Nanotextured laser surface treated aggregate

Abstract

The utility model relates to a kind of nanostructure of laser surface treatment aggregate, wherein the surface of the aggregate is titanium metal, and at least one microchannel with titanium dioxide (TiO2) after cooling is formed by laser melting and sputtering to form molten titanium, at least one microchannel includes: at least one micropore, at least one guide channel, and at least one nano-wall formed at least one nano-bulge layer and at least one nano-wall. The following bone healing and antibacterial index effects and purposes are achieved: A. accelerate bone healing related protein deposition, B. accelerate bone cell attachment, C. induce neovascularization, D. accelerate early calcification and bone mineralization, E. improve nutrient exchange, F. stabilize surface bone structure, and G. resist plaque formation.

Description

Technical Field

[0001] This utility model relates to a bone material, and more particularly to a nanostructure of a laser-surface-treated bone material. Background Technology

[0002] Existing technologies use grinding (G) and sandblasting acid etching to treat the surface metal of the bone material.

[0003] Existing technologies use laser irradiation to form an array of pits on the surface of the metal material. Existing technologies do not disclose the formation of nanowalls by laser irradiation, nor do they disclose the structure of pits arranged in the guide channels.

[0004] The existing technology patent number WO2016171638 discloses a surface treatment method for implants, which only discloses the steps of using laser irradiation to form pits and applying a small-diameter laser on the ridge between two pits. Utility Model Content

[0005] This invention discloses a nanostructure of laser-surface-treated bone material, wherein the bone material includes: a dental implant or a bone screw, wherein the implant has a connecting end and a threaded portion, the threaded portion having a threaded protrusion and a threaded concave portion, wherein the bone screw has at least one thread, wherein the surface of the bone material is titanium metal, and a laser-processed layer is provided on it, which is composed of titanium dioxide (TiO2) formed by continuous laser ablation and melting of the titanium metal surface of the bone material and cooling, and the laser-processed layer has at least one microchannel in the linear direction of advancement, wherein the at least one microchannel includes: at least one micropore disposed on the bottom side of the at least one microchannel;

[0006] At least one nanowall is disposed on the longitudinal side of the at least one microchannel, including at least one nanoparticle layer and at least one wall layer on the lower end surface of the at least one nanowall; and

[0007] At least one guiding channel is provided between adjacent nanowalls;

[0008] The guiding channel between adjacent nanowalls has a first width, and the thickness of the nanowalls between parallel adjacent nanowalls has a pitch.

[0009] The first height of the at least one microchannel includes: a second height of the at least one nanowall, and a third height representing the depth of the micropore; and

[0010] The roughness of the at least one nano-scale protrusion layer is greater than the roughness of the at least one wall layer formed on the bottom side of the adjacent guide channel.

[0011] This invention discloses a method for laser surface treatment of a titanium metal material, comprising the following steps: using a laser to continuously and precisely irradiate the titanium metal surface of the material along its straight-axis direction to continuously ablate the formed molten titanium metal, which, upon cooling, forms titanium dioxide (TiO2). At least one microchannel is formed along the straight-axis direction by sputtering the molten titanium metal, wherein the bottom side of the at least one microchannel is formed by continuously sputtering at least one continuous micropore beneath the titanium metal surface using the laser. The longitudinal side of the microchannel is formed by continuously melting and sputtering the laser along the direct axis of the laser, creating at least one nanowall around the at least one micropore on the titanium surface. At least one guiding channel is formed between the at least one nanowall using the laser in a direction perpendicular to the irradiated direct axis. The guiding channel between adjacent nanowalls has a first width, and the thickness of the nanowall parallel to the adjacent guiding channels is... The laser has a pitch; when irradiating the titanium metal surface of the bone material with the laser, a first height of the at least one microchannel is formed along the longitudinal axis perpendicular to the direct axis of the laser irradiation, wherein the first height includes: a second height of the at least one nanowall and a third height of the micropore depth; when irradiating the titanium metal surface with the laser, at least one nanoparticle layer of clump-shaped nanoparticles is formed by molten sputtering on the upper end surface of the at least one nanowall; and when irradiating the titanium metal surface with the laser, at least one nanoparticle layer of clump-shaped nanoparticles is formed on the upper end surface of the at least one nanowall. The lower end surface of the nanowall is formed by molten sputtering on a titanium metal surface to form at least one sublayer; wherein, the roughness of the molten sputtering on the titanium metal surface is formed by using a laser to irradiate it, and the roughness of the at least one nano-particle layer is greater than the roughness formed by the at least one sublayer of the wall on the bottom side of the adjacent guide channel; wherein, the micropores are provided to activate cells into osteoblasts, and the osteoblasts form at least one Z-shaped network of attachments that rapidly adhere to the nano-particle layers of the adjacent at least one nanowall of the at least one guide channel.

[0012] This invention discloses a method for laser surface treatment of aggregate, wherein the first width of the guiding channel between adjacent at least one nanowall is 20 μm to 50 μm, the thickness of the nanowall between parallel adjacent at least one guiding channel 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 at least one nanowall is 10 μm to 30 μm, the third height of the micropore depth is 10 μm to 30 μm, the pitch of the thickness of at least one nanowall is 10 μm to 30 μm, the diameter of at least one micropore is 20 μm to 50 μm, and the spacing between at least one micropore is 30 μm to 50 μm.

[0013] This invention discloses a method for laser surface treatment of bone materials, wherein the laser is switched in Q-Switch mode to output short pulses of solid-state laser with controlled power intensity to perform continuous micro-ablation in the straight axis direction.

[0014] This invention discloses a method for laser surface treatment of bone material, wherein during the activation of osteoblasts in at least one of the at least one attachment, the protein secretions formed by preosteoblasts are selected from at least one of type I collagen α1 chain (COL1A1), core proteoglycan (Decorin, DCN), tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), and secretory phosphoprotein-1 (SPP1).

[0015] This invention discloses a method for laser surface treatment of bone materials, wherein the structure of at least one microchannel has the ability to resist and inhibit the growth of bacteria into the at least one microchannel.

[0016] This invention discloses a method for laser surface treatment of bone materials, wherein the titanium metal is titanium or a titanium alloy, and the microchannel crystal has a rutile crystal structure.

[0017] This invention discloses a method for laser surface treatment of bone materials, wherein the bone material is a dental implant or a bone screw.

[0018] This invention relates to a method for laser surface treatment of bone material, wherein the bone material is placed horizontally, and blood is dripped onto the threaded portion of the bone material, resulting in a contact angle of 0 to 12 degrees.

