Nanostructure of laser surface-treated bone materials

Abstract

The present invention provides a nanostructure of a laser surface-treated bone material. [Solution] The surface of the bone material is titanium metal 3, and molten titanium metal is formed by laser sputtering. After cooling, it has at least one microchannel 10 made of titanium dioxide (TiO2). The nanostructure of the bone material includes at least one micropore 12, at least one guide channel 16, at least one nanoprotrusion particle layer 111 formed by at least one nanowall 11, and at least one nanowall. The effects and purposes of improving bone healing and antibacterial indicators are achieved: A. accelerating the deposition of bone healing-related proteins; B. accelerating the attachment of bone cells; C. inducing neovascularization; D. accelerating early calcification and bone mineralization; E. improving the exchange of nutrients; F. stabilizing the surface bone structure; and G. inhibiting plaque formation.

Description

[Technical Field]

[0001] The present invention relates to nanostructures of bone materials, particularly bone materials that have been subjected to laser surface treatment. [Background technology]

[0002] In prior art bone materials, the surface metal of the bone material is treated with abrasive group (Grind, G) and sandblasting acid etching.

[0003] In the prior art, laser irradiation is used to treat the surface metal of bone materials to form only arrayed pits, and the prior art does not disclose the use of laser irradiation to form nanowalls, nor does it disclose a structure in which pits are arranged within a guide channel.

[0004] The prior art implant surface treatment method of patent number WO2016171638 only discloses the steps of forming pits using laser irradiation and applying a small diameter laser to the raised portion between two pits. Summary of the Invention [Means for solving the problem]

[0005] The nanostructure of the bone material subjected to the laser surface treatment of the present invention, the bone material includes a dental implant or a bone nail, the implant has a joint end and a threaded portion, the threaded portion has a threaded protrusion and a threaded recess, the bone nail has at least one screw, the surface of the bone material is titanium metal provided with a laser-processed layer made of titanium dioxide (TiO2) which is obtained by continuously ablating the surface of the titanium metal of the bone material with a laser and melting and cooling it, the laser-processed layer has at least one microchannel in the linear axial direction, the at least one microchannel is

[0006] At least one micropore provided on the bottom side of the at least one microchannel;

[0007] At least one nanowall disposed on a longitudinal side of the at least one microchannel, the nanowall including at least one nanoprojection particle layer and at least one wall bottom layer located on a surface of a lower end of the at least one nanowall;

[0008] at least one guiding channel disposed between adjacent ones of the at least one nanowall;

[0009] the guiding channels between adjacent ones of the at least one nanowall have a first width, and the thickness of the nanowalls between adjacent parallel ones of the at least one guiding channels has a pitch;

[0010] the first height of the at least one microchannel comprises a second height of the at least one nanowall and a third height of a depth of the micropore; and

[0011] A nanostructure of a laser surface-treated bone material, wherein the roughness of the at least one nanoprotrusion particle layer is greater than the roughness formed by the at least one wall bottom layer on the bottom side of the adjacent guide channel.

[0012] The method for laser surface treatment of bone material of the present invention includes the steps of: continuously irradiating the surface of the titanium metal of the bone material with a laser in a direction parallel to the axis of travel of the bone material with a fixed point, continuously ablating the surface of the titanium metal of the bone material with the laser, forming molten titanium metal by continuous ablation, forming titanium dioxide (TiO2) after cooling, and melt-sputtering the titanium metal to form at least one microchannel in the direction parallel to the axis of travel of the bone material; the bottom side of the at least one microchannel is at least one continuous micropore formed by continuously melt-sputtering the surface of the titanium metal with the laser, and the longitudinal side of the at least one microchannel is at least one nanowall of the at least one microchannel formed by continuously melt-sputtering the at least one micropore with the laser along the direction parallel to the axis of travel of the laser, and then melt-sputtering the surface of the titanium metal around the at least one micropore; and forming at least one guide channel of the at least one microchannel by melt sputtering between the at least one nanowall along a direction perpendicular to the direction of travel, the guide channel between adjacent nanowalls having a first width and a nanowall thickness between adjacent parallel guide channels having a pitch; irradiating a titanium metal surface of the bone material using the laser to form a first height of the at least one microchannel along a longitudinal axis direction perpendicular to the direction of travel of the laser irradiation, the first height including a second height of the at least one nanowall and a third height of a depth of the micropore; irradiating the titanium metal surface with the laser to form at least one nanoprojection particle layer of aggregate nanoprojection particles on a surface of an upper end of the at least one nanowall by melt sputtering on the surface of the titanium metal; irradiating the titanium metal surface with the laser to form at least one nanoprojection particle layer on a surface of a lower end of the at least one nanowall;and forming at least one bottom wall layer by melt sputtering on the surface of the titanium metal. The laser is used to irradiate the surface of the titanium metal by melt sputtering to form a roughness variation, the roughness of the at least one nanoprotrusion particle layer being greater than the roughness formed in the at least one bottom wall layer on the bottom side of the adjacent guide channel. The micropores are provided to activate cells into osteoblasts, and the osteoblasts form at least one attachment in a Z-shaped network and rapidly attach between the nanoprotrusion particle layers of the at least one adjacent nanowall of the at least one guide channel.

[0013] The laser surface-treated bone material structure of the present invention, wherein the first width of the guide channel between adjacent nanowalls is 20 μm to 50 μm, the thickness of the nanowalls between adjacent parallel guide channels has a pitch of 10 μm to 30 μm, the first height of at least one microchannel is 20 μm to 60 μm, the second height of the at least one nanowall is 10 μm to 30 μm, the third height of the depth of the micropore is 10 μm to 30 μm, the pitch of the thickness of the at least one nanowall is 10 μm to 30 μm, the diameter of the at least one micropore is 20 μm to 50 μm, and the spacing distance of the at least one micropore is 30 μm to 50 μm.

[0014] In the method of laser surface treatment of bone material of the present invention, the laser is switched in giant pulse generator (Q-Switch) mode to output short pulses as a solid-state laser, and micro-ablation is performed continuously in the direct axis direction under controlled power intensity.

[0015] In the method of the present invention for laser surface-treated bone material, during the activation process of osteoblasts that form at least one attachment, the protein secreted by the pre-osteoblasts is at least one selected from type I collagen alpha 1 chain (COL1A1), decorin (DCN), tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), and secreted phosphoprotein-1 (SPP1).

[0016] In the method of laser surface-treated bone material of the present invention, the structure of the at least one microchannel inhibits bacterial growth inside the at least one microchannel.

[0017] In the method for laser surface-treated bone material of the present invention, the titanium metal is titanium or a titanium alloy, and the microchannel crystals have a rutile crystal structure.

[0018] In the method of laser surface treatment of bone material of the present invention, the bone material is a tooth implant or a bone nail.

