CN109316624B - Integrated degradable cartilage connecting suture with needle - Google Patents
Integrated degradable cartilage connecting suture with needle Download PDFInfo
- Publication number
- CN109316624B CN109316624B CN201710641650.8A CN201710641650A CN109316624B CN 109316624 B CN109316624 B CN 109316624B CN 201710641650 A CN201710641650 A CN 201710641650A CN 109316624 B CN109316624 B CN 109316624B
- Authority
- CN
- China
- Prior art keywords
- magnesium
- suture
- based alloy
- needle
- cartilage
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
- A61L17/06—At least partially resorbable materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
- A61L17/14—Post-treatment to improve physical properties
- A61L17/145—Coating
Abstract
The invention provides an integrated degradable cartilage connecting suture with a needle, which aims to solve the problems that cartilage connecting wires in the existing ear reconstruction and other operations need to be taken out in a secondary operation and the like, and comprises a traction needle and a suture, and is characterized in that: the suture is made of magnesium-based alloy wires, the magnesium-based alloy is a two-to five-element alloy, the added alloy elements are one or more of zinc, strontium, zirconium, copper and rare earth elements, and the total content of the alloy elements is less than 5 wt.%. The invention utilizes the characteristics of magnesium-based alloy such as biodegradability and excellent mechanical property, can realize a cartilage connection method without secondary operation, reduces the operation bacterial infection risk while relieving the pain and burden of a patient, and has good application prospect in the aspect of cartilage connection as shown by the experimental result of the implantation of magnesium-based alloy wires in animal bodies.
Description
Technical Field
The invention belongs to the field of medical use, and particularly provides a method for cartilage connection by adopting a degradable magnesium-based alloy wire as a cartilage connecting wire.
Background
The medical connecting wire is a special wire material used for wound suturing, tissue connection and ligation hemostasis, plays a key role in wound healing and repair, and has important significance in effective healing of tissues and recovery of human health. At present, the materials applied to cartilage connection of ear reconstruction and the like are mainly stainless steel wires, stainless steel belongs to non-absorbable materials and is foreign matters in a human body, and adverse reactions such as inflammation, delayed healing, sensitization, carcinogenesis and the like of an organism are easily caused by long-term residence. After the tissue of the body patient is repaired or healed, the patient needs to be taken out by a secondary operation, which brings additional operation risk, economic pressure and physiological pain to the patient. With the increasing economic level and the increasing awareness of people to protect their bodies, the secondary operation is unacceptable. The absorbable connecting line can be degraded and absorbed in the in-vivo biological environment, meets the current advanced medical concept and human body requirements, and is the mainstream and trend of future development. At present, most of absorbable connecting wires are made of high polymer materials, the mechanical strength is low, the absorbable connecting wires are difficult to be suitable for tissue suture with larger tension, and the absorbable connecting wires can only be suitable for a few non-bearing parts, so the development and clinical application of the absorbable connecting wires are limited to a great extent.
The magnesium-based alloy wire can be applied to the cartilage connection in plastic surgery by reasonably adjusting the degradation speed, the mechanical property and the antibacterial property, and the magnesium-based alloy wire has attractive prospect in the aspect of cartilage connection application as a degradable connecting wire. Therefore, aiming at the problem that the existing suture for cartilage connection needs to be taken out by a secondary operation, the invention develops a degradable and absorbable surgical suture with good mechanical property, which can be used for cartilage connection.
Disclosure of Invention
Aiming at the problems that the cartilage connecting wire needs to be taken out in secondary operations in the existing operations such as ear reconstruction and the like, the invention provides the integrated degradable cartilage connecting suture with the needle, which can realize a cartilage connecting method without the secondary operations by utilizing the characteristics of magnesium-based alloy such as biodegradability and excellent mechanical properties.
The technical scheme of the invention is as follows:
the utility model provides an integral type area needle degradable cartilage connection suture, includes traction needle and suture line, its characterized in that: the suture is made of magnesium-based alloy wires, the magnesium-based alloy is a two-to five-element alloy, the added alloy elements are one or more of zinc, strontium, zirconium, copper and rare earth elements, and the total content of the alloy elements is less than 5 wt.%.