[0019] This invention discloses a method for laser surface treatment of bone materials, wherein the contact angle of the blood is reduced to 0 degrees, requiring a time of less than 20 seconds.

[0020] This invention discloses a method for laser surface treatment of bone materials, wherein the guiding channel between adjacent at least one nanowall forms a nutrient, blood, serum, and bone calcification transport and exchange channel, wherein the micropores of the at least one microchannel form a micro-culture dish, and wherein the at least one guiding channel and the at least one micropore form a simulated biological environment of the at least one microchannel to promote the formation of new blood vessels.

[0021] This invention discloses a nanostructure for laser-treated bone material. The bone material has a titanium metal surface. A laser continuously and precisely irradiates the titanium metal surface of the bone material to continuously ablate it, forming molten titanium metal. After cooling, titanium dioxide (TiO2) is formed. At least one microchannel is formed along the direct axis of the laser beam by sputtering the molten titanium metal. This at least one microchannel includes at least one micropore located on the bottom side of the at least one microchannel. The continuous molten sputtering of the laser along the direct axis of the laser beam forms a nanostructure beneath the titanium metal surface. The at least one microchannel has at least one micropore; at least one nanowall is disposed on the longitudinal side of the at least one microchannel, along the direct direction of the laser's propagation. After the laser continuously melts and sputters the at least one micropore, it melts and sputters onto the titanium metal surface, forming the at least one nanowall of the at least one microchannel. On the upper end surface of the at least one nanowall, at least one nanoparticle layer of clump-shaped nanoparticles is formed by melt sputtering from the titanium metal surface, and on the lower end surface of the at least one nanowall... At least one wall layer is formed by molten sputtering on a titanium metal surface; and at least one guiding channel is disposed between adjacent nanowalls, forming at least one guiding channel of the at least one microchannel by molten sputtering between adjacent nanowalls in a direction perpendicular to the irradiated straight axis; wherein the guiding channel between adjacent nanowalls has a first width, and the thickness of the nanowalls parallel to the at least one guiding channel has a pitch; wherein the first height of the at least one microchannel includes: The second height of the at least one nanowall and the third height of the micropore depth; wherein, the change in roughness formed by the molten sputtering of the titanium metal surface by using the laser irradiation, the roughness of the at least one nano-particle layer is greater than the roughness formed by the at least one wall layer on the bottom side of the adjacent guide channel; wherein, providing the micropores activates cells into osteoblasts, the osteoblasts form at least one Z-shaped network of attachments, and rapidly adhere to the nano-particle layers of the adjacent at least one nanowall of the at least one guide channel.

[0022] The present invention discloses a nanostructure for laser surface treatment of a bone material, wherein the first width of the guiding channel between adjacent at least one nanowall is 20 μm to 50 μm, the thickness of the nanowall between parallel adjacent at least one guiding channel 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 at least one nanowall is 10 μm to 30 μm, the third height of the micropore depth is 10 μm to 30 μm, the pitch of the thickness of at least one nanowall is 10 μm to 30 μm, the diameter of at least one micropore is 20 μm to 50 μm, and the spacing between at least one micropore is 30 μm to 50 μm.

[0023] This invention relates to a nanostructure of bone material for laser surface treatment, wherein the laser, in the Q-Switch mode, outputs short pulses of solid-state laser with controlled power intensity to perform continuous micro-ablation in the straight axis direction.

[0024] The present invention discloses a nanostructure for laser-treated bone material, wherein, during the osteoblast activation process of at least one attachment, a protein secretion of pre-osteoblast cells is formed, which is selected from at least one of type I collagen α1 chain (COL1A1), core proteoglycan (Decorin, DCN), tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), and secretory phosphoprotein-1 (SPP1).

[0025] The present invention discloses a nanostructure for laser surface treatment of bone material, wherein the structure of at least one microchannel has the ability to resist and inhibit the growth of bacteria into the at least one microchannel.

[0026] This invention relates to a nanostructure of laser-treated bone material, wherein the titanium metal is titanium or a titanium alloy, and the microchannel crystal has a rutile crystal structure.

[0027] This invention relates to a nanostructure of laser-treated bone material, wherein the bone material is a dental implant or a bone screw.

[0028] This invention relates to a nanostructure of laser-treated bone material, wherein the bone material is placed horizontally, and blood is dripped onto the threaded portion of the bone material, resulting in a contact angle of 0 to 12 degrees.

[0029] This invention relates to a nanostructure of bone material that undergoes laser surface treatment, wherein the contact angle of the blood is reduced to 0 degrees, requiring less than 20 seconds.

[0030] This invention relates to a nanostructure of bone material with laser surface treatment, wherein the guiding channel between adjacent at least one nanowall forms a transport and exchange channel for nutrients, blood, serum, and bone calcification, wherein the micropores of the at least one microchannel form a micro-culture dish, and wherein the at least one guiding 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.

[0031] This invention discloses a method for laser surface treatment of bone materials and its nanostructure. The invention features a nano-walled nanoparticle layer, a sublayer, micropores, and guiding channels on the titanium surface, enhancing protein adhesion and cell attachment. This provides more climbing sites for pre-osteoblasts and provides resistance to biofilm formation, increasing bone integration, osteoblast proliferation and adhesion, and osteogenic differentiation. Furthermore, the deeper microchannels on the titanium surface created by the laser treatment generate more space, promoting adequate nutrient supply to pre-osteoblasts and facilitating their maturation process, including proliferation, osteogenic differentiation, and extracellular mineralization. Specifically, this invention achieves faster bone healing and stable bone integration with human tissue.

[0032] This invention discloses a method for laser surface treatment of bone materials and its nanostructure. The method involves establishing a working module—a laser-processed micron-channel attachment of micron-pores and nanostructures. This structure can increase the following bone healing and antibacterial indicators: A. Accelerating the deposition of bone healing-related proteins; B. Accelerating bone cell attachment; C. Inducing angiogenesis; D. Accelerating initial calcification and bone mineralization; E. Improving nutrient exchange; F. Stabilizing surface bone structure; G. Resisting dental plaque formation. Attached Figure Description

[0033] Figure 1 This is a schematic diagram of the nanostructure of the laser surface-treated bone material according to this utility model.

[0034] Figure 2 This is a schematic diagram of the periodontal ligament corresponding to the bone implant for laser surface treatment according to this utility model.

[0035] Figure 3 This is a schematic diagram showing the laser surface treatment of bone implants according to this invention, applied to the laser irradiation and the corresponding angle of the implant shape.

[0036] Figure 4 This is a schematic diagram of a bone nail made of laser-treated bone material, applied to the scaphoid bone of the hand.

[0037] Figure 5 This is a schematic diagram of the laser surface treatment of bone implants according to this invention, applied to the blood contact angle and adsorption angle.

[0038] Figure 6 This is a schematic diagram of the nanostructure of the laser surface-treated bone material according to this invention, compared with that of sandblasting and acid etching.

[0039] Figure 7 This is a schematic diagram of a scanning electron microscope image showing the nanostructure of the laser-treated bone material of this invention, compared with titanium plates that have been ground and sandblasted and acid-etched.

[0040] Figure 8 This is a schematic diagram of the nanostructure of the laser surface-treated bone material according to this invention, compared with that of sandblasting and acid etching.

[0041] Figure 9 This is a schematic diagram illustrating the serum adhesion of bone materials treated by laser surface treatment according to this invention, compared with sandblasting and acid etching.

[0042] Figure 10 This is a schematic diagram showing the cell number of bone material treated by laser surface treatment according to this invention, compared with grinding and sandblasting / acid etching.

[0043] Figure 11-1 This diagram illustrates the ratio of mRNA expression in bone material treated with laser according to this invention, compared to grinding and sandblasting / acid etching.

[0044] Figure 11-2 This is a schematic diagram of the Western blot assay of purified cell protein lysate for (A) COL1A1, (B) DCN, (C) TNFRSF11B, (D) SPP1 and β-actin antibodies in the laser surface-treated bone material of this utility model.

[0045] Figure 12 This diagram illustrates the concentrations of COL1A1, DCN, and TNFRSF11B in the laser-treated bone material of this invention, compared to those obtained through grinding and sandblasting / acid etching.

[0046] Figure 13 This is a schematic diagram illustrating the mineralization of aggregates through laser surface treatment, compared to grinding and sandblasting / acid etching.

[0047] Figure 14 The diagram shows that the guiding channel of this invention has a sufficient first width of 20μm to 50μm, compared with the implant of the prior art which is only 10μm. The microchannel surface of this invention has better bone cell growth.

[0048] Figure 15 This is a schematic diagram illustrating the tightly integrated implant and bone interface structure of this utility model, which is completely different from the separation phenomenon of SLA implant and bone interface structure.

[0049] Figure 16 This diagram illustrates the formation and quantity of biofilm on five surfaces: the nanostructured surface of the microchannel of this invention, a laser-etched surface with dot-matrix pits, a machined surface, a polished surface, and a sandblasted surface, as well as the composition and quantity of dental plaque.

[0050] Symbol explanation:

[0051] 3. Titanium

[0052] 10 microchannels

[0053] 11 nanometer walls

[0054] 111 nanometer-sized protrusion layer

[0055] 112 Bottom layer of the wall

[0056] 12 micropores

[0057] 15. Attachments

[0058] 16 Guide Channels

[0059] D1 Altitude 1

[0060] D2 Altitude 2

[0061] D3 3rd height

[0062] D4, 4th Altitude

[0063] P1 pitch

[0064] W1 First Width

[0065] K laser irradiation scanning direction

[0066] 51 teeth

[0067] 52. Gum

[0068] 53 Periodontal ligament

[0069] 54 Alveolar bone

[0070] 55 Blood Vessels

[0071] 60 implants

[0072] 61 Threaded section

[0073] 611 Threaded protrusion

[0074] 612 Threaded recess

[0075] 613 Surface

[0076] 62 Joint end

[0077] 71 fingers

[0078] 72. Scaphoid bone

[0079] 721 Fracture fissure

[0080] 722 Front end

[0081] 723 Rear End

[0082] 724 Bone Marrow

[0083] 73 Blood vessels

[0084] 74 bone screws

[0085] 8. Blood

[0086] 81 Horizontal Line

[0087] α Contact angle

[0088] β adsorption angle

[0089] SLA sandblasting and acid etching group

[0090] G Grinding Group

[0091] L laser irradiation group

[0092] COL1A1 Type I Collagen α1 Chain

[0093] Decorin (DCN) is a core proteoglycan.

[0094] TNFRSF11B is a member of the tumor necrosis factor receptor superfamily.

[0095] SPP1 secretory phosphoprotein-1

[0096] β-actin, a protein of β-actin

[0097] OCN osteocalcin (osteocalcin, OCN). Detailed Implementation

[0098] like Figure 1 , Figure 6 , Figure 7 , Figure 8As shown in one embodiment of the present invention, a method for laser surface treatment of a material is provided. The at least one microchannel 10 includes at least one micropore 12, at least one nanowall 11, and at least one guiding channel 16. The at least one nanowall 11 includes at least one nano-particle layer 111 and at least one bottom wall layer 112. The steps include: using a laser to continuously and precisely irradiate the surface of the titanium metal 3 of the material along its linear direction to continuously ablate and form molten titanium metal. The molten titanium metal 3 is then sputtered to form at least one microchannel 10 along its linear direction. The bottom side of the at least one microchannel 10 is formed by continuously sputtering the at least one micropore 12 beneath the surface of the titanium metal 3 using the laser. The longitudinal side of the at least one microchannel 10 is formed by continuously sputtering the at least one micropore along the linear direction of the laser. After the hole 12, the at least one micropore 12 is melt-splashed onto the surface of the titanium metal 3, forming at least one nanowall 11 of the at least one microchannel 10; using the laser in a direction perpendicular to the irradiated axis, at least one guiding channel 16 of the at least one microchannel 10 is formed between the at least one nanowall 11 by melt-splashing, the guiding channel 16 between adjacent nanowalls 11 having a first width W1, and the thickness of the nanowall 11 parallel to adjacent guiding channels 16 having a pitch P1; using the laser to irradiate the surface of the titanium metal 3 of the bone material. Along the longitudinal axis perpendicular to the direct axis of the laser irradiation, a first height D1 of the at least one microchannel 10 is formed, 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; using the laser to irradiate the surface of the titanium metal 3, at least one nanoparticle layer 111 is formed by molten sputtering of clumps of nanoparticles on the upper end surface of the at least one nanowall 11; and using the laser to irradiate the surface of the titanium metal 3, at least one nanoparticle layer 111 is formed by molten sputtering of clumps of nanoparticles on the lower end surface of the at least one nanowall 11; At least one sub-wall layer 112 is formed by molten sputtering on the surface of the titanium metal 3; wherein, when irradiated with a laser, the roughness of the molten sputtering on the surface of the titanium metal 3 changes, and the roughness of the at least one nano-particle layer 111 is greater than the roughness of the at least one sub-wall layer 112 formed on the bottom side of the adjacent guide channel 16; wherein, the micropores 12 provide activation of cells into osteoblasts, and the osteoblasts form at least one Z-shaped network of attachments 15, which rapidly adhere to the nano-particle layers 111 of the adjacent at least one nanowall 11 of the at least one guide channel 16. The laser irradiation scanning direction is K. The interface formed between the at least one nano-particle layer 111 on the upper end surface of the at least one nanowall 11 and the at least one sub-wall layer 112 on the lower end surface of the at least one nanowall 11 is a cell attachment zone, which activates cells into osteoblasts.The laser is continuously and precisely irradiated onto the surface of the titanium metal 3 of the aggregate to continuously ablate and form molten titanium metal. Titanium dioxide is formed during the cooling process after the ablation; during the ablation process, before cooling, there is no titanium dioxide, but rather molten titanium metal.