[0019] In the method for laser surface-treated bone material of the present invention, the bone material is placed horizontally, and blood is dropped onto the threaded portion of the bone material, resulting in a contact angle of 0 to 12 degrees.

[0020] In the method of the present invention for laser surface treatment of bone material, the time required for the blood contact angle to decrease to 0 degrees is 20 seconds or less.

[0021] In the method of laser surface-treated bone material of the present invention, the guide channel between the at least one adjacent nanowall 11 forms a transport and exchange channel for nutrients, blood, serum, and bone mineralization, the micropores of the at least one microchannel form a microculture dish, and the at least one guide channel and the at least one micropore form a simulated biological environment of the at least one microchannel, promoting the formation of new blood vessels.

[0022] In the nanostructure of the bone material that has been subjected to the laser surface treatment of the present invention, the surface of the bone material is titanium metal, and the laser is continuously irradiated at a fixed point on the titanium metal surface of the bone material, causing continuous ablation to form molten titanium metal, which forms titanium dioxide (TiO2) after cooling, and at least one microchannel is formed in the direction of the perpendicular axis by melting and sputtering the titanium metal. The at least one microchannel has at least one continuous micropore formed on the bottom side of the at least one microchannel by continuous melt sputtering with the laser below the surface of the titanium metal along the laser's direct axis traveling direction, and at least one nanowall of the at least one microchannel formed on the longitudinal axis side thereof by continuous melt sputtering with the laser along the laser's direct axis traveling direction, and then melt sputtering on the surface of the titanium metal around the at least one micropore, and at least one nanowall of the at least one microchannel has at least one nanowall layer of aggregate nanoprojection particles formed on the surface of the upper end of the at least one nanowall by melt sputtering on the surface of the titanium metal. and at least one nanowall on the surface of the lower end of the at least one nanowall, forming at least one bottom wall layer by melt sputtering titanium metal on the surface; and at least one guide channel of the at least one microchannel provided between adjacent at least one nanowall, formed by melt sputtering between adjacent at least one nanowall along a direction perpendicular to the linear axis of laser irradiation, wherein the guide channel between adjacent at least one nanowall has a first width, the thickness of the nanowall between adjacent parallel at least one guide channel has a pitch, and the first height of the at least one microchannel includes a second height of the at least one nanowall and a third height that is the depth of the micropore.The laser is used to irradiate the surface of the titanium metal and melt sputter it to form a roughness variation, the roughness of the at least one nanoprotrusion particle layer being greater than the roughness formed in the at least one wall bottom layer on the bottom side of the adjacent guide channel, the micropores are provided to activate cells into osteoblasts, and the osteoblasts form at least one Z-shaped mesh of attachments and rapidly attach between the nanoprotrusion particle layers of the at least one adjacent nanowall of the at least one guide channel.

[0023] The nanostructure of the laser surface-treated bone material of the present invention, wherein the first width of the guide channel between adjacent nanowalls is 20 μm to 50 μm, the thickness of the nanowalls between adjacent parallel guide channels has a pitch of 10 μm to 30 μm, the first height of at least one microchannel is 20 μm to 60 μm, the second height of the at least one nanowall is 10 μm to 30 μm, the third height of the depth of the micropore is 10 μm to 30 μm, the pitch of the thickness of the at least one nanowall is 10 μm to 30 μm, the diameter of the at least one micropore is 20 μm to 50 μm, and the spacing distance of the at least one micropore is 30 μm to 50 μm.

[0024] In the nanostructure of bone material subjected to the laser surface treatment of this invention, the laser is switched in giant pulse generator (Q-Switch) mode to output short pulses as a solid-state laser, and micro-ablation is performed continuously in the direct axis direction under controlled power intensity.

[0025] In the nanostructure of the laser surface-treated bone material of the present invention, during the activation process of osteoblasts that form this at least one attachment, the protein secretion product of the pre-osteoblast is at least one selected from type I collagen alpha 1 chain (COL1A1), decorin (DCN), tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), and secreted phosphoprotein-1 (SPP1).

[0026] In the nanostructure of the laser surface-treated bone material of the present invention, the structure of the at least one microchannel inhibits the growth of bacteria inside the at least one microchannel.

[0027] In the nanostructure of the laser surface-treated bone material of the present invention, the titanium metal is titanium or a titanium alloy, and the microchannel crystals have a rutile crystal structure.

[0028] In the nanostructure of the laser surface treated bone material of the present invention, the bone material is a tooth implant or a bone nail.

[0029] In the nanostructure of the bone material that has been subjected to the laser surface treatment of the present invention, the bone material is placed horizontally, and blood is dropped onto the threaded portion of the bone material; the resulting contact angle is 0 to 12 degrees.

[0030] In the nanostructure of the bone material subjected to the laser surface treatment of the present invention, the time required for the blood contact angle to decrease to 0 degrees is less than 20 seconds. [Effects of the Invention]

[0031] In the nanostructure of the laser surface-treated bone material of the present invention, the guide channel between the at least one adjacent nanowall 11 forms a transport and exchange channel for nutrients, blood, serum, and bone mineralization, the micropores of the at least one microchannel form a microculture dish, and the at least one guide channel and the at least one micropore form a simulated biological environment for the at least one microchannel, promoting the formation of new blood vessels.

[0032] The nanostructure of the laser-surface-treated bone material of the present invention and its nanostructure comprise a nanowall nanoprotrusion particle layer, a wall base layer, micropores, and guide channels located on the titanium surface, which enhance protein adhesion and cell attachment, provide more attachment sites for pre-osteoblast extension, and provide biofilm formation resistance, improving osseointegration, osteoblast proliferation and adhesion, and osteoblast differentiation. Furthermore, the deeper microchannels on the laser-surface-treated titanium surface of the present invention create more space, promoting sufficient nutrient replenishment for pre-osteoblasts and supporting the maturation process of pre-osteoblasts, including proliferation, osteoblast differentiation, and extracellular mineralization. Specifically, the present invention aims to improve the healing rate of the bone material and achieve the osseointegration effect of stable adhesion between the bone material and human tissue.

