shape formed by the lateral surface 263 of the thread.

[0069] 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, forming the tapered thread structure 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.

[0070] 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.

[0071] Referring to 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.

[0072] 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.

[0073] Referring to 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.

[0074] 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.

[0075] 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.

[0076] 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 140 diameter of this segment to gradually increase along the coronal end 110, which creates radial compression of the cartilage, further enhancing initial stability.

[0077] 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.

[0078] 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 breakage or deformation of 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.

[0079] 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.

[0080] 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.

[0081] 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.

[0082] 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, combined with radial compression of the bone tissue by the threads, thereby increasing 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.

[0083] In the embodiment, the cylindrical core section 240 of the core 140 is arranged parallel to the cylindrical section 210 of the gradient thread structure, 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, the heat generation is small, and the pain of the recipient can be reduced.

[0084] In this embodiment, the tapered section 220 of the gradient thread structure 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.

[0085] Referring to Figures 1, 4 or 5, the tapered thread structure is provided with at least one cutting groove 150, which extends in a spiral manner from the crown end 110 to the top end 160.

[0086] 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.

[0087] 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 extension of the cutting grooves 150 to the conical section 220 allows them to continuously perform bone 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, and the extension of the cutting grooves 150 from the top to the conical section 220 can effectively guide the bone fragments into the straight section of the implant. The diameter of the implant socket is 0.1 mm larger than the core diameter of the dental implant. When the dental implant is screwed into the implant socket, the bone fragments produced will be discharged into this 0.1 mm gap. These bone fragments have a similar effect to bone powder, thereby accelerating the bone healing speed. If the extension distance is too long, the bone fragments will not be able to be fully discharged into the 0.1 mm gap of the straight section. Therefore, in this preferred embodiment, the cutting groove 150 extends from the top to 0 to 1 mm above the tapered section 220.

[0088] Referring to Figure 3, at least one cutting groove 150 forms at least one cutting surface on the tapered thread structure, and the at least one cutting surface is perpendicular to the tangential direction of the tapered thread helix.

[0089] 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.

[0090] 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.

[0091] The dental implants provided in this application can be roughened using any known surface roughening method, with sandblasting and acid etching being preferred.

[0092] 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.

[0093] The dental implants provided in this application can be bone-level implants or tissue-level implants.

[0094] The gradient thread structure 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 gradient thread extends helically along its central longitudinal axis L.

[0095] 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.

[0096] 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 stability in the implantation direction.

[0097] 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.

[0098] In addition, a bone implant is provided, including a non-gradient thread structure and a gradient thread structure as described above, wherein the non-gradient thread structure is provided with a standard thread, and the standard thread is connected to the gradient thread.

[0099] A standard thread is a thread whose tooth profile, diameter, and pitch all conform to relevant standards and is considered a conventional thread. In this embodiment, the standard thread can be an equidistant thread with the same pitch, employing mature technology, facilitating processing, and effectively controlling manufacturing costs. Referring to Figure 1, the non-gradient thread structure includes a core and a gradient thread section 130. The non-gradient thread structure and the gradient thread structure are located on the same core, and the gradient thread section 130 is located on the core. The gradient thread structure of the dental implant includes the gradient thread section 130 and the standard thread section 120. Referring again to Figure 2, in the gradient thread section 130, the included angle β between the crown facet 261 and the top facet 262 varies along its axial direction. In the standard thread section 120, the included angle β between the crown facet 261 and the top facet 262 remains constant along its axial direction. The outermost end of the coronal end 110 is the coronal bevel 111, below which is the neck section 112, which is continuously connected to the standard thread section 120. Furthermore, each implant thread may include multiple tapered thread sections 130 or multiple standard thread sections 120. In a preferred embodiment of this application, all implant threads use tapered thread sections 130.

[0100] In this embodiment, the dental implant can be configured with a combination of gradient thread structures and non-gradient thread structures to improve the applicability of the dental implant. The non-gradient section can adapt to the oral environment of different recipients. For different alveolar bone structures, shapes, and textures, the thread structure can be flexibly adapted to meet biocompatibility requirements and broaden its applicability.

[0101] It should be noted that the above embodiments are also applicable to the field of orthopedic implants, and will not be described in detail here.

[0102] This application also provides a method for installing a bone implant, applied to the bone implant described above, as shown in Figure 6, comprising the following steps:

[0103] Step S601: Use a non-gradient thread tapping drill to prepare an implantation groove, the shape of which matches the outer contour of the bone implant.