[0099] like Figure 1 , Figure 6 , Figure 7 , Figure 8 As shown in the figure, one embodiment of this invention is a method for laser surface treatment of bone materials and its nanostructure. In this method, a titanium dioxide oxide layer is formed on the surface of titanium metal 3, which can optimize the adhesion and regeneration of blood and bone cells. The nanostructure of this invention is formed by laser. When irradiated by laser emission, the irradiated area on the surface of titanium metal 3 continuously melts, sputters, and ablates, combining with oxygen atoms in the air to form a titanium dioxide oxide layer. The thickness of this oxide layer is determined by adjusting the laser parameters. X-ray photoelectron spectroscopy measurements showed that the oxide layer thickness at the bottom of the microchannel 10 and the bottom of the micropore 12 was approximately 45 nm, and at the top of the microchannel 10 and the top of the nanowall 11 was approximately 110 nm. Compared to other existing surface structures, the oxide layer of the surface structure of this invention is significantly thicker.

[0100] like Figure 1 , Figure 6 , Figure 7 , Figure 8 As shown in the figure, one embodiment of the present invention is a method for laser surface treatment of bone material and its nanostructure, wherein the first width W1 of the guiding channel 16 between adjacent nanowalls 11 is 20μm to 50μm, the thickness of the nanowalls 11 between parallel adjacent guiding channels 16 has a pitch P1 of 10μm to 30μm, the first height D1 of the at least one microchannel 10 is 20μm to 60μm, the second height D2 of the at least one nanowall 11 is 10μm to 30μm, the third height D3 of the depth of the micropore 12 is 10μm to 30μm, the pitch P1 of the thickness of the at least one nanowall 11 is 10μm to 30μm, the diameter of the at least one micropore 12 is 20μm to 50μm, and the spacing of the at least one micropore 12 is 30μm to 50μm.

[0101] like Figure 1 , Figure 6 , Figure 7 , Figure 8 As shown in the figure, one embodiment of the present invention is a method for laser surface treatment of bone materials and its nanostructure. In this method, the laser is switched in Q-Switch mode to output short pulses of solid-state laser, which, through controlled power intensity, perform continuous micro-ablation in the straight axis direction.

[0102] like Figures 11-1 to 12 As shown in one embodiment of the present invention, a method for laser surface treatment of bone material and its nanostructure are described. In the process of osteoblast activation of the at least one attachment 15, the protein secretion formed by preosteoblasts is selected from at least one of type I collagen α1 chain (COL1A1), core proteoglycan (Decorin, DCN), tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), and secretory phosphoprotein-1 (SPP1).

[0103] like Figure 16 As shown in the figure, one embodiment of the present invention is a method for laser surface treatment of bone material and its nanostructure, wherein the structure of the at least one microchannel 10 has the ability to resist and inhibit the growth of bacteria into the at least one microchannel 10.

[0104] like Figure 5 As shown in one embodiment of this utility model, a method for laser surface treatment of bone material and its nanostructure are disclosed. The titanium metal 3 is titanium or a titanium alloy, and the microchannel 10 crystals have a rutile crystal structure. The bone material is a dental implant or a bone screw. When the bone material is placed horizontally, blood is dripped onto the threaded portion of the bone material, creating a contact angle of 0 to 12 degrees. The contact angle of the blood decreases to 0 degrees within less than 20 seconds.

[0105] like Figures 1 to 9 As shown, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure. In this method, the guiding channel 16 between adjacent nanowalls 11 forms a transport and exchange channel for nutrients, blood, serum, and bone calcification. The micropores 12 of the at least one microchannel 10 form a micro-culture dish. The at least one guiding channel 16 and the at least one micropore 12 form a simulated biological environment for the at least one microchannel 10, promoting the formation of new blood vessels.

[0106] like Figures 1 to 9 As shown in the illustration, one embodiment of this invention provides a method for laser surface treatment of bone materials and its nanostructure. This invention improves nutrient exchange; the microchannel 10 provides an excellent surface area for monolayer cell attachment, while simultaneously enabling good temperature regulation and rapid exchange of liquid media. It is suitable for the growth and differentiation of osteoblasts and endothelial cells within and outside the nanostructured microchannel 10.

[0107] like Figures 1 to 9As shown in one embodiment of the present invention, a nanostructure of a laser-treated bone material is described. The surface of the bone material is titanium metal 3. A laser continuously and precisely irradiates the surface of the titanium metal 3 to continuously ablate and form molten titanium metal. The molten titanium metal 3 is then sputtered to form at least one microchannel 10 along the direct axis of the laser beam. Each microchannel 10 includes at least one micropore 12 located on the bottom side of the at least one microchannel 10. The at least one micropore 12 is continuously formed along the direct axis of the laser beam by sputtering the molten titanium metal 3 beneath the surface of the surface. A hole 12; at least one nanowall 11, located on the longitudinal side of the at least one microchannel 10, along the direct direction of the laser's propagation, is formed by continuous molten sputtering of the at least one microhole 12 by the laser, and then molten sputtering around the at least one microhole 12 onto the surface of the titanium metal 3, forming at least one nanoparticle layer 111 of clump-shaped nanoparticles formed by molten sputtering from the surface of the titanium metal 3 on the upper end surface of the at least one nanowall 11, and at least one nanoparticle layer 111 of clump-shaped nanoparticles formed by molten sputtering from the surface of the titanium metal 3 on the lower end surface of the at least one nanowall 11. At least one wall substrate 112; and at least one guiding channel 16, disposed between adjacent nanowalls 11, wherein the guiding channel 16 of the at least one microchannel 10 is formed by melt sputtering between adjacent nanowalls 11 in a vertical direction along the irradiated axis; wherein the guiding channel 16 between adjacent nanowalls 11 has a first width W1, and the thickness of the nanowalls 11 parallel to the at least one guiding channel 16 has a pitch P1; wherein the first height D1 of the at least one microchannel 10 includes: the at least one nanowall The second height D2 of 11 and the third height D3 of the depth of the micropore 12; wherein, the change in roughness formed by the molten sputtering of the titanium metal 3 surface by using the laser irradiation, the roughness of the at least one nano-particle layer 111 is greater than the roughness formed by the at least one wall layer 112 on the bottom side of the adjacent guide channel 16; wherein, the micropore 12 is provided to activate cells into osteoblasts, the osteoblasts form at least one attachment 15 in a Z-shaped network, and rapidly attach to the nano-particle layer 111 of the adjacent at least one nanowall 11 of the at least one guide channel 16.

[0108] like Figure 2As shown in the figure, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure. The tooth 52 and alveolar bone 54 are connected by a periodontal ligament 53. The gingiva 52 has blood vessels 55, and the periodontal ligament 53 provides nutrients and blood to the tooth 53 and alveolar bone 54 via the blood vessels 55. The tooth implant 60 of this utility model, which uses laser surface treatment of bone materials, has microchannels 10 that can simulate the function of the periodontal ligament 53. The microchannel 10 structure can increase bone healing and antibacterial indicators, accelerate the deposition of bone healing-related proteins, accelerate bone cell attachment, induce angiogenesis, accelerate initial calcification and bone mineralization, improve nutrient exchange, stabilize the surface bone structure, and resist plaque formation. The microchannels 10 on the laser surface of this utility model provide nutrients and blood to the alveolar bone via blood vessels, accelerating bone healing with the alveolar bone.

[0109] like Figure 3 As shown in the figure, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure. The implant 60 has a joint end 62 and a threaded portion 61, with a threaded protrusion 611 and a threaded concave portion 612. If the surface layer 613 of the threaded portion is parallel to the laser irradiation scanning direction K, the laser irradiation cannot scan the sputtered surface layer 613. Therefore, the surface layer 613 of the threaded protrusion 611 and the threaded concave portion 612 can be trapezoidal. By forming a non-parallel angle between the surface layer 613 and the laser irradiation scanning direction K, the laser irradiation can effectively sputter the surface layer 613, forming a specific structure of effective microchannel 10, including a nano-protrusion layer 111 of nanowall 11, a wall bottom layer 112 of nanowall 11, micropores 12, and guiding channels 16 located on the surface of titanium metal 3.

[0110] like Figure 4As shown in one embodiment of this utility model, a method for laser surface treatment of bone materials and its nanostructure are described. In the case of a fracture of the scaphoid bone 72 in the finger 71 and palm due to a sports injury, the fracture fissure 721 of the scaphoid bone 72 breaks it 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 lacks blood vessels 73 supplying bone marrow 724, making it prone to necrosis and hindering fracture healing. The laser-treated bone nail 74 of this utility model forms a specific structure of effective microchannels 10, including a nano-protrusion layer 111 of nanowalls 11, a wall layer 112, micropores 12, and guide channels 16 located on the titanium surface of the bone nail 74. This structure can increase bone healing and antibacterial indicators, accelerate the deposition of bone healing-related proteins, accelerate bone cell attachment, induce angiogenesis, accelerate initial calcification and bone mineralization, improve nutrient exchange, stabilize the surface bone structure, and resist dental plaque formation. Therefore, the posterior end 723 has microchannels 10 supplying blood and nutrients to the bone marrow 724, so the scaphoid bone 72 is not prone to necrosis and fractures are easier to heal faster.

[0111] like Figure 5As shown in the figure, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure. A blood droplet test is performed on the implant 60. The implant 60 is placed vertically, and the blood droplet 8 is at a height D4, resulting in an adsorption angle β of 0 to 15 degrees. With the implant 60 placed vertically, the contact angle α drops to 0 degrees in less than 20 seconds. Because the laser-treated implant 60 of this utility model forms a specific structure of effective microchannels 10 on the titanium surface of the implant 60, including a nano-protrusion layer 111 of nanowalls 11, a bottom layer 112 of the nanowalls 11, micropores 12, and guiding channels 16, the adsorption angle β of this utility model is greater than that of general implants in the grinding (G) and sandblasting acid etching (SLA) groups. The contact angle α of this utility model is also smaller than that of general implants in the grinding (G) and sandblasting acid etching (SLA) groups. Furthermore, the microspheres flowing through the surface of the nanostructure of this invention can flow at a significantly higher speed, resulting in substantial differences in cell adhesion and protein uptake. In the laser-treated structure with hydrophilic micro / nanopores, cell adhesion, proliferation, differentiation, and prostaglandin E2 production on the surface of this invention are higher than those on polished titanium and SLA-treated titanium surfaces. Laser treatment can prepare the hydrophilic micro / nanoporous titanium surface of this invention, and the surface characteristics of this invention enhance the adhesion, proliferation, and differentiation of MG-63 cells. Moreover, dental implants with the surface characteristics of this invention, as shown by scanning electron microscopy (SEM), exhibit high wear resistance, with only minor damage during repeated insertion and removal. These damages include spalling, pitting, and deformation. In contrast, SLA implants show more pitting, deformation, and fusion areas on their surfaces than this invention. Defects in the prior art are particularly easily found at the tip thread corresponding to the self-tapping design. The surface of this invention has no obvious sharp edges or irregularities at the microscopic level, which is why it requires less surface modification and is more durable. Therefore, the macroscopic-nanoscale roughness of this invention is less susceptible to damage under high torque. In contrast, SLA surfaces typically exhibit sharp edges and irregularities, which inevitably deform and become damaged under compressive forces. The surface of this invention is also more physically resistant to pressure, and in clinical applications, implant removal and reinsertion will not endanger the implant.

[0112] like Figures 9 to 12As shown in the figure, one embodiment of this invention is a method for laser surface treatment of bone materials and its nanostructure. This invention accelerates the deposition of bone healing-related proteins. This invention uses high laser energy to generate a high oxide layer (45-110nm) on the surface of the titanium metal 3 structure of this invention. The titanium dioxide oxide layer can optimize blood and serum compatibility, thereby providing an environment for fibrin adhesion, which in turn facilitates the formation of a temporary matrix, which is important for the early stages of bone healing. Figure 9 As shown, the serum viscosity test of this invention is as follows: because the implant 60 of this invention with laser surface treatment forms a specific structure of effective microchannel 10, including the nano-protrusion layer 111 of the nanowall 11, the wall bottom layer 112, the micropores 12, and the guiding channel 16 located on the titanium surface of the implant 60, the serum viscosity is greater than that of general implants in the grinding group (G) and sandblasting acid etching group (SLA).

[0113] like Figure 1 As shown in one embodiment of this utility model, a method for laser surface treatment of bone materials and its nanostructure are described. In this method, at the laser surface, the first height D1, second height D2, and third height D3 of the microchannel 10 are not suitable if the irradiation and melting sputtering are too shallow, as there will not be sufficient depth of the guiding channels 16, making it difficult to provide nutrients, blood, and serum. The first width W1 of the microchannel 10 is not suitable if it is too wide, because the attachment material 15 will not easily adhere, such as the protein secretions of pre-osteoblasts, and will not easily adhere to form between the at least one nanowall 11 on the upper layer of the guiding channels 16, making it difficult to form a Z-shaped network. The first width W1 of the microchannel 10 is not suitable if it is too narrow, resulting in less adhesion of the attachment material 15. The microchannel 10 is not suitable if the special nano-protrusion layer 111 of the nanowall 11 is not sputtered out, because on the upper layer of the guiding channels 16, the reticular cells of the attachment material 15 or pre-osteoblasts will not easily adhere to the nano-protrusion layer 111, and the pre-osteoblast protein secretions will not easily be expressed and secreted. The microchannel 10 contains multiple sputtered deep micropores 12 at a third height D3, which have a biomimetic environment for growth and a micro-culture dish effect. This novel microchannel, by scanning the same position vertically and horizontally, uses laser frequency, energy intensity, pulse (frequency), and specific unit area / unit time / unit pulse / unit energy to produce the optimal structure described above.

[0114] like Figure 7 ,as well as Figure 10As shown in the figure, one embodiment of the present invention is a method for laser surface treatment of bone materials and its nanostructure. The scanning electron microscope images are shown on titanium plates with surfaces treated by three groups: grinding (G), sandblasting acid etching (SLA), and laser irradiation (L). Figure 10 As shown, pre-osteoblasts, palatal mesenchyma cells from human embryos, have been shown to differentiate into osteoblasts on titanium plates. This invention utilizes 2.3 × 10⁻⁶ cells... 5 Pre-osteoblasts were cultured for 3 days on titanium plates with surfaces treated in three groups: grinding (G), sandblasting acid etching (SLA), and laser irradiation (L). The effects of the three modified titanium surfaces on pre-osteoblast growth were analyzed based on the pre-osteoblast proliferation rate. The laser irradiation group (L) showed a higher cell count than the grinding group (G) and the sandblasting acid etching group (SLA). This invention accelerates osteoblast attachment; the structure of the microchannel 10 maximizes the surface area for monolayer cell attachment while achieving good temperature regulation and rapid exchange of liquid culture medium. The microchannel 10 of this invention serves as a bioreactor, generating a localized flow environment in which many cell types, such as osteoblasts (bone cells) and endothelial cells (vascular lining), have evolved to prefer continuous exposure to shear stress of 0.1 dynes / cm and exhibit only the normal phenotype in the environment of the microchannel 10 of this invention.

[0115] like Figure 11-1As shown in this embodiment, a method for laser surface treatment of bone material and its nanostructure are described. This invention accelerates osteoblast adhesion. The titanium metal surface with the laser microchannel 10 structure of this invention increases bone integration capacity compared to the SLA group and the G-treated surface group. The laser-treated titanium surface with the channel structure of this invention enhances pre-mature osteoblast bone integration. According to the qPCR results of this invention, the pre-osteoblasts treated with the laser irradiation (L) group showed significantly increased mRNA and protein expression / secretion ratios of COL1A1, DCN, TNFRSF11B, and SPP1, as well as extracellular mineralization. Among them, 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). This invention regulates the expression of pre-osteoblastic differentiation markers obtained by qPCR on titanium surfaces treated with this novel method. 2.3 × 10⁻⁶ 5Pre-osteoblast cells were incubated for 72 hours on titanium plates with surfaces treated with grinding (G), sandblasting acid etching (SLA), and laser irradiation (L), respectively. Purified cellular mRNA was used for qPCR assays of COL1A1, DCN, TNFRSF11B, and SPP1 primer sets. Osteogenic differentiation markers, such as COL1A1, DCN, TNFRSF11B, and SPP1, were identified. Type I collagen alpha 1 (COL1A1) is the main 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 maintaining tissue development and homeostasis. Decorin (DCN) is a protein encoded by the DCN gene in humans. It is a proteoglycan, specifically a pericellular matrix proteoglycan closely related to biglycan proteins. Decorin is a result of gene replication. This protein is a component of connective tissue, binds to type I collagen fibrils, and plays a role in matrix assembly. Decorin (DCN) gets its name from its decoration of type I collagen and its interaction with the "d" and "e" bands of these collagen fibrils. Decorin influences fiber formation, specifically myokine. In this process, it binds to myostatin to promote muscle hypertrophy.Among them, tumor necrosis factor receptor superfamily member 11B (TNFRSF11B), also known as osteoprotegerin (OPG) or osteoclastogenesis inhibitory factor (OCIF), is a novel secreted tumor necrosis factor receptor (TNFR)-related protein that plays a role in bone mineral density regulation. Secreted phosphoprotein-1 (SPP1), also known as osteopontin (OPN), is a glycoprotein associated with bone formation. Secreted phosphoprotein-1 (SPP1) plays a role in anchoring osteoclasts to the bone remodeling matrix by binding to the vitronectin (VTN) receptor. Vitronectin (VTN) is a multifunctional glycoprotein with various physiological functions, present in plasma and the extracellular matrix. Vitronectin (VTN) primarily binds to integrin receptors via its RGD sequence, participating in cell attachment, diffusion, and migration. Vitronectin (VTN) is also widely used for the maintenance and expansion of pluripotent stem cells. Vitronectin (VTN) has even more functions in the nervous system, as it participates in neural differentiation, neurotrophic factors, and neurogenesis, as well as regulating axon size and supporting and guiding neurite extension. In addition, vitronectin (VTN) has been shown to play a key role in protecting the brain because it can reduce the permeability of the blood-brain barrier by interacting with integrin receptors in vascular endothelial cells.

[0116] like Figure 11-1As shown in one embodiment of this invention, a method for laser surface treatment of bone materials and its nanostructure are described. This invention accelerates osteoblast attachment, and pre-osteoblasts express / secrete more COL1A1, DCN, TNFRSF11B, and SPP1 proteins. Furthermore, the expression of osteogenic differentiation markers in pre-osteoblasts was upregulated on the titanium surface treated with laser irradiation (L) using Western blotting.

[0117] like Figure 11-2 As shown, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure, which incorporates 2.3 × 10⁻⁶ nanometers. 5 Pre-osteoblasts were incubated for 72 hours on titanium plates with G, SLA, and L-treated surfaces. Purified cell protein lysates were used for Western blot assays of (A) COL1A1, (B) DCN, (C) TNFRSF11B, (D) SPP1, and β-actin antibodies. Laser irradiation (L) treatment significantly increased the Western blot assays of COL1A1, DCN, TNFRSF11B, and SPP1 on pre-osteoblasts.

[0118] like Figure 12 As shown in one embodiment of this invention, a method for laser surface treatment of bone materials and its nanostructure are described. During osteoblast activation, pre-osteoblasts secrete various proteins, such as COL1A1, OCN, and TNFRSF11B. The laser irradiation group (L) showed significantly higher levels of COL1, OCN, and TNFRSF11B secreted by the pre-osteoblasts on the treated surface. Figure 13 As shown, laser irradiation (L) treatment of titanium surfaces promotes the secretion of osteogenic differentiation markers in pre-osteoblasts. 2.3 × 10⁻⁶ 5Osteoblasts were incubated for 72 hours on titanium plates with G, SLA, and L-treated surfaces. Cellular medium was collected and used for multiplex assays to determine the concentrations of (A) COL1A1, (B) OCN, and (C) TNFRSF11B. Multiplex assay data showed that pre-osteoblasts on the laser-irradiated (L) surface secreted significantly more COL1, OCN, and TNFRSF11B. Osteocalcin (OCN) is a non-collagenous protein secreted by osteoblasts (the cells responsible for bone formation) in bone tissue. It plays an important role in bone metabolism, primarily involved in bone mineralization and calcium binding. Furthermore, osteocalcin (OCN) is also believed to play a role in regulating glucose metabolism and energy balance. 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 hormone found in bone and dentin, initially identified as a calcium-binding protein. Osteocalcin is secreted solely by osteoblasts and is thought to play a role in the body's metabolic regulation. In its carboxylated form, it binds directly to calcium, thus condensing in the bones. In its uncarboxylated form, osteocalcin acts as a hormone in the body, signaling in the pancreas, fat cells, muscles, testes, and brain. In the pancreas, osteocalcin acts on β-cells, causing them to release more insulin. In fat cells, osteocalcin triggers the release of the hormone adiponectin, thereby increasing insulin sensitivity. In muscles, osteocalcin acts on myocytes to promote energy availability and utilization, thus benefiting athletic performance. In the testes, osteocalcin acts on interstitial cells, stimulating testosterone biosynthesis, thus affecting male fertility. In the brain, osteocalcin plays a crucial role in development and function, including spatial learning and memory. The acute stress response (ASR), commonly known as the fight-or-flight response, stimulates the release of osteocalcin from bones within minutes in mice, rats, and humans. In the presence of adrenal insufficiency, injection of high levels of osteocalcin alone can trigger an ASR. Clinically, osteocalcin serves as a biomarker for assessing bone metabolism and for diagnosing and monitoring skeletal diseases such as osteoporosis.

[0119] like Figure 13As shown in one embodiment of this invention, a method for laser surface treatment of bone material and its nanostructure are described. This invention accelerates early calcification. When pre-osteoblasts are seeded onto titanium plates, the laser irradiation (L) group exhibits an increased Alizarin red S stain rate on day 18, indicating that the laser-irradiated (L) surface promotes enhanced calcium ion secretion. Extracellular mineral deposition near the top of the microchannels 10 of the nanostructure was detected using energy-scattered X-ray spectroscopy. When the surface structure of this invention is embedded in a non-cellular solution, there is no significant difference in calcium or potassium compound deposition compared to titanium metal surfaces or SLA-treated surfaces. However, when pre-osteoblasts are implanted into titanium plates, the surface structure of this invention shows an increased Alizarin red S stain rate on day 18, indicating enhanced calcium ion secretion promoted by the surface structure of this invention. The surface of this invention has a significantly higher osteoblast mineralization capacity than SLA-treated titanium surfaces.

[0120] like Figure 13 As shown, one embodiment of this invention is a method for laser surface treatment of bone materials and its nanostructure. This invention accelerates early calcification, and the laser irradiation (L) treatment of titanium surfaces promotes pre-osteoblast extracellular mineralization. (A) 2.3 × 10⁻⁶ cells were cultured on titanium plates with G, SLA, and L-treated surfaces. 5 Images of pre-osteoblast cells were collected 4 or 18 days later. A 100 μm scale bar is shown in the left column, and a 50 μm scale bar in the right column. Reddish-brown calcium compounds indicate the mineralization capacity of the pre-osteoblasts. (B) Quantitative results are shown at the OD540 level. 100 μm and 50 μm scale bars were used for imaging in the left and right columns, respectively.

[0121] like Figure 14 As shown in this embodiment, a method for laser surface treatment of bone material and its nanostructure, as well as the cell morphology and cell adhesion of human fetal osteoblasts (HFOBs) implanted on the implant, are described. Laser-modified titanium implants may increase the chances of successful osseointegration because the microchannels 10 of this invention promote the abundant growth of filamentous pseudopodia human fetal osteoblasts on the implant sample with multiple channels and nanostructures. The guiding channels 16 of this invention have a sufficient first width W1 of 20 μm to 50 μm, compared to the existing implants which are only 10 μm wide, resulting in better osteoblast growth on the surface of the microchannels 10 of this invention.

[0122] like Figure 15As shown in the figure, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure. This utility model can stabilize the surface bone structure, with initial bone formation starting at the lower edge of the nanostructure on the upper edge of the microchannel 10. Clinically, when this utility model is removed from the mouth of a car accident patient, it exhibits a tightly integrated interface. This is completely different from the bone-to-implant interface structure of clinically removed SLA implants, where bone separation from the SLA implant surface is observed. The bone-to-implant integration ability of this utility model is significantly superior to that of the SLA implant. Furthermore, animal experiments also show that within the first two months after implantation, the surface of the this utility model implant already exhibits excellent bone-to-implant integration, while the SLA implant surface only shows integration after the third month.

[0123] like Figure 16 As shown in the figure, one embodiment of this utility model is a method for laser surface treatment of bone materials and its nanostructure. This utility model can resist plaque formation and has the ability to resist and inhibit bacterial growth into at least one microchannel 10. The nanostructure surface of the microchannel 10 of this utility model is compared with the formation and amount of biofilm on five surfaces: a laser-treated surface with a dot-matrix pit, a machined surface, a polished surface, and a sandblasted surface. The nanostructure surface of the microchannel 10 of this utility model has the least amount of biofilm formed because the structure of the microchannel 10 affects the chemical composition of the surface. The microchannel 10 of this utility model has a pitch P1 between the guide channels 16, which prevents the biofilm from crossing the pitch P1 between the guide channels 16. This utility model helps to reduce the occurrence of peri-implantitis. In the prior art, the laser surface of the dot matrix pit lacks the pitch P1 between the guiding channels 16. As biofilm grows and covers different dot matrix pits, the laser surface of the prior art dot matrix pit cannot effectively resist and inhibit the growth of bacteria into the laser surface of the dot matrix pit.

[0124] Existing surface modification methods pose a potential risk of introducing foreign matter onto the implant surface during manufacturing, leading to surface contamination and thus reducing safety and effectiveness. In contrast, an embodiment of this invention, a method for laser surface treatment of bone materials and its nanostructure, is a clean and economical method that avoids direct contact with the implant during surface adjustment, ensuring the product remains uncontaminated. In this embodiment, the microchannel 10 structure formed from titanium metal 3 utilizes a high-temperature laser to form a layer of titanium dioxide (TiO2) titanium oxide, leaving no chemical residues. The nanochannel 10 structure of this invention is primarily in a crystalline phase, wherein the crystalline phase has a rutile crystal structure.

[0125] Compared to SLA and G-treated surfaces, the microchannels 10 on the laser-treated surface of this invention feature a nano-protrusion layer 111 of nanowalls 11, a sublayer 112 of nanowalls 11, micropores 12, and guiding channels 16 on the titanium metal 3 surface. These nano / microporous surface structures enhance protein adhesion and cell attachment, provide more climbing sites for pre-osteoblast stretching, and provide resistance to biofilm formation, promoting osteogenic gene expression, such as the expression of parathyroid hormone-related protein genes in osteoblasts. This increases bone integration, osteoblast proliferation and adhesion, and osteogenic differentiation. The more complex nanoscale structure surrounding the microchannels 10 on the titanium metal 3 surface at the laser-treated surface provides more climbing sites for pre-osteoblast stretching, which may promote osteogenic gene expression, such as the expression of parathyroid hormone-related protein genes in osteoblasts. In addition, the deeper microchannels 10 on the titanium surface at the laser-treated surface of this invention create more space, promoting adequate nutrient replenishment for pre-osteoblasts and contributing to the pre-osteoblast maturation process, including proliferation, osteogenic differentiation, and extracellular mineralization.

[0126] This invention relates to microchannels 10 on a titanium surface at a laser-guided surface, where each process is controlled by specific osteogenic differentiation markers that regulate cellular responses. For example, COL1A1 is upregulated during osteoblast differentiation, and SPP1 is a marker of extracellular matrix maturation. DCN regulates collagen matrix assembly and mineralization, and also regulates the cell cycle, which is expressed during extracellular matrix mineralization. Furthermore, osteoprotegerin, translated from the TNFRSF11B gene, is a suppressor of bone resorption. Physiological stretching of cells affects the expression of insulin-like growth factor and mechanotrophic factor. Mechanostretching is mediated through the mechanosensor polycystin-1 in human osteoblasts. Runx2 expression is promoted via 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 on laser-generated microchannels 10 may be caused by the effect of mechanical tensile force. In the pre-osseous integration stage, the microchannels 10 on the laser-generated titanium surface of this invention allow mesenchymal fibroblast-like cells and endothelial cells to play a crucial role in angiogenesis immediately during implantation. After the stabilization period, the antibacterial properties of the processed implant suggest the possibility of eliminating peri-implantitis. The laser-generated titanium surface microchannels 10 of this invention, when applied to bone material, can enhance angiogenesis and antibacterial capabilities. Furthermore, it enhances pre-osteoblast proliferation and promotes the expression / secretion of COL1, SPP1, DCN, and TNFRSF11B mRNA and protein, as well as extracellular mineralization.

[0127] The above description and explanation are merely illustrative of preferred embodiments of the present utility model. Those skilled in the art can make other modifications based on the following defined claims and the above description, but such modifications should still be within the creative spirit of the present utility model and within the scope of the claims of the present utility model.

Claims

1. A nanostructure for laser-surface-treated bone material, characterized in that, The bone material includes: a dental implant or a bone screw, wherein the implant has a connecting end and a threaded portion, the threaded portion having a threaded protrusion and a threaded concave portion, wherein the bone screw has at least one thread, wherein the surface of the bone material is titanium metal, and a laser-processed layer is provided on it, which is composed of titanium dioxide (TiO2) formed by continuous laser ablation and melting of the titanium metal surface of the bone material and subsequent cooling, the laser-processed layer having at least one microchannel in the linear direction of travel, the at least one microchannel including: At least one micropore is provided on the bottom side of the at least one microchannel; At least one nanowall is disposed on the longitudinal side of the at least one microchannel, including at least one nanoparticle layer and at least one sublayer on the lower end surface of the at least one nanowall; and At least one guiding channel is provided between adjacent nanowalls; The guiding channel between adjacent nanowalls has a first width, and the thickness of the nanowalls between parallel adjacent nanowalls has a pitch. The first height of the at least one microchannel includes: a second height of the at least one nanowall, a third height of the micropore depth; and The roughness of the at least one nano-scale protrusion layer is greater than the roughness of the at least one wall layer formed on the bottom side of the adjacent guide channel.

2. The nanostructure of laser-surface-treated bone material as described in claim 1, characterized in that, The first width of the guiding channel between adjacent nanowalls is 20 μm to 50 μm, the thickness of the nanowalls between parallel adjacent guiding 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 micropore depth 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 between the at least one micropore is 30 μm to 50 μm.

3. The nanostructure of laser-surface-treated bone material as described in claim 1, characterized in that, The titanium metal is titanium or a titanium alloy, and the microchannel crystal has a rutile crystal structure.

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