[0033] In the method of laser surface-treated bone material and its nanostructure of the present invention, micro-pores and micro-channels with nano-structures are constructed by the work module-laser process, and this structure can improve bone healing and antibacterial indicators by A. accelerating the deposition of bone healing-related proteins, B. accelerating the attachment of bone cells, C. inducing neovascularization, D. accelerating early calcification and bone mineralization, E. improving the exchange of nutrients, F. stabilizing the surface bone structure, and G. inhibiting plaque formation. [Brief explanation of the drawings]

[0034] [Figure 1]1 is a schematic diagram of the nanostructure of a bone material that has been subjected to laser surface treatment according to the present invention. [Figure 2] 1 is a schematic diagram of a bone material implant that has been subjected to laser surface treatment according to the present invention and the corresponding periodontal ligament. [Figure 3] 1 is a schematic diagram showing the angle between the laser irradiation and the outer shape of the implant in a bone material implant that has been laser surface treated according to the present invention. [Figure 4] 1 is a schematic diagram showing the use of a bone nail made of bone material with laser surface treatment of the present invention on the palmar navicular bone. [Figure 5] 2 is a schematic diagram of the blood contact angle and adsorption angle of a bone material implant that has been subjected to laser surface treatment of the present invention. [Figure 6] 1 is a schematic diagram showing a comparison of the nanostructure of a bone material subjected to the laser surface treatment of the present invention with the nanostructure of a bone material subjected to sandblasting acid etching. [Figure 7] 1 is a schematic diagram of a scanning electron microscope image showing a comparison of the nanostructure of the bone material subjected to the laser surface treatment of the present invention with the nanostructure on a titanium plate subjected to polishing and sandblasting acid etching. [Figure 8] 1 is a schematic diagram showing a comparison of the nanostructure of a bone material subjected to the laser surface treatment of the present invention with the nanostructure of a bone material subjected to sandblasting acid etching. [Figure 9] 1 is a schematic diagram showing a comparison of serum adhesion of a bone material that has been subjected to the laser surface treatment of the present invention with that of a bone material that has been subjected to sandblasting and acid etching. [Figure 10] 1 is a schematic diagram showing a comparison of the cell counts of bone material subjected to the laser surface treatment of the present invention with the cell counts of bone material subjected to polishing and sandblasting acid etching. [Figure 11-1] 1 is a schematic diagram showing a comparison of the mRNA expression ratio of bone material subjected to the laser surface treatment of the present invention with the mRNA expression ratio of bone material subjected to polishing and sandblasting acid etching. [Figure 11-2]This is a schematic diagram showing the use of the laser surface-treated bone material of the present invention and purified cell protein lysate in Western blot assays using antibodies to (A) COL1A1, (B) DCN, (C) TNFRSF11B, (D) SPP1, and β-actin. [Figure 12] 1 is a schematic diagram showing a comparison of the concentrations of COL1A1, DCN, and TNFRSF11B in bone materials that have been subjected to the laser surface treatment of the present invention with those in bone materials that have been subjected to polishing and sandblast acid etching. [Figure 13] 1 is a schematic diagram showing a comparison of the mineralization of bone material subjected to the laser surface treatment of the present invention with that of bone material subjected to grinding and sandblasting acid etching. [Figure 14] 1 is a schematic diagram showing that the guide channel of the present invention has a sufficient first width W1 of 20 μm to 50 μm, compared to only 10 μm in the prior art implant, and bone cells grow better on the surface of the microchannel of the present invention. [Figure 15] FIG. 1 is a schematic diagram showing a comparison between the closely bonded implant-bone interface structure of the present invention and the separated implant-bone interface structure of the SLA group. [Figure 16] 1 shows a comparative schematic diagram of biofilm formation and amount, as well as a comparative schematic diagram of plaque content, on five surfaces: a nanostructured surface with microchannels according to the present invention, a laser-treated surface with lattice-like pits, a mechanically processed surface, a polished surface, and a sandblasted surface. DETAILED DESCRIPTION OF THE INVENTION

[0035] As shown in Figures 1, 6, 7 and 8, one embodiment of the present invention is a method for laser surface-treated bone material, in which at least one microchannel 10 includes at least one micropore 12, at least one nanowall 11, and at least one guide channel 16. The at least one nanowall 11 includes at least one nanoprotrusion particle layer 111 and at least one wall bottom layer 112. The step is to use a laser to continuously irradiate the surface of the titanium metal 3 of the bone material at a fixed point along the surface of the titanium metal 3 in the direction of linear axis travel, thereby continuously ablating the surface to form molten titanium metal, and melt-sputtering the titanium metal 3 to form at least one microchannel 10 in the direction of linear axis travel, the bottom side of the at least one microchannel 10 being at least one continuous micropore 12 formed by continuously melt-sputtering the underside of the surface of the titanium metal 3 with the laser, and the longitudinal side of the at least one microchannel 10 being at least one continuous micropore 12 formed by continuously melt-sputtering the at least one micropore 12 with the laser along the direction of linear axis travel, and then melt-sputtering the surface of the titanium metal 3 around the at least one micropore 12. at least one nanowall 11 of at least one microchannel 10; forming at least one guide channel 16 of the at least one microchannel 10 by melt sputtering between the at least one nanowall 11 along a direction perpendicular to the linear axis of laser irradiation, wherein the guide channel 16 between adjacent nanowalls 11 has a first width W1, and the thickness of the nanowalls 11 between adjacent parallel guide channels 16 has a pitch P1; irradiating the surface of the titanium metal 3 of the bone material using the laser to form a first height D1 of the at least one microchannel 10 along a longitudinal axis direction perpendicular to the linear axis of laser irradiation, wherein the first height D1 includes a second height D2 of the at least one nanowall 11 and a third height D3 of the depth of the micropore 12;The method includes irradiating the surface of the titanium metal 3 with the laser to form at least one nanoprotrusion particle layer 111 of bulk nanoprotrusion particles on the surface of the upper end of the at least one nanowall 11 by melting and sputtering the surface of the titanium metal 3, and forming at least one bottom wall layer 112 on the surface of the lower end of the at least one nanowall 11 by irradiating the surface of the titanium metal 3 with the laser to form melting and sputtering the surface of the titanium metal 3. The laser is used to irradiate the surface of the titanium metal 3 to form melting and sputtering to form a roughness variation, the roughness of the at least one nanoprotrusion particle layer 111 being greater than the roughness formed in the at least one bottom wall layer 112 on the bottom side of the adjacent guide channel 16. The micropores 12 are provided to activate cells into osteoblasts, and the osteoblasts form at least one Z-shaped meshwork attachment 15 and rapidly attach between the nanoprotrusion particle layers 111 of the at least one adjacent nanowall 11 of the at least one guide channel 16. The laser irradiation scanning direction is K. The boundary formed between the at least one nanoprotrusion particle layer 111 on the upper end surface of the at least one nanowall 11 and the at least one wall bottom layer 112 on the lower end surface of the at least one nanowall 11 is a cell adhesion region, thereby activating cells into osteoblasts. The laser is continuously irradiated at a fixed point on the surface of the titanium metal 3 of the bone material, causing continuous ablation to form molten metallic titanium. Titanium dioxide is formed after laser treatment and during cooling. On the other hand, during laser treatment and before cooling, it is not titanium dioxide but molten metallic titanium.