[0104] Step S602: Install a bone implant in the implantation socket, wherein the outer diameter of the bone implant is larger than the inner diameter of the implantation socket.

[0105] As shown in Figure 7, in this embodiment, the implantation socket is first prepared, and tapping is performed using a tapping drill that matches the outer contour of the implant. The thread inside the implantation socket is a non-gradient thread, i.e., a standard thread. The outer diameter of the implant is slightly larger than the inner diameter of the implantation socket. Preferably, the top diameter of the implant is 0.1 mm larger than the bottom diameter of the implantation socket.

[0106] In one embodiment, the diameter of the implant socket is 0.1 mm larger than the core diameter of the bone implant. When the bone implant is screwed into the implant socket, the resulting bone fragments are discharged into this 0.1 mm gap. These bone fragments have a similar effect to bone powder, thereby accelerating bone healing. When an implant with a tapered thread is screwed into the implant socket, the tapered thread, whose tooth base gradually widens along its axial direction, gradually compresses the standard thread groove with a constant tooth base width, forming an axial compressive force in the direction along the implant axis, thereby achieving good initial stability.

[0107] During the insertion of the implant into the implant socket, the threads gradually compress the bone tissue, resulting in less force, less friction between the implant and the bone, and less heat generation. This reduces patient discomfort and facilitates installation. Because the tip of the threaded structure is screwed into the implant socket first, the radial dimension of the tapered thread at the tip is the smallest, serving as a positioning guide. This allows the implant to be aligned with the socket without applying force, and this embodiment further facilitates implant installation.

[0108] 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.

[0109] 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.

[0110] 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.

[0111] 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.

[0112] 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.

[0113] 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.

[0114] 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 gradient thread structure, which extends from the coronal end to the apex along the central longitudinal axis of the implant; The gradient thread structure includes: a core and a gradient thread extending radially outward along the core, the gradient thread including 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 gradient thread, the gradient thread extending helically along the direction of the central longitudinal axis. Wherein, in at least one segment of the central longitudinal axis range, the angle formed by the top side surface and the coronal side surface gradually increases along the direction extending from the top to the coronal end.

2. The bone implant according to claim 1, characterized in that, Along the direction extending from the crown end to the apex, the gradient thread structure is formed by sequentially arranged cylindrical sections and conical sections.

3. The bone implant according to claim 2, characterized in that, Along the direction extending from the crown end to the apex, the core includes a second conical core section, a cylindrical core section, and a first conical core section arranged sequentially.

4. The bone implant according to claim 3, 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.

5. The bone implant according to claim 3, 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.

6. The bone implant according to claim 5, characterized in that, The length of the conical section is equal to that of the first conical core section.

7. The bone implant according to claim 2, characterized in that, The tapered thread structure is provided with at least one cutting groove, which extends spirally from the crown end to the top end.

8. The bone implant according to claim 7, characterized in that, The at least one cutting groove forms at least one cutting surface on the gradient thread structure, and the at least one cutting surface is perpendicular to the tangential direction of the gradient thread rotation.

9. The bone implant according to claim 2, characterized in that, The pitch of the gradient thread is 0.6-2.4 mm.

10. The bone implant according to claim 2, characterized in that, Along the direction extending from the apex to the coronal end, the angle formed by the apical side and the coronal side gradually increases within the range of 0° to 90°.

11. The bone implant according to claim 3, characterized in that, The width of the lateral surface of the tapered thread on the cylindrical core section is 0.2 mm.

12. The bone implant according to claim 8, characterized in that, The cutting groove extends from the top to 0 to 1 mm above the tapered section.

13. The bone implant according to claim 4, characterized in that, α1 < 20°, and α3 < 15°.

14. The bone implant according to claim 2, characterized in that, The width of the lateral surface is set between 0.05 mm and 0.5 mm.

15. The bone implant according to claim 5, characterized in that, The thread height of the tapered thread in the cylindrical core section is 0.3 mm.

16. A bone implant, characterized in that, It includes a non-gradient thread structure and a gradient thread structure as described in any one of claims 1-15, wherein the non-gradient thread structure is provided with a standard thread, and the standard thread is connected to the gradient thread.

17. 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 1-16, wherein the base is placed within the bone implant and the connecting screw is fixed to the base.

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