When the magnesium-based alloy suture is used, the magnesium-based alloy suture line can penetrate through cartilage tissues and is connected through the traction needle, the wire has good mechanical property, cartilage can be bound and connected, the cartilage is connected in a perforation mode, the magnesium-based alloy suture line has good biological safety, and after the cartilage tissues are connected perfectly, the magnesium-based alloy suture line can be biodegraded and absorbed, so that the magnesium-based alloy suture line is prevented from being taken out in a secondary operation.
The invention relates to a cartilage connecting suture line, which is characterized in that: the diameter of the magnesium-based alloy wire is 0.1-0.5 mm. According to the invention, the alloy elements are added into the pure magnesium, so that the mechanical strength and the processing performance of the pure magnesium are improved, the magnesium alloy wire with the diameter of less than 0.5mm can be prepared, the surface of the wire is smooth and uniform in thickness, and the wire has biodegradability, good mechanical property and excellent biological safety, and can be used as a cartilage connecting wire for effectively connecting cartilage and promoting the healing of bone tissues.
The cartilage connection suture with the needle is characterized in that the magnesium-based alloy is preferably Mg-1.0Zn-0.5Nd-0.8Zr-0.8Cu, Mg-2Zn-0.5Nd or Mg-0.2Zn-2Nd, and the magnesium-based alloy has good wire processing and forming performance and high plasticity.
The cartilage connecting suture with the needle is characterized in that the rare earth element is one or more of neodymium, gadolinium and yttrium elements, and the weight percentage of the rare earth element is as follows: neodymium: 0.2-2.0%, gadolinium: 0.3-0.8%, yttrium: 0.1 to 1.0 percent.
The cartilage connection suture with the needle is characterized in that: the magnesium-based alloy suture line is provided with a surface fluorination treatment layer, the thickness of the magnesium-based alloy suture line is 0.1-2 mu m, and the treatment process is to soak the magnesium-based alloy suture line in hydrofluoric acid for 20-80 h.
The cartilage connecting suture line is characterized in that the preparation method of the magnesium-based alloy suture line comprises the following steps: the magnesium-based alloy wire rod with the diameter of 3-10mm is drawn by a drawing machine, the process of single-pass small deformation and multi-pass drawing is adopted in the drawing process, the necessary annealing heat treatment is used for obtaining the accumulated large deformation, the single-pass 10-20% small deformation is adopted in the drawing process, then the total drawing pass is calculated according to the total deformation and the single-pass deformation, the drawing speed is 0.01-0.25mm/s, and the magnesium-based alloy wire rod with the diameter of 0.1-0.5mm is finally processed.
The cartilage connection suture with the needle is characterized in that the annealing heat treatment has the following process parameters: keeping the temperature at 350 ℃ for 1-5h at 250 ℃ and cooling along with the furnace.
The cartilage connection suture with the needle is characterized in that: the needle head of the traction needle is made of antibacterial or nickel-free stainless steel (preferably antibacterial 2Cr13Cu3 stainless steel), and has the characteristics of high bending strength, good antibacterial effect, easiness in penetrating cartilage tissues and the like.
The cartilage connecting suture line is characterized in that: the needle tail of the traction needle adopts a hollow tube structure, and magnesium-based alloy wires can be inserted into the needle tail and connected into an integrated suture structure with the needle by pressure.
The cartilage connecting suture line is characterized in that: the surface of the magnesium-based alloy wire adopts a barb structure, and the wire can be prevented from knotting after passing through the cartilage.
Compared with the existing stainless steel for cartilage connection suture material, the magnesium-based alloy suture filament has the advantages that the magnesium-based alloy filament replaces a stainless steel wire to connect cartilage tissues, the magnesium-based alloy suture filament can be gradually degraded and disappear in vivo after tissues are healed while the suture effect is achieved, the magnesium-based alloy suture filament is prevented from being taken out after a secondary operation, the pain and burden of a patient are relieved, the risk of operation bacterial infection is reduced, the cell proliferation rate of the magnesium-based alloy on fibroblasts and chondrocytes is more than 90%, the cytotoxicity rating is 1 level, and good biocompatibility is shown. The experimental result of the magnesium-based alloy wire implanted in the animal body shows that the magnesium-based alloy wire has good application prospect in the aspect of cartilage connection.
Drawings
FIG. 1 shows the tensile stress-strain curve and mechanical properties of Mg-Zn-Nd.
FIG. 2 shows the cell compatibility of Mg-Zn-Nd alloy.
Fig. 3 is a macroscopic photograph of cartilage connections and their removal after three months (connecting filament degradation).
Fig. 4 shows the surface topography of the mg-based alloy wire after three months and EDS spectroscopy analysis (a) binding (b) through.
Detailed Description
The following examples illustrate the invention in detail: the present embodiment is implemented on the premise of the technical solution of the present invention, and a detailed implementation manner and a specific operation process are given, but the protection scope of the present invention is not limited to the following embodiments.
Example 1
The magnesium-based alloy wire is made of Mg-Zn-Nd alloy and comprises the following components in percentage by mass: zn: 2.0%, Nd: 0.5 percent and the balance of Mg, which is expressed as Mg-2Zn-0.5Nd and is called ZN20 for short.
Using a well-type crucible resistance furnace at 99.5% CO2+0.5％SF6Under the protective gas of (2), high-purity magnesium ingot (99.99) is putwt.Percent) and high-purity zinc ingot (99.99)wt.Percent) and Mg-30Nd intermediate alloy are melted in an iron crucible according to a given proportion, poured into a graphite crucible with the diameter of 90mm and cooled to form a ZN20 cast ingot. The ingot is subjected to homogenization annealing heat treatment at the temperature of 325 ℃ for 5 h. The ingot with the diameter of 90mm was processed into an ingot with the diameter of 80mm and the length of 150mm, and the ingot was extruded into a rod with the diameter of 10mm on a 460T horizontal extruder. The parameters of the extrusion process are as follows: preheating the ingot at 390 ℃ for 2h, extruding at 390 ℃, extruding at 10mm/s and extruding at a ratio of 64: 1. In order to obtain a bar with a smooth surface, high-temperature grease is uniformly coated on the inner walls of the extrusion female die and the charging barrel, so that friction is reduced, and extrusion deformation of the alloy is facilitated. According to the GB/T228-. ZN20 alloy tensile fracture is composed of dimples with different sizes and is characterized by ductile fracture. The degradation speed of the ZN20 alloy after being soaked in Hank's solution for 14 days is 0.20mm/year, the corrosion appearance is represented by the fact that the alloy is composed of densely distributed shallow and fine corrosion pits, and the macroscopic view is represented by the characteristic of filiform corrosion. Utilizing electrochemical experiments to obtain a polarization curve and an impedance spectrogram of the ZN20 alloy in Hank's solution, and obtaining the ZN20 alloy with the corrosion potential of-1.56 +/-0.03V and the corrosion current of 2.94 +/-0.35 multiplied by 10-6A·cm-2The polarization resistance is 14.5 + -0.50 × 10-3Ohm·cm-2. The ZN20 alloy has a cell proliferation rate of more than 90% on fibroblasts and chondrocytes, and shows good biocompatibility with a cytotoxicity rating of 1 grade.
The ZN20 alloy was drawn by a hydraulic drawing machine with a drawing force of 5T at a drawing speed of 0.01 mm/s. In the drawing deformation, a process of single-pass small deformation and multi-pass drawing is adopted, and a necessary annealing heat treatment is supplemented to obtain a process method of accumulated large deformation, so that extremely high accumulated deformation is obtained, the drawing forming problem of the ZN20 alloy superfine wire is solved, the drawing process of the wire with the diameter from 10mm to 0.1mm is established, and the single-pass deformation is 20%. Finally, the bar with the diameter of 10mm is processed into ZN20 wire with the diameter of 0.3 mm. The surface of the ZN20 wire is subjected to fluorination treatment, the treatment process is that the surface fluoride layer with the thickness of about 0.1 mu m is obtained by soaking the surface of the ZN20 wire in hydrofluoric acid for 72 hours, and the tensile strength of the ZN20 wire is 295MPa, the yield strength is 205MPa, and the elongation is 13.8%.
ZN20 wire with the diameter of 0.3mm is implanted into the subcutaneous tissues of mice, x-ray film observation for 30 days and 45 days can find that ZN20 metal is deposited in the mice, the deposited metal disappears by metabolism absorption along with the time, and the activity and the food intake of the mice after the operation are normal, which shows that ZN20 alloy still has good biocompatibility in the bodies of animals. ZN20 wire material is implanted into Panama miniature pig to carry out cartilage connection experiment, two cartilages are taken out from the end of the miniature pig rib, the ZN20 wire material is used for connecting by two modes of binding the cartilages and penetrating the inner part of the cartilages, and clinically common stainless steel wire is selected as a control group. After three months, the cartilage is taken out, all the cartilage is normally connected, the ZN20 wire is intact, not completely degraded and not broken, an SEM electron microscope shows that the ZN20 wire penetrating through the cartilage is degraded more, the surface of the wire is covered with a layer of corrosion products, and transverse cracks exist; while the wires subjected to the bond joint corroded relatively lightly and no significant cracks were found on the surface, as shown in FIG. 4. Therefore, animal experiments show that the ZN20 alloy wire can be used as a connecting wire for ear reconstruction surgery to effectively connect broken cartilages, the wire material is not completely degraded after being implanted for 3 months, and the stainless steel wire of a control group is not degraded.
Example 2
The magnesium-based alloy wire is made of Mg-Zn-Nd alloy and comprises the following components in percentage by mass: zn: 0.2%, Nd: 2.0 percent and the balance of Mg, namely Mg-0.2Zn-2Nd, which is called NZ20 for short.
Using a well-type crucible resistance furnace at 99.5% CO2+0.5％SF6Under the protective gas of (2), melting a high-purity magnesium ingot (99.99 wt.%), a high-purity zinc ingot (99.99 wt.%), and a Mg-30Nd intermediate alloy in a predetermined ratio in an iron crucible, pouring the molten Mg into a graphite crucible with a diameter of 90mm, and cooling to form an NZ20 ingot. Adopting a homogenization heat treatment process: and carrying out homogenization annealing on the ingot at 300 ℃ for 2 h. An ingot having a diameter of 90mm was processed into an ingot having a diameter of 83mm and a length of 150mm, and the ingot was extruded into a rod having a diameter of 10mm on a 460T horizontal extruder. The parameters of the extrusion process are as follows: preheating the ingot at 390 ℃ for 2h, extruding at 390 ℃, extruding at 10mm/s and extruding at a ratio of 64: 1. In order to obtain a bar with a smooth surface, high-temperature grease is uniformly coated on the inner walls of the extrusion female die and the charging barrel, so that friction is reduced, and extrusion deformation of the alloy is facilitated. According to the GB/T228-. The NZ20 alloy tensile fracture is dimple-shaped and is characterized by ductile fracture. The degradation speed of the NZ20 alloy after being soaked in Hank's solution for 14 days is 0.23mm/year, and the corrosion morphology is composed of fine corrosion pits. Utilizing electrochemical experiments to obtain a polarization curve and an impedance spectrogram of the NZ20 alloy in Hank's solution, and obtaining the NZ20 alloy with the corrosion potential of-1.58 +/-0.03V and the corrosion current of 6.10 +/-0.52 multiplied by 10-6A·cm-2The polarization resistance is 7.45 +/-0.32 multiplied by 10-3Ohm·cm-2. The NZ20 alloy has a cell proliferation rate of more than 90% on fibroblasts and chondrocytes, and has a cytotoxicity rating of 1 grade, and shows good biocompatibility.
The NZ20 alloy was drawn by a hydraulic drawing machine with a 5T drawing speed of 0.03 mm/s. In the drawing deformation, a process of single-pass small deformation and multi-pass drawing is adopted, and a necessary annealing heat treatment is supplemented to obtain a process method of accumulated large deformation, so that extremely high accumulated deformation is obtained, the drawing forming problem of the ZN20 alloy superfine wire can be solved, the drawing process of the wire with the diameter from 10mm to 0.1mm is established, and the single-pass deformation is 20%. Finally, a bar with a diameter of 10mm is processed into an NZ20 wire with a diameter of 0.25 mm. The NZ20 wire had a tensile strength of 245MPa, a yield strength of 165MPa and an elongation of 19.9%. Soaking the NZ20 wire material in hydrofluoric acid for 62h to obtain a surface fluoride layer with the thickness of about 0.1 μm.
The NZ20 wire material is implanted into a Panama miniature pig to perform a cartilage connection experiment, two cartilages are taken out from the tail end of a miniature pig rib, the NZ20 wire material is used for connecting the cartilages in a mode of binding the cartilages and penetrating the cartilages, and a clinically common stainless steel wire is selected as a control group. After three months, the cartilage is taken out, all the cartilage is normally connected, the NZ20 wire is intact, not completely degraded and not broken, an SEM electron microscope shows that the NZ20 wire penetrating through the cartilage is degraded more, the surface of the NZ20 wire is covered with a layer of corrosion products, and transverse cracks are formed; while the wires subjected to the bond joint corroded relatively lightly and no significant cracks were found on the surface, as shown in FIG. 4. Therefore, animal experiments show that the NZ20 alloy wire can be effectively used as a connecting wire for ear reconstruction surgery to connect broken cartilages, the wire material is degraded by 20% after being implanted for 3 months, and the stainless steel wire of a control group is not degraded.
Example 3
The magnesium-based alloy wire is prepared from Mg-Zn-Sr-Zr alloy, and comprises the following components in percentage by mass: zn: 0.5%, Sr: 1.0%, Zr 0.5%, and the balance Mg, which is Mg-0.5Zn-Sr-0.5 Zr. The preparation process of the alloy is the same as that of the embodiment 1, and according to the GB/T228-. The degradation rate of the alloy after soaking in Hank's solution for 14 days is 0.25 mm/year. The cell proliferation rate of the alloy on fibroblasts and chondrocytes is more than 90%, the cytotoxicity rating is 1 grade, and the alloy shows good biocompatibility.
The Mg-0.5Zn-Sr-0.5Zr wire was produced in the same manner as in example 1, and had a diameter of 0.28mm, a tensile strength of 275MPa, a yield strength of 165MPa and an elongation of 12.3%. The wire was immersed in hydrofluoric acid for 62h to obtain a surface fluoride layer having a thickness of about 0.1 μm.
Animal experiments show that the Mg-0.5Zn-Sr-0.5Zr wire can bind cartilage and penetrate through the cartilage for connection. After three months of operation, all cartilages are normally connected, and animal experiments show that the wire can be effectively connected with broken cartilages as a connecting wire for ear reconstruction surgery, the wire is degraded by 16% after being implanted for 3 months, and the stainless steel wire of a control group is not degraded.
Example 4
The magnesium-based alloy wire is made of Mg-Sr alloy, and the mass percentage of Sr: 0.8 percent, and the balance being Mg, which is expressed as Mg-0.8 Sr. The preparation process of the alloy is the same as that of the embodiment 2, and according to the GB/T228-. The degradation rate of the alloy after soaking in Hank's solution for 14 days is 0.20 mm/year. The cell proliferation rate of the alloy on fibroblasts and chondrocytes is more than 90%, the cytotoxicity rating is 1 grade, and the alloy shows good biocompatibility.
The Mg-0.8Sr wire was produced in the same manner as in example 2, and the wire had a diameter of 0.3mm, a tensile strength of 232MPa, a yield strength of 122MPa and an elongation of 9.3%. The wire was immersed in hydrofluoric acid for 72 hours to obtain a surface fluoride layer having a thickness of about 0.1 μm.
Animal experiments show that the Mg-0.8Sr wire can bind cartilage and connect cartilage through the inside of cartilage. After three months of operation, all cartilages are normally connected, and animal experiments show that the wire can be effectively connected with broken cartilages as a connecting wire for ear reconstruction surgery, the wire is degraded by 18% after being implanted for 3 months, and the stainless steel wire of a control group is not degraded.
Example 5
The magnesium-based alloy wire is made of Mg-Zn-Nd-Zr-Cu alloy, and the mass percentage of the Mg-based alloy wire is as follows: 1.0%, Nd: 0.5 percent of Zr, 0.8 percent of Cu and the balance of Mg. The preparation process of the alloy is the same as that of the embodiment 1, and the tensile strength of the Mg-Zn-Nd-Zr-Cu alloy is 284MPa, the yield strength is 139MPa, the elongation is 25.9 percent and the reduction of area is 40.1 percent according to the GB/T228-. The degradation rate of the alloy after soaking in Hank's solution for 14 days is 0.18 mm/year. The cell proliferation rate of the alloy on fibroblasts and chondrocytes is more than 90%, the cytotoxicity rating is 1 grade, and the alloy has good biocompatibility.
The Mg-Zn-Nd-Zr-Cu wire was produced in the same manner as in example 1, and had a tensile strength of 301MPa, a yield strength of 140MPa and an elongation of 8.6% for a wire diameter of 0.20 mm. The wire was immersed in hydrofluoric acid for 72 hours to obtain a surface fluoride layer having a thickness of about 0.1 μm.
Animal experiments show that the Mg-Zn-Nd-Zr-Cu wire can bind cartilage and penetrate through the inside of the cartilage for connection. After three months of operation, all cartilages are normally connected, and animal experiments show that the wire can be effectively connected with broken cartilages as a connecting wire for ear reconstruction surgery, the wire is degraded by 23% after being implanted for 3 months, and the stainless steel wire of a control group is not degraded.
Example 6
The magnesium-based alloy wire is prepared from Mg-Gd-Zr-Y alloy, and the mass percentage of Gd: 0.8 percent of Zr, 0.8 percent of Y and the balance of Mg. The preparation process of the alloy is the same as that of the embodiment 1, and according to the GB/T228-. The degradation rate of the alloy after soaking in Hank's solution for 14 days is 0.19 mm/year. The cell proliferation rate of the alloy on fibroblasts and chondrocytes is more than 90%, the cytotoxicity rating is 1 grade, and the alloy has good biocompatibility.
The Mg-Gd-Zr-Y wire was produced in the same manner as in example 1, and the wire having a diameter of 0.30mm had a tensile strength of 286.1MPa, a yield strength of 154.2MPa and an elongation of 9.7%. And soaking the wire in hydrofluoric acid for 80h to obtain a surface fluoride layer with the thickness of about 0.1 mu m.
Animal experiments show that the Mg-Gd-Zr-Y wire can bind the cartilage and penetrate through the inner part of the cartilage for connection. After three months of operation, all cartilages are normally connected, and animal experiments show that the wire can be effectively connected with broken cartilages as a connecting wire for ear reconstruction surgery, the wire is degraded by 24.0% after being implanted for 3 months, and the stainless steel wire of a control group is not degraded.
The above embodiments are merely illustrative of the technical ideas and features of the present invention, and the purpose thereof is to enable those skilled in the art to understand the contents of the present invention and implement the present invention, and not to limit the protection scope of the present invention. All equivalent changes and modifications made according to the spirit of the present invention should be covered within the protection scope of the present invention.
Claims (8)
1. The utility model provides an integral type area needle degradable cartilage connection suture, includes traction needle and suture line, its characterized in that: the suture is made of magnesium-based alloy wires, the magnesium-based alloy is a two-to five-element alloy, the added alloy elements are one or more of zinc, strontium, zirconium, copper and rare earth elements, and the total content of the alloy elements is less than 5 wt.%; the rare earth element is one or more of neodymium, gadolinium and yttrium, and the rare earth element comprises the following components in percentage by weight: neodymium: 0.2-2.0%, gadolinium: 0.3-0.8%, yttrium: 0.1 to 1.0 percent;
the magnesium-based alloy suture line is provided with a surface fluorination treatment layer, the thickness of the magnesium-based alloy suture line is 0.1-2 mu m, and the treatment process is to soak the magnesium-based alloy suture line in hydrofluoric acid for 20-80 h.
2. The integrated degradable cartilage suture with needle according to claim 1, wherein: the diameter of the magnesium-based alloy wire is 0.1-0.5 mm.
3. The integrated degradable cartilage suture with needle according to claim 1, wherein: the magnesium-based alloy is Mg-1.0Zn-0.5Nd-0.8Zr-0.8Cu, Mg-2Zn-0.5Nd or Mg-0.2Zn-2 Nd.
4. The integrated degradable cartilage connecting suture with the needle according to claim 1, wherein the magnesium-based alloy wire is prepared by the following steps: the magnesium-based alloy wire rod with the diameter of 3-10mm is drawn by a drawing machine, the single-pass deformation amount of 10-20% is adopted in the drawing process, then the total drawing pass is calculated according to the total deformation amount and the single-pass deformation amount, the necessary annealing heat treatment is assisted to obtain the process method of accumulating large deformation amount, the drawing speed is 0.01-0.25mm/s, and the magnesium-based alloy wire rod with the diameter of 0.1-0.5mm is finally processed.
5. The integrated degradable cartilage connecting suture with the needle according to claim 4 is characterized in that the annealing heat treatment has the following process parameters: keeping the temperature at 350 ℃ for 1-5h at 250 ℃ and cooling along with the furnace.
6. The integrated degradable cartilage suture with needle according to claim 1, wherein: the needle head of the traction needle adopts antibacterial 2Cr13Cu3 stainless steel.
7. The integrated degradable cartilage suture with needle according to claim 1, wherein: the needle tail of the traction needle adopts a hollow tube structure, and magnesium-based alloy wires can be inserted into the needle tail and connected into an integrated suture structure with the needle by pressure.
8. The integrated degradable cartilage suture with needle according to claim 1, wherein: the surface of the magnesium-based alloy wire adopts a barb structure.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710641650.8A CN109316624B (en) | 2017-07-31 | 2017-07-31 | Integrated degradable cartilage connecting suture with needle |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710641650.8A CN109316624B (en) | 2017-07-31 | 2017-07-31 | Integrated degradable cartilage connecting suture with needle |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN109316624A CN109316624A (en) | 2019-02-12 |
| CN109316624B true CN109316624B (en) | 2021-07-02 |
Family
ID=65245021
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201710641650.8A Active CN109316624B (en) | 2017-07-31 | 2017-07-31 | Integrated degradable cartilage connecting suture with needle |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109316624B (en) |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP1618901A1 (en) * | 2004-07-23 | 2006-01-25 | Biotronik VI Patent AG | Biokompatible and biodegradable suture and staple material for surgical use |
| CN101773402A (en) * | 2002-09-30 | 2010-07-14 | 奎尔医疗公司 | The barb configuration that the sutures of barb is arranged |
| CN101909528A (en) * | 2007-12-27 | 2010-12-08 | 马尼株式会社 | Medical suture needle |
| CN104451303A (en) * | 2014-12-03 | 2015-03-25 | 东南大学 | Biomedical magnesium alloy and preparation method and application of biomedical magnesium alloy wire |
| CN104511048A (en) * | 2013-09-27 | 2015-04-15 | 上海交通大学医学院附属第九人民医院 | Degradable metal antibacterial suture |
| CN104784750A (en) * | 2015-04-03 | 2015-07-22 | 中国科学院金属研究所 | Surface modification method for improving corrosion resistance of deformable biomedical magnesium alloy implantable device |
-
2017
- 2017-07-31 CN CN201710641650.8A patent/CN109316624B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101773402A (en) * | 2002-09-30 | 2010-07-14 | 奎尔医疗公司 | The barb configuration that the sutures of barb is arranged |
| EP1618901A1 (en) * | 2004-07-23 | 2006-01-25 | Biotronik VI Patent AG | Biokompatible and biodegradable suture and staple material for surgical use |
| CN101909528A (en) * | 2007-12-27 | 2010-12-08 | 马尼株式会社 | Medical suture needle |
| CN104511048A (en) * | 2013-09-27 | 2015-04-15 | 上海交通大学医学院附属第九人民医院 | Degradable metal antibacterial suture |
| CN104451303A (en) * | 2014-12-03 | 2015-03-25 | 东南大学 | Biomedical magnesium alloy and preparation method and application of biomedical magnesium alloy wire |
| CN104784750A (en) * | 2015-04-03 | 2015-07-22 | 中国科学院金属研究所 | Surface modification method for improving corrosion resistance of deformable biomedical magnesium alloy implantable device |
Non-Patent Citations (1)
| Title |
|---|
| 挤压态Mg-Zn-Nd医用镁合金的组织与性能研究;李军雷等;《中国医疗设备》;20150930;第30卷(第09期);第6-7页"0 前言"章节和表1、第8-10页"2.2 挤压态Mg-Zn-Nd合金的力学性能"、"2.3 挤压态Mg-Zn-Nd合金的降解性能"章节和表2 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN109316624A (en) | 2019-02-12 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101899600B (en) | Osteopathic magnesium alloy interstitial implant material and preparation method thereof | |
| EP2764130B1 (en) | Biodegradable metal alloys | |
| CN103184379B (en) | Biodegradable Mg-Gd-Zn-Ag-Zr series magnesium alloy and preparation method thereof | |
| CN101658691B (en) | Method for plastically manufacturing high-purity magnesium alloy absorbable stent | |
| CN107557632B (en) | Degradable biomedical Mg-Zn-Zr-Nd alloy material and preparation method thereof | |
| EP2213314B1 (en) | Implant with a base body of a biocorrodible magnesium alloy | |
| WO2011160534A1 (en) | Magnesium alloy used for degradable stent material in vivo and preparation method thereof | |
| CN104498790A (en) | Degradable magnesium alloy bio-implantation material and preparation method thereof | |
| CN111424202B (en) | Degradable magnesium alloy in-situ composite anastomosis nail and preparation method thereof | |
| CN104630587A (en) | Degradable magnesium alloy plate and bar for fracture internal fixation and preparation methods thereof | |
| CN104328312A (en) | Medical biodegradable zinc alloy and preparation method thereof | |
| CN104120320A (en) | Degradable rare earth magnesium alloy medical biomaterial and preparation method thereof | |
| CN102258806B (en) | Degradable magnesium-base biomedical material for implantation in orthopaedics, and preparation method thereof | |
| CN101264339A (en) | Magnesium alloy bone surgery internal fixation and implantation material | |
| CN107736906A (en) | A kind of Absorbale magnesium alloy skin closure nail and preparation method thereof | |
| CN109602960B (en) | Preparation method of medical zinc alloy bar with superplasticity | |
| CN105087980A (en) | Method for preparing hemostatic clips through surface-passivated degradable magnesium alloy | |
| CN107198796B (en) | Biomedical Zn-Mn-Cu zinc alloy and preparation method thereof | |
| CN111826564A (en) | Absorbable magnesium alloy cosmetic line and preparation method thereof | |
| CN103184380A (en) | Biodegradable Mg-Gd-Zn-Ag-Zr series magnesium alloy and preparation method thereof | |
| CN105803282B (en) | A kind of single-phase Multielement rare-earth magnesium alloy biodegradation material and preparation method thereof | |
| CN114074129B (en) | Preparation method of magnesium alloy wire used as implant material | |
| CN112355586B (en) | Preparation method of degradable double-layer biological magnesium alloy | |
| CN109316624B (en) | Integrated degradable cartilage connecting suture with needle | |
| CN104846247A (en) | Magnesium alloy biodegradable material added with gadolinium and yttrium and preparing method thereof |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |