WO2022242270A1

WO2022242270A1 - Method for fine machining of surgical instrument

Info

Publication number: WO2022242270A1
Application number: PCT/CN2022/078870
Authority: WO
Inventors: 底月兰; 王力; 王海斗; 梁俊容; 邢志国; 黄艳斐; 韩敏娜
Original assignee: 中国人民解放军陆军装甲兵学院
Priority date: 2021-05-18
Filing date: 2022-03-02
Publication date: 2022-11-24
Also published as: CN113996942A

Abstract

A method for fine machining of a surgical instrument. The method comprises forming strip-shaped groove microstructures in the surface of the surgical instrument by means of laser etching. A bacteriostatic surface having bacteriostatic properties is formed on the surgical instrument. The bacteriostatic surface is a change of physical appearance formed on the surface of the surgical instrument, and the bacteriostatic properties do not depend on any bacteriostatic element, thus the bacteriostatic effect is more stable, durable, safe and effective.

Description

Method for fine machining surgical instruments

technical field

The present disclosure relates to the field of medical instruments, and in particular, the present disclosure relates to a method for finely processing surgical instruments.

Background technique

Stainless steel is a widely used base material for medical devices, and currently more than 80% of stent materials are made of stainless steel. The antibacterial effect on the surface of stainless steel materials of existing medical devices is mainly achieved through the action of components: one is to add antibacterial metal elements to the stainless steel matrix as a whole, and after heat treatment, the precipitates with antibacterial effects are uniformly dispersed in the stainless steel; Antibacterial films such as silver and _TiO2 are deposited to make the surface have antibacterial properties. Although these two methods have certain antibacterial effects, there is no unified conclusion on the interaction mechanism between antibacterial metal elements and bacteria, and the precipitation of metals will also have certain toxicity to the human body. In addition, due to the thin antibacterial film on the surface, generally less than 100nm, it is easy to wear during use, which greatly affects the antibacterial performance. The surface of materials treated in this way does not have antibacterial properties, and the antibacterial properties are achieved through the surface component elements. Once the components are removed, they will not have antibacterial effect, so they will not have permanent antibacterial properties.

Therefore, the antibacterial properties of medical devices need to be further improved.

Contents of the invention

The present disclosure aims to solve one of the technical problems in the related art at least to a certain extent. For this reason, an object of the present disclosure is to propose a method for finely processing surgical instruments, which combines laser etching with surgical instruments, and successfully forms bacteriostatic Surface, the bacteriostatic surface is a change in the physical shape formed on the surface of the surgical instrument, so the bacteriostatic performance does not depend on any bacteriostatic elements, and the bacteriostatic effect is more stable, durable, safe and effective. In addition, the adoption of the method can also significantly improve the antibacterial properties and easy-to-clean properties of surgical instruments, improve cleaning efficiency, and reduce costs.

According to one aspect of the present disclosure, the present disclosure proposes a method for finely processing a surgical instrument, the method comprising forming a microstructure of strip grooves on the surface of the surgical instrument by laser etching.

Therefore, the present disclosure combines laser etching with surgical instruments to produce strip-shaped grooves on the surgical instruments, thereby making the surgical instruments have hydrophobic, hemophobic properties, anti-bacterial adhesion, and anti-protein adhesion , anti-platelet adhesion and good performance in inhibiting biofilm growth. Therefore, the surgical instrument has the advantages of easy cleaning and high disinfection efficiency.

In addition, the method for finely processing surgical instruments according to the above-mentioned embodiments of the present disclosure may also have the following additional technical features:

In some embodiments of the present disclosure, nanosecond pulse laser is used for the laser etching.

In some embodiments of the present disclosure, the parameters of using the nanosecond pulsed laser for etching include: power 20w, scanning speed 600mm/s, frequency 20KHz, number of scans 10 or 20 times, scanning distance 60 microns-150 microns . Thus, grooves of predetermined size can be efficiently etched on the surgical instrument.

In some embodiments of the present disclosure, the scanning pitch is 60 microns, 90 microns, 120 microns or 150 microns.

In some embodiments of the present disclosure, the microstructure is a plurality of parallel grooves.

In some embodiments of the present disclosure, each of the plurality of parallel grooves has a width of 40 microns to 60 microns and a depth of 60 microns to 70 microns. The thus formed surface (antibacterial surface) with the microstructure has superhydrophobic and superhemophobic properties as well as good properties of anti-protein adhesion, anti-platelet adhesion and inhibition of biofilm growth.

In some embodiments of the present disclosure, each of the plurality of parallel grooves has a width of 60 microns, 90 microns, 120 microns or 150 microns, and a depth of 20 microns to 50 microns.

In some embodiments of the present disclosure, the method further includes: using a chemical modification method to perform low surface energy modification on the surface of the microstructure, so as to form a self-cleaning surface. Thus, the bacteriostatic effect of the bacteriostatic surface can be further improved.

In some embodiments of the present disclosure, the chemical modification method includes: using absolute ethanol to clean the surface of the surgical instrument forming the microstructure, and then soaking the surface of the surgical instrument in 5 mmol/L PFDTES methanol solution for 10 hours, and placed in a constant temperature blast drying oven at 150°C for 1 hour to solidify, then took it out and allowed it to cool.

In some embodiments of the present disclosure, the surface having the microstructure has super-hydrophobic properties and super-plasma-repellent properties.

In some embodiments of the present disclosure, the surface having the microstructure has anti-bacterial adhesion properties, anti-biofilm growth properties, anti-protein adhesion properties and anti-platelet adhesion properties.

In some embodiments of the present disclosure, the bacteriostatic rate of the surface having the microstructure is not lower than 40%.

Description of drawings

FIG. 1 is a diagram of a stainless steel sample used in Example 1 of the present disclosure.

FIG. 2 is a strip groove microstructure according to an embodiment of the present disclosure.

3 is a three-dimensional topography diagram of the microstructure of strip grooves obtained by etching under conditions of multiple scanning pitches and two scanning times in Example 1 of the present disclosure (microscope lens: 10×)

FIG. 4 is an SEM image of the strip groove microstructure etched under the conditions of multiple scanning pitches and 10 scans in Example 1 of the present disclosure.

FIG. 5 is an SEM image of the strip-shaped groove microstructure etched under the conditions of multiple scanning pitches and 20 scans in Example 1 of the present disclosure.

Fig. 6 is a schematic diagram of measurement of static contact angle and rolling angle in Example 2 of the present disclosure.

Fig. 7 is a diagram of sterilization-pair-adhesion culture of the Escherichia coli adhesion test sample in Example 3 of the present disclosure.

Fig. 8 is the plate counting result of the E. coli adhesion test in Example 3 of the present disclosure.

Fig. 9 is a diagram of sterilization-pair culture of Escherichia coli biofilm experimental samples in Example 4 of the present disclosure.

Fig. 10 is a laser confocal microscope observation view (1000×) in Example 4 of the present disclosure.

Fig. 11 is an EDS energy spectrum analysis diagram of sample 5 (G) and control sample (K) in Example 5 of the present disclosure: including 11-G and 11-K.

Figure 12 is the protein adhesion SEM images of sample 5 (G) and control sample (K) in Example 5 of the present disclosure: including 12-500×, 12-1000×, 12-2000×, 12-5000×.

Fig. 13 is an optical metallographic microscope image of protein adhesion on the surface of sample 5 (G) and control sample (K) in Example 5 of the present disclosure.

Fig. 14 is an SEM image of platelet adhesion on the surface of sample 5 (G) and control sample (K) in Example 6 of the present disclosure: including 14-1, 14-2, and 14-3.

Detailed ways

Embodiments of the present disclosure will be described in detail below, and the embodiments described below are exemplary and intended to explain the present disclosure, and should not be construed as limiting the present disclosure.

According to one aspect of the present disclosure, the present disclosure proposes a method of finishing a surgical instrument using laser etching to form a bacteriostatic surface on the surgical instrument. According to a specific embodiment of the present disclosure, the method includes forming a strip-shaped groove on the surgical instrument by laser etching. Therefore, the present disclosure combines laser etching with surgical instruments to produce strip-shaped grooves on the surgical instruments, thereby making the surgical instruments have hydrophobic, hemophobic properties, anti-bacterial adhesion, and anti-protein adhesion , anti-platelet adhesion and good performance in inhibiting biofilm growth. Therefore, the surgical instrument has the advantages of easy cleaning and high disinfection efficiency.

In the present disclosure, it is a new idea to change the microstructure of the surface of the surgical instrument by laser etching so that it has antibacterial effect. Specifically, the laser etching technology uses pulsed laser to act on the surface of surgical instruments, and prepares strip grooves as shown in Figure 2 on the surface, thereby changing the wettability of the material surface to reduce or even inhibit bacterial adhesion. Effect.

According to a specific embodiment of the present disclosure, the laser etching of the present disclosure adopts nanosecond pulse laser. The inventors found that the microstructure obtained by etching with nanosecond pulsed laser can achieve the effect of inhibiting or reducing bacterial adhesion, and nanosecond pulsed laser is more cost-effective than micron laser, and the etching efficiency is higher.

According to a specific embodiment of the present disclosure, the parameter setting for etching by nanosecond laser includes: the etching power is 20w, the scanning speed is 600mm/s, the frequency is 20KHz, and the number of scanning is 10 times. Therefore, grooves of a predetermined size can be effectively etched on the surgical instrument under the conditions of the nanosecond laser etching, thereby making it capable of inhibiting or reducing bacterial adhesion. In addition, the inventors found that the number of scans directly affects the depth of etched grooves. If the number of scans is too high, the groove depth will be too deep, which will reduce the superhydrophobic and superhemophobic properties of the microstructure. By further optimizing the number of scans, it is found that the number of scans is 10 times, and the depth of the etched trench is 60 microns to 70 microns.

According to a specific embodiment of the present disclosure, the scanning pitch may be 60 microns, 90 microns, 120 microns, or 150 microns. Therefore, in the strip-shaped grooves etched under the scan spacing, the distance between the grooves is appropriate, which can endow the microstructure surface with strong superhydrophobic and superhemophobic properties. In addition, the inventors found through further research that the strip groove also has anti-bacterial adhesion properties, anti-biofilm growth properties, anti-protein adhesion properties and anti-platelet adhesion properties.

According to specific embodiments of the present disclosure, the inventors found that the shape of the microstructure etched by nanosecond laser directly affects the antibacterial effect, specifically, the microstructure with strip grooves has the best antibacterial effect.

According to a specific embodiment of the present disclosure, if the etched microstructure is a plurality of parallel grooves, the size after etching may be that the width of each of the plurality of parallel grooves is 40 microns-60 microns, and the depth is 60 microns - 70 microns. The thus formed surface (antibacterial surface) with this microstructure has superhydrophobic and superhemophobic properties, as well as good properties of anti-protein adhesion, anti-platelet adhesion and inhibition of biofilm growth. According to a specific example of the present disclosure, each of the plurality of parallel grooves may have a width of 60 microns, 90 microns, 120 microns or 150 microns, and a depth of 20 microns-50 microns. According to a specific embodiment of the present disclosure, the antibacterial rate of the surface with the microstructure of the above-mentioned size (ie antibacterial surface) is not lower than 40%. Specifically, compared with the surface without any microstructure etched, the antibacterial surface with the above-mentioned strip-shaped groove microstructures had a 39.4% higher ability to inhibit the adhesion of E. coli.

According to another embodiment of the present disclosure, the method for finely processing surgical instruments in the above embodiment further includes: using a chemical modification method to modify the surface of the microstructure with low surface energy, thereby further improving the antibacterial surface bacteria effect.

According to a specific embodiment of the present disclosure, the chemical modification method includes: using absolute ethanol to clean the surface of the surgical instrument forming the microstructure, and then immersing the surface of the surgical instrument in a 5 mmol/L methanol solution of PFDTES 10 hours, and placed in a constant temperature blast drying oven at 150 ° C for 1 hour to solidify, take it out and wait for it to cool. Through chemical modification, the surface of surgical instruments after laser processing can quickly reach a superhydrophobic state, and then quickly achieve antibacterial and hemophobic properties. In addition, chemical modification also has the advantages of simple handling and convenient operation.

Therefore, the surface (bacteriostatic surface) with the microstructure on the surgical instrument in the above-mentioned embodiments of the present disclosure has super-hydrophobic and super-plasma-repellent properties. Therefore, when the used surgical instrument is stained with blood, it is easy to remove the blood as long as simple alcohol disinfection is performed. In turn, the cleaning efficiency of the surgical instrument is significantly improved.

In addition, the inventors evaluated the microstructure antibacterial surface prepared by the above method, and found that the antibacterial surface also has antibacterial adhesion properties, anti-biofilm growth properties, anti-protein adhesion properties and anti-platelet adhesion properties. Due to its anti-bacterial adhesion properties, it can significantly reduce the risk of cross-infection, and its anti-protein adhesion properties and anti-platelet adhesion properties can make it difficult for the surgical instrument (such as a surgical scalpel) to cut skin or tissue. Adhesive tissue and blood, etc., can improve the sharpness and ease of operation of surgical instruments.

Embodiment 1 (preparation antibacterial surface)

(1) Material selection

This experiment uses martensitic 3Cr13 stainless steel, which has a high carbon content and exhibits high strength, hardness and wear resistance. It is often used as a material for medical devices such as surgical knives. A 10mm×10mm×1mm stainless steel sample (Figure 1) was used in the experiment, and the detailed composition is shown in Table 1.

Table 1 Composition list of 3Cr13

(2) Laser scanning etching

Firstly, the processed original sample was polished, and then the polished sample was immersed in absolute ethanol for ultrasonic cleaning for 5 minutes and dried.

The surface of the substrate is textured by a nanosecond fiber pulse laser (Lajamin Laser, LJM-50D-Ⅲ) (the laser wavelength is 1064nm, the pulse duration is about 100ns, the repetition rate is 20kHz, the focal length is 224mm, and the maximum processing range is 110mm×110mm. Focus spot diameter is 60 μm), irradiate the pretreated sample with laser, adjust the laser parameters, and etch the strip groove structure as shown in Fig. 2 .

The laser processing parameters in this experiment are: power 20w, scanning speed 600mm/s, frequency 20KHz, and scanning intervals of 60μm, 90μm, 120μm, and 150μm respectively. two samples. After laser treatment, ultrasonic cleaning with absolute ethanol for 10 minutes and drying to remove surface impurities and oil stains.

(3) Low surface energy modification

The initial samples prepared above were cleaned with five pairs of samples, and then soaked in 5mmol/L PFDTES (1H,1H,2H,2H-perfluorodecyltriethoxysilane) methanol solution for 10 hours, and then used DH -101-2BS type electric constant temperature blast drying oven, solidify at 150°C for 1 hour, take it out and let it cool down.

(4) Surface morphology analysis

With the increase of the scanning interval, the distance between the grooves also increases, and the depth and width of the groove remain basically stable; In the case of , the depth of the groove increases significantly, but the width does not change significantly, indicating that the number of scans has a direct impact on the depth of the groove, as shown in Figures 3-5. According to the scanning electron microscope Figure 4 and Figure 5, it can be seen that in laser scanning etching, the surface material is instantly melted and sputtered to the surface of the material due to the high-energy laser irradiation, and finally cooled and re-melted in the edges and grooves. The sample after laser processing forms a stable and regular micron-scale array structure.

Embodiment 2 (human plasma wettability experiment)

(1) Evaluation method:

Measure the static contact angle and rolling angle of water and PRP (platelet-rich plasma) on the sample 5 prepared in Example 1 with a spacing of 90 μm and a scan frequency of 10 times, and measure the average value for three times, which is used for measuring the contact angle and rolling angle The volume of PRP (platelet rich plasma) is 10 μL. The diagram of the measurement method is shown in Figure 6.

(2) Results and conclusions:

Table 2 Measurement results of contact angle and rolling angle

It can be drawn from Table 2 that the water contact angle of sample 3-sample 10 is in the range of 147.1°-152.4°; the water rolling angle is in the range of 1°-8.5°, and the PRP contact angle of sample 5 is in the range of 151.9°; The PRP roll angle is in the range of 7.6°. It can be explained that sample 5 has superhydrophobic and superhemophobic properties. By comparing the samples with 20 scans and 10 scans, it is found that the sample with 10 scans has better wetting performance. Therefore, the sample with 10 scans not only has better superhydrophobic performance, but also can greatly shorten the processing time by 50%, thereby greatly improving the efficiency of production. Under the condition that the number of scans is 10 times, the effect of the scan distance on the surface wetting properties of the material is explored. The experimental results show that when the scanning distance of sample 5 is 90 μm, the wetting performance of the material surface is the best, the static contact angle is 152.4°, and the rolling angle is 1°. In addition, in order to explore the hydrophobic performance of the superhydrophobic material