[0036] As shown in Figures 1, 6, 7, and 8, one embodiment of the present invention is a method and nanostructure for laser-surface-treated bone material. By forming an oxide layer of titanium dioxide on the surface of titanium metal 3, the adhesion and regeneration of blood and bone cells can be optimized. The nanostructure of the present invention is formed by laser irradiation. When irradiated by the laser, the irradiated area on the surface of titanium metal 3 is continuously melted, sputtered, and ablated, combining with oxygen atoms in the air to form an oxide layer of titanium dioxide, the thickness of which depends on the adjustment of the laser parameters. In this invention, X-ray photoelectron spectroscopy was used to measure the thickness of the oxide layer at the bottom of the micropores 12 at the bottom of the microchannel 10 to be approximately 45 nm, and the thickness of the oxide layer at the top of the nanowalls 11 at the top of the microchannel 10 to be approximately 110 nm. The oxide layer of the surface structure of the present invention is much thicker than that of other prior art surface structures.

[0037] As shown in Figures 1, 6, 7 and 8, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, wherein the first width W1 of the guide channel 16 between the at least one adjacent nanowall 11 is 20 μm to 50 μm, the thickness of the nanowall 11 between the parallel adjacent at least one guide channel 16 has a pitch P1 of 10 μm to 30 μm, and the first height D1 of the at least one microchannel 10 is: The second height D2 of the at least one nanowall 11 is 10 μm to 30 μm, the third height D3 of the depth of the micropore 12 is 10 μm to 30 μm, the pitch P1 of the thickness of the at least one nanowall 11 is 10 μm to 30 μm, the diameter of the at least one micropore 12 is 20 μm to 50 μm, and the spacing distance of the at least one micropore 12 is 30 μm to 50 μm.

[0038] As shown in Figures 1, 6, 7 and 8, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, in which the laser is switched in giant pulse generator (Q-Switch) mode to output short pulses as a solid-state laser, and perform continuous micro-ablation in the linear axis direction under controlled power intensity.

[0039] As shown in Figures 11-1 to 12, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, and during the activation process of osteoblasts that form at least one attachment 15, the protein secretion product of the pre-osteoblasts is at least one selected from type I collagen alpha 1 chain (COL1A1), decorin (DCN), tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), and secreted phosphoprotein-1 (SPP1).

[0040] As shown in FIG. 16, one embodiment of the present invention is a method and nanostructure of a laser surface-treated bone material, wherein the structure of the at least one microchannel 10 inhibits bacterial growth inside the at least one microchannel 10.

[0041] As shown in Figure 5, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure. The titanium metal 3 is titanium or a titanium alloy, and the crystals of the microchannel 10 have a rutile crystal structure. This bone material is a dental implant or a bone nail. The bone material is placed horizontally, and blood is dropped onto the threaded portion of the bone material. The resulting contact angle is 0 to 12 degrees. The time required for the blood contact angle to decrease to 0 degrees is 20 seconds or less.

[0042] As shown in Figures 1 to 9, one embodiment of the present invention is a method and nanostructure of a laser surface-treated bone material, in which the guide channel 16 between the at least one adjacent nanowall 11 forms a transport and exchange channel for nutrients, blood, serum, and bone mineralization, the micropores 12 of the at least one microchannel 10 form a microculture dish, and the at least one guide channel 16 and the at least one micropore 12 form a simulated biological environment of the at least one microchannel 10, promoting the formation of new blood vessels.

[0043] As shown in Figures 1 to 9, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, which improves the exchange of nutrients, and the microchannels 10 and the microchannels 10 provide an excellent surface area for the attachment of monolayer cells, and also provide good temperature control and opportunities for rapid exchange of liquid media, which are suitable for the growth and differentiation of osteoblasts and endothelial cells inside and outside the nanostructured microchannels 10.

[0044] As shown in Figures 1 to 9, one embodiment of the present invention is a nanostructure of a bone material that has been subjected to laser surface treatment. The surface of this bone material is titanium metal 3, and the laser is continuously irradiated at a fixed point on the surface of the titanium metal 3 of this bone material, causing continuous ablation to form molten titanium metal, and the titanium metal 3 is melted and sputtered to form at least one microchannel 10 in the linear traveling direction.The at least one microchannel 10 has at least one continuous micropore 12 formed on the bottom side of the at least one microchannel 10 by continuous melt sputtering with the laser below the surface of the titanium metal 3 along the laser's direct axis traveling direction, and at least one nanowall 11 of the at least one microchannel 10 formed on the longitudinal side of the at least one microchannel 10 by continuous melt sputtering with the laser along the laser's direct axis traveling direction, and then melt sputtering on the surface of the titanium metal 3 around the at least one micropore 12, wherein at least one nanowall 11 is formed on the surface of the upper end of the at least one nanowall 11 by melt sputtering on the surface of the titanium metal 3, and At least one nanowall 11 has at least one bottom wall layer 112 formed by melt sputtering titanium metal 3 on the surface of the lower end of at least one nanowall 11; and at least one guide channel 16 of the at least one microchannel 10 provided between adjacent nanowalls 11 and formed by melt sputtering the at least one adjacent nanowall 11 along a direction perpendicular to the linear axis of the laser irradiation, the guide channel 16 between the at least one adjacent nanowall 11 having a first width W1, the thickness of the nanowall 11 between adjacent parallel guide channels 16 having a pitch P1, and the first height D1 of the at least one microchannel 10 including a second height D2 of the at least one nanowall 11 and a third height D3 of the depth of the micropore 12. The laser is used to irradiate the surface of the titanium metal 3 and melt and sputter it to form a roughness variation, and the roughness of the at least one nanoprotrusion particle layer 111 is greater than the roughness formed in the at least one wall bottom layer 112 on the bottom side of the adjacent guide channel 16.The micropores 12 are provided to activate the cells into osteoblasts, which form at least one Z-shaped mesh-like attachment 15 and rapidly attach between the nanoprotrusion particle layers 111 of the at least one adjacent nanowall 11 of the at least one guiding channel 16.

[0045] As shown in Figure 2, one embodiment of the present invention is a method and nanostructure of a laser-surface-treated bone material. Between a tooth 52 and an alveolar bone 54, there is a periodontal ligament 53. The gum 52 has blood vessels 55, which provide nutrients and blood to the tooth 53 and alveolar bone 54. A dental implant 60 made of the laser-surface-treated bone material of the present invention has microchannels 10, which can mimic the function of the periodontal ligament 53. The structure of the microchannels 10 can improve bone healing and antibacterial properties, accelerate the deposition of bone healing-related proteins, accelerate bone cell attachment, induce neovascularization, accelerate early calcification and bone mineralization, improve nutrient exchange, stabilize the surface bone structure, and inhibit plaque formation. The microchannels 10 on the laser-treated surface of the present invention allow nutrients and blood to be supplied to the alveolar bone via the blood vessels, accelerating bone healing with the alveolar bone.

[0046] 3 , one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, in which an implant 60 has a joint end 62 and a threaded portion 61 having a threaded protrusion 611 and a threaded recess 612. If the surface layer 613 of the threaded portion is parallel to the laser irradiation scanning direction K, the laser irradiation cannot scan and melt or sputter the surface layer 613. Therefore, the surface layer 613 of the threaded protrusion 611 and the threaded recess 612 may be trapezoidal, and by forming a non-parallel cross angle between the surface layer 613 and the laser irradiation scanning direction K, the laser irradiation can effectively melt and sputter the surface layer 613, forming a specific structure of effective microchannels 10, including a nanoprotrusion particle layer 111 of the nanowalls 11, a wall bottom layer 112 of the nanowalls 11, micropores 12, and guide channels 16 located on the surface of the titanium metal 3.

[0047] As shown in Figure 4, one embodiment of the present invention is a method and nanostructure of a laser surface-treated bone material. For a finger 71 and a navicular bone 72 in the palm of the hand, after a fracture due to a sports injury, the fracture crack 721 of the navicular bone 72 folds to divide the navicular bone 72 into an anterior end 722 and a posterior end 723. The anterior end 722 has blood vessels 73 supplying bone marrow 724, while the posterior end 723 does not have blood vessels 73 supplying bone marrow 724, making it prone to necrosis and making it difficult for the fracture to heal. The bone nail 74 with the laser surface treatment of the present invention has a specific structure of effective microchannels 10, including the nanoprotrusion particle layer 111 of the nanowall 11, the wall bottom layer 112, the micropores 12, and the guide channels 16 located on the titanium surface of the bone nail 74. This structure can improve bone healing and antibacterial index, accelerate the deposition of bone healing-related proteins, accelerate the attachment of bone cells, induce neovascularization, accelerate early calcification and bone mineralization, improve the exchange of nutrients, stabilize the surface bone structure, and inhibit plaque formation. Therefore, since the rear end 723 has microchannels 10 that supply blood and nutrients to the bone marrow 724, the navicular bone 72 is less likely to necrosize and is more likely to accelerate fracture healing.

[0048] As shown in FIG. 5, one embodiment of the present invention is a method for laser-surface-treated bone material and its nanostructure. A blood test implant 60 is vertically positioned, with a fourth height D4 between the blood 8 and the horizontal line 81, resulting in a contact angle β of 0 to 15 degrees. When the implant 60 is vertically positioned, it takes less than 20 seconds for the contact angle α to drop to 0 degrees. This is because the laser-surface-treated implant 60 of the present invention forms a specific structure of effective microchannels 10 on the titanium surface of the implant 60, including the nanoprotrusion particle layer 111 of the nanowalls 11, the bottom wall layer 112 of the nanowalls 11, the micropores 12, and the guide channels 16. As a result, the contact angle β of the present invention is larger than that of typical implants in the grinding group (G) and the sandblasting acid etching group (SLA). The contact angle α of the present invention is smaller than that of conventional implants in the grinding group (G) and the sandblasting acid etching (SLA) group. Furthermore, microspheres flowing through the nanostructured surface of the present invention can flow at significantly higher velocities, sufficient to produce significant differences in cell adhesion and protein absorption. For the hydrophilic micropore / nanopore laser-treated structure, cell adhesion, proliferation, differentiation, and prostaglandin E2 levels on the present invention's structured surface are higher than those on the polished titanium metal 3 surface and the SLA-treated titanium metal 3 surface. The hydrophilic micropore / nanoporous titanium surface of the present invention can be produced by laser treatment, and the structured surface characteristics of the present invention enhance the adhesion, proliferation, and differentiation of MG-63 cells. Furthermore, scanning electron microscopy (SEM) showed that dental implants with the structured surface characteristics of the present invention have strong wear resistance and show only minor damage during repeated implantation and removal. These damages include peeling, pitting, and deformation. In contrast, the pitting, deformation, and melting areas on the surface of the SLA implants are more than those of the present invention. The defects of the prior art are particularly likely to be found in the distal threads corresponding to the self-tapping design.The surface of the present invention does not have obvious sharp irregularities at the microscopic level. This is why the surface of the present invention is less susceptible to changes and more durable. Therefore, the macro-roughness of the present invention is less likely to be damaged under high torque. In contrast, the surface of SLAs typically exhibits sharp irregularities, which will inevitably be deformed or damaged when subjected to compressive force. The surface of the present invention has excellent physical pressure resistance, and in clinical applications, the implant of the present invention can be removed and reinserted without harming the implant.

[0049] As shown in Figures 9-12, one embodiment of the present invention is a method for laser-surface-treated bone material and its nanostructure. This method accelerates the deposition of bone healing-related proteins. High laser energy is used to form a thick oxide layer (45-110 nm) on the surface of the titanium metal 3 structure of the present invention. The titanium dioxide oxide layer optimizes compatibility with blood and serum, provides an environment for fibrin adhesion, and is beneficial for the formation of a temporary matrix, which is important in the early stages of bone healing. As shown in Figure 9, serum viscosity testing of the present invention revealed that the laser-surface-treated implant 60 of the present invention formed a specific structure of effective microchannels 10, including the nanoprotrusion particle layer 111 of the nanowall 11, the wall base layer 112, the micropores 12, and the guide channels 16 located on the titanium surface of the implant 60. This resulted in a serum viscosity higher than that of the conventional implants in the grinding group (G) and the sandblasting acid etching group (SLA).

[0050] As shown in FIG. 1 , one embodiment of the present invention is a method for laser-surface-treated bone material and its nanostructure. The first height D1, second height D2, and third height D3 of the microchannel 10 on the laser-treated surface must not be too shallow for irradiation melt sputtering. This is because a guide channel 16 without sufficient depth would be difficult to provide nutrients, blood, and serum. The first width W1 of the microchannel 10 must not be too wide. This is because it would be difficult for deposits 15 to adhere, such as protein secretions from pre-osteoblasts, between the at least one nanowall 11 formed in the upper layer of the guide channel 16 and to adhere to form a Z-shaped network. The first width W1 of the microchannel 10 must not be too narrow. This is because the amount of deposits 15 would be low. The microchannel 10 must be melt sputtered by the nanowalls 11 of the special nanoprotrusion particle layer 111. This is because the reticulated cells or preosteoblasts of the attachment material 15 in the upper layer of the guide channel 16 have difficulty adhering to the nanoprotrusion particle layer 111, making it difficult for the preosteoblasts to express and secrete secreted proteins. The microchannel 10 has a third height D3 of multiple deep micropores 12 formed by melt sputtering, which simulates growth in a biological environment and has the effect of simulating a microculture dish. The microchannel of the present invention generates the above-mentioned optimal structure by scanning the same position vertically and scanning along the horizontal direction, using laser frequency, energy intensity, pulse (frequency), and specific unit area / unit time / unit pulse / unit energy.

[0051] As shown in Figures 7 and 10, one embodiment of the present invention is a method for laser surface-treated bone-like materials and their nanostructures. Scanning electron microscope images of titanium plates with three surface treatments, namely, grinding group (G), sandblasting acid etching group (SLA), and laser irradiation group (L), are shown. As shown in Figure 10, pre-osteoblasts and human palatal mesenchymal cells were demonstrated to be able to differentiate into osteoblasts on titanium plates. In this invention, 2.3 x 10 5 Pre-osteoblasts (pre-osteoblasts) were cultured for three days on titanium plates with three treated surfaces: a grinding group (G), a sandblasting acid etching group (SLA), and a laser irradiation group (L). Based on the proliferation rate of pre-osteoblasts, the effects of the three modified titanium surfaces on pre-osteoblast growth were examined. The cell count in the laser irradiation group (L) was higher than that in the grinding group (G) and the sandblasting acid etching group (SLA). This invention accelerates bone cell attachment, and the structure of the microchannel 10 of this invention maximizes the surface area for monolayer cell attachment while also achieving good temperature control and rapid liquid medium exchange. The microchannel 10 of this invention functions as a bioreactor, creating a localized flow environment. In this environment, many cell types, such as osteoblasts (bone cells) and endothelial cells (blood vessel lining cells), have evolved to prefer exposure to sustained shear stress of 0.1 dynes / cm and only exhibit normal phenotypes in the environment of the microchannel 10 of the present invention.

[0052] As shown in Figure 11-1, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, which accelerates bone cell attachment. The titanium metal 3 surface with the laser microchannel 10 structure of the present invention has improved osseointegration ability compared to the surfaces of the SLA and G groups. The laser-treated titanium surface with the channel structure of the present invention enhances the pre-osteoblast maturation stage and osseointegration. According to the qPCR results of the present invention, pre-osteoblasts on the treated surface of the laser irradiation group (laser irradiation, L) showed significantly improved mRNA expression levels, protein expression / secretion ratios, and extracellular mineralization of COL1A1, DCN, TNFRSF11B, and SPP1. The Minimum Information for Publication of Quantitative Real-Time PCR Experiments (MIQE), abbreviated as qPCR, is used for quantitative real-time polymerase chain reaction (PCR). The treated titanium surface of the present invention up-regulates the expression of pre-osteoblast differentiation markers in osteoblasts as determined by qPCR assay. 2.3 x 10 5Pre-osteoblast cells were incubated for 72 hours on titanium plates with surfaces treated with grinding (G), sandblasting acid etching (SLA), or laser irradiation (L). Purified cellular mRNA was used in qPCR assays using primer sets for COL1A1, DCN, TNFRSF11B, and SPP1. Osteogenic differentiation markers include COL1A1, DCN, TNFRSF11B, and SPP1. Collagen type I alpha 1 (COL1A1) is the major component of type I collagen and is widely distributed in the interstitium of parenchymal organs and connective tissues throughout the body. Collagen plays an important role in tissue development and homeostasis. Decorin (DCN) is a protein encoded by the human DCN gene. Decorin (DCN) is a proteoglycan. It is a small pericellular matrix proteoglycan that is structurally closely related to biglycan protein. Decorin is the result of gene duplication. This protein is a component of connective tissue, binds to type I collagen fibrils, and plays a role in matrix assembly.Decorin (DCN) is named for its ability to "decorate" type I collagen and its interaction with the "d" and "e" bands of collagen fibrils. Decorin influences fibrillogenesis and functions as a myokine. In this role, it binds to myostatin to promote muscle hypertrophy. Tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), also known as osteoprotegerin (OPG) and osteoclastogenesis inhibitory factor (OCIF), is a member of the tumor necrosis factor receptor superfamily. Osteoprotegerin (OPG) was originally discovered as a novel secreted tumor necrosis factor receptor (TNFR)-associated protein that plays a role in regulating bone mineral density. Secreted phosphoprotein-1 (SPP1), also known as osteopontin (OPN), is a glycoprotein involved in bone formation. Secreted phosphoprotein-1 (SPP1) binds to the vitronectin (VTN) receptor and plays a role in anchoring osteoclasts to the bone remodeling matrix. Vitronectin (VTN) is a multifunctional glycoprotein with diverse physiological functions that is present in plasma and the extracellular matrix. Vitronectin (VTN) binds to integrin receptors primarily via the RGD sequence and is involved in cell adhesion, spreading, and migration.Vitronectin (VTN) is widely used for the maintenance and proliferation of pluripotent stem cells. Vitronectin (VTN) has many functions in the nervous system, including involvement in neuronal differentiation, neurotrophy, and neurogenesis, as well as in regulating axon size and supporting and guiding neurite outgrowth. Vitronectin (VTN) has also been shown to reduce blood-brain barrier permeability through its interaction with integrin receptors on vascular endothelial cells, thereby playing an important role in brain protection.

[0053] As shown in Figure 11-1, one embodiment of the present invention is a method and nanostructure of laser-surface-treated bone material, which accelerates bone cell attachment and causes pre-osteoblasts to express / secrete more COL1A1, DCN, TNFRSF11B, and SPP1 proteins. Furthermore, Western blot assay showed that the expression of osteoblast differentiation markers in pre-osteoblasts was upregulated on the treated titanium surface in the laser irradiation group (L).

[0054] As shown in Figure 11-2, one embodiment of the present invention is a method for laser surface treatment of bone material and its nanostructure, which has a surface roughness of 2.3 x 10 5 Preosteoblasts were incubated for 72 hours on titanium plates with the treated surfaces of groups G, SLA, and L. Purified cell protein lysates were used for Western blot assays with antibodies against (A) COL1A1, (B) DCN, (C) TNFRSF11B, (D) SPP1, and β-actin. Western blot assays showed that the expression levels of COL1A1, DCN, TNFRSF11B, and SPP1 were significantly increased in preosteoblasts on the treated surfaces of group L (laser irradiation).

[0055] As shown in Figure 12, one embodiment of the present invention is a method and nanostructure of laser-surface-treated bone material. During osteoblast activation, pre-osteoblasts secrete several proteins, including COL1A1, OCN, and TNFRSF11B. The amounts of COL1, OCN, and TNFRSF11B secreted by pre-osteoblasts on the treated surface of the laser irradiation group (L) were significantly higher. As shown in Figure 13, the treated titanium surface of the laser irradiation group (L) promoted the secretion of osteogenic differentiation markers in pre-osteoblasts. 2.3 x 10 5Preosteoblasts were incubated on titanium plates with treated surfaces (G, SLA, and L) for 72 hours. Cell culture medium was collected and used in multiplex assays to determine the concentrations of (A) COL1A1, (B) OCN, and (C) TNFRSF11B. Multiplex assay data showed significantly higher levels of COL1, OCN, and TNFRSF11B secreted by preosteoblasts on the treated surface of the laser irradiation group (L). Osteocalcin (OCN) is a non-collagenous protein secreted by osteoblasts (bone-generating cells) in bone tissue. It plays an important role in bone metabolism, primarily involved in bone mineralization and calcium binding. Osteocalcin (OCN) is also thought to be involved in the regulation of glucose metabolism and energy homeostasis. Studies have shown that osteocalcin (OCN) is associated with insulin secretion, glucose tolerance, and adipose tissue function. Osteocalcin (OCN), also known as gamma-carboxyglutamic acid-containing protein (BGLAP), is a small, non-collagenous protein hormone found in bone and dentin. It was first identified as a calcium-binding protein. Osteocalcin is secreted exclusively by osteoblasts and is thought to be involved in metabolic regulation. In its carboxylated form, it directly binds calcium and is concentrated in bone, while in its uncarboxylated form, it acts as a hormone in the body, transmitting signals to the pancreas, fat, muscle, testes, and brain. In the pancreas, osteocalcin acts on beta cells, encouraging them to release more insulin. In adipocytes, osteocalcin promotes the release of the hormone adiponectin, thereby improving insulin sensitivity. In muscle, osteocalcin acts on muscle cells, promoting energy availability and utilization, which is beneficial for athletic performance.In the testes, osteocalcin stimulates testosterone synthesis by acting on interstitial cells, thereby affecting male fertility. In the brain, osteocalcin plays an important role in development and functions, including spatial learning and memory. The acute stress response (ASR), commonly known as the fight-or-flight response, stimulates osteocalcin release from bone within minutes in mice, rats, and humans. In the presence of adrenal insufficiency, high levels of osteocalcin alone can induce the acute stress response (ASR). Clinically, osteocalcin can be used as a biomarker to assess bone metabolism and for the diagnosis and monitoring of bone diseases such as osteoporosis.

[0056] As shown in Figure 13, one embodiment of the present invention is a method for laser-surface-treated bone material and its nanostructure. This method accelerates early mineralization. When pre-osteoblasts (pre-osteoblasts) were seeded and cultured on a titanium plate, the laser irradiation group (L) showed an increased Alizarin red S stain rate on day 18, indicating that the laser irradiation group (L)-treated surface promoted enhanced calcium ion secretion. Energy dispersive X-ray spectroscopy was used to detect extracellular mineral precipitation at the top of the microchannel 10 near the nanostructure. When the surface structure of the present invention was immersed in a cell-free solution, there was no significant difference in calcium or potassium compound precipitation compared to the titanium metal 3-treated surface or the SLA-treated surface. However, when pre-osteoblasts were cultured on the titanium plate, the surface structure of the present invention showed an increased Alizarin red S stain rate on day 18, indicating that the surface structure of the present invention promoted enhanced calcium ion secretion. The surfaces of the present invention have a significantly greater bone cell mineralization capacity than SLA treated titanium surfaces.

[0057] As shown in Figure 13, one embodiment of the present invention is a method for laser surface-treated bone material and its nanostructure, which accelerates early mineralization, and the treated titanium surface of the laser irradiation group (L) promotes pre-osteoblast extracellular mineralization. (A) shows the results of 2.3 x 10 dendritic cells on the titanium plates with the treated surfaces of the G, SLA, and L groups. 5 (B) Images of preosteoblasts collected after 4 or 18 days of culture. The left column shows a 100 μm scale, and the right column shows a 50 μm scale. The reddish-brown calcium compounds indicate the mineralization ability of preosteoblasts. (C) Quantitative results are shown as OD540 levels. Scales of 100 μm and 50 μm are used for imaging the left and right columns, respectively.

[0058] As shown in Figure 14, one embodiment of the present invention is a method for laser surface-modifying bone material and its nanostructure. The cell morphology and cell adhesion of human fetal osteoblasts (HFOB) cultured on the implant are shown. The microchannels 10 of the present invention facilitate the growth of large numbers of filopodia of human fetal osteoblasts in the implant samples with their multi-channel and nanostructure. Laser-modified titanium implants may increase the chances of successful osseointegration. The guide channels 16 of the present invention have a sufficient first width W1 of 20 μm to 50 μm, compared to only 10 μm in prior art implants, which allows for better bone cell growth on the surface of the microchannels 10 of the present invention.

[0059] As shown in Figure 15, one embodiment of the present invention is a method and nanostructure of a laser-surface-treated bone material. This method can stabilize the surface bone structure, with initial bone formation beginning at the lower edge of the nanostructure at the upper edge of the microchannel 10. A cross-section of an implant of the present invention clinically harvested from the oral cavity of a car accident patient shows that the implant exhibits a tightly bonded interface. This is completely different from the clinically harvested implant-bone interface structure of the SLA group, where the bone separates from the implant surface. The bonding ability of the implant surface of the present invention to bone is significantly better than that of the SLA group. Furthermore, animal experiments showed that the implant surface of the present invention already exhibited good bone bonding ability within the first two months after implant implantation, while the SLA group's implant surface only began to bond after three months.

[0060] As shown in FIG. 16 , one embodiment of the present invention is a method for laser-surface-treated bone material and its nanostructure, which can inhibit plaque formation and bacterial growth inside at least one microchannel 10. The formation and amount of biofilms on five surfaces are compared: a nanostructured surface with the microchannel 10 of the present invention, a laser-treated surface with lattice-like pits, a machined surface, a polished surface, and a sandblasted surface. The nanostructured surface of the microchannel 10 of the present invention minimizes biofilm formation on the surface of the microchannel 10 of the present invention because the structure of the microchannel 10 affects the chemical composition of the surface. The microchannel 10 of the present invention has a pitch P1 between the guide channels 16 that prevents biofilms from crossing between the guide channels 16, thereby helping to reduce the occurrence of peri-implantitis. In the prior art laser-treated surface with lattice pits, there is no pitch P1 between the guide channels 16, so biofilms grow and cover different lattice pits, thereby not effectively suppressing bacterial growth inside the laser-treated surface with lattice pits.

[0061] Prior art surface modification methods pose a potential risk of introducing foreign materials to the implant surface during the manufacturing process, resulting in surface contamination and thus reducing safety and efficacy. In contrast, one embodiment of the present invention is a method for laser surface-treating bone materials and their nanostructures, which is a clean and economical method for ensuring product contamination without direct contact with the implant during surface preparation. In one embodiment of the present invention, the microchannel 10 structure formed from titanium metal 3 is formed by high-temperature laser irradiation to form a titanium oxide layer consisting of a single layer of titanium dioxide (TiO2), without any chemical residues. The nanoscale microchannel 10 structure of the present invention is at least predominantly crystalline, with the crystalline phase having a rutile crystal structure.

[0062] Compared with the SLA and G groups, the microchannels 10 on the laser-treated surface of the present invention have a nanoprotrusion particle layer 111 of the nanowalls 11, a wall base layer 112 of the nanowalls 11, micropores 12, and guide channels 16 located on the surface of the titanium metal 3. These nano / micropore surface structures are conducive to enhanced protein and cell adhesion, provide more attachment sites for pre-osteoblast extension, provide biofilm formation resistance, and promote osteoblast gene expression, such as the expression of the parathyroid hormone-related protein gene in osteoblasts, thereby improving osseointegration, osteoblast proliferation and adhesion, and osteoblast differentiation. The more complex nano-level structure around the microchannels 10 on the surface of the laser-treated titanium metal 3 provides more attachment sites for pre-osteoblast extension, which may promote osteoblast gene expression, such as the expression of the parathyroid hormone-related protein gene in osteoblasts. Furthermore, the deeper micro-channels 10 on the titanium surface treated with the laser surface of the present invention create more space, promote sufficient nutrient replenishment for pre-osteoblasts, and are beneficial to the maturation process of pre-osteoblasts, including proliferation, osteoblast differentiation, and extracellular mineralization.

[0063] The microchannels 10 on the laser-surface-treated titanium surface of the present invention are regulated by specific osteoblast differentiation markers, each of which regulates cellular responses. For example, COL1A1 is upregulated during osteoblast differentiation, and SPP1 is a maturation marker of extracellular matrix. DCN regulates collagen matrix assembly and mineralization and regulates the cell cycle, which is expressed during extracellular matrix mineralization. Osteoprotegerin, translated from the TNFRSF11B gene, is a suppressor of bone resorption. Physiological cell stretching affects the expression of insulin-like growth factors and mechano-growth factors. Mechanical stretching acts via the mechanosensor polycystin-1 in human osteoblasts, promoting Runx2 expression through the JAK2 / STAT3 pathway. JAK-STAT3 is an important signaling pathway involved in regulating cell growth, differentiation, and survival. The upregulation of COL1, SPP1, DCN, and TNFRSF11B in human embryonic palatal mesenchymal cells cultured in laser-generated microchannels 10 may be due to the effect of mechanical stretching. In the microchannels 10 on the titanium surface treated with the present invention, mesenchymal fibroblast-like cells and endothelial cells play important roles in angiogenesis during implantation, i.e., before osseointegration. After the stabilization period, the antibacterial ability of the processed implant may help eliminate the possibility of peri-implantitis. When used in bone materials, the microchannels 10 on the titanium surface treated with the present invention can improve angiogenesis and antibacterial ability. Furthermore, they enhance the proliferation of preosteoblasts, the expression / secretion of COL1, SPP1, DCN, and TNFRSF11B mRNA and protein, and promote extracellular mineralization.

[0064] The above description and explanation are merely explanations of the preferred embodiments of the present invention, and those skilled in the art may make other modifications based on the patent application scope defined below and the above description, but these modifications should be within the spirit and scope of the present invention. [Explanation of symbols]

[0065] 3. Titanium metal 10 microchannels 11 Nano Wall 111 Nanoprotrusion particle layer 112 Wall bottom layer 12 Micropore 15. Adhesion 16 Guidance Channel D1 First height D2 Second height D3 Third height D4 4th height P1 Pitch W1 1st width K Laser irradiation scanning direction 51 teeth 52 Gums 53 Periodontal ligament 54 Alveolar bone 55 Blood vessels 60 Implants 61 Threaded part 611 Screw convex part 612 Thread recess 613 Surface layer 62 Joint end 71 fingers 72 Scaphoid bone 721 Fracture Crack 722 Front end 723 Rear end 724 Bone marrow 73 Blood vessels 74 Bone nail 8 blood 81 Horizontal line α contact angle β adsorption angle SLA Sandblast Acid Etching Group G polishing group L laser irradiation group COL1A1 Type I collagen α1 chain DCN Decorin (Decorin, DCN), TNFRSF11B Tumor necrosis factor receptor superfamily member 11B SPP1 secreted phosphoprotein-1 β-actin Osteocalcin (OCN)

Claims

1. A nanostructure of a laser surface-treated bone material, comprising: The bone material includes a dental implant or a bone nail, the implant is provided with a joint end and a threaded portion, the threaded portion has a threaded protrusion and a threaded recess, the bone nail is provided with at least one screw, and the surface of the bone material is made of titanium dioxide (TiO ) which is melted and cooled by continuously ablating the surface of titanium metal of the bone material with a laser. ２ ) is a titanium metal provided with a laser-processed layer consisting of, the laser-processed layer is provided with at least one microchannel in the direction of linear axis travel, and the at least one microchannel is At least one micropore provided on the bottom side of the at least one microchannel; At least one nanowall provided on a longitudinal side of the at least one microchannel, the nanowall including at least one nanoprojection particle layer and at least one wall bottom layer located on a surface of a lower end of the at least one nanowall; at least one guiding channel disposed between adjacent ones of the at least one nanowall; the guiding channels between adjacent ones of the at least one nanowall have a first width, and the thickness of the nanowalls between adjacent parallel ones of the at least one guiding channels has a pitch; the first height of the at least one microchannel comprises a second height of the at least one nanowall and a third height of a depth of the micropore; and A nanostructure of a laser surface-treated bone material, wherein the roughness of the at least one nanoprotrusion particle layer is greater than the roughness formed by the at least one wall bottom layer on the bottom side of the adjacent guide channel.

2. 2. The nanostructure of claim 1, wherein the first width of the guide channel between adjacent nanowalls is 20 μm to 50 μm, the thickness of the nanowalls between adjacent parallel guide channels has a pitch of 10 μm to 30 μm, the first height of the at least one microchannel is 20 μm to 60 μm, the second height of the at least one nanowall is 10 μm to 30 μm, the third height of the depth of the micropore is 10 μm to 30 μm, the pitch of the thickness of the at least one nanowall is 10 μm to 30 μm, the diameter of the at least one micropore is 20 μm to 50 μm, and the spacing distance of the at least one micropore is 30 μm to 50 μm.

3. 2. The nanostructure of the laser surface-treated bone material according to claim 1, wherein the titanium metal is titanium or a titanium alloy, and the microchannel crystals have a rutile crystal structure.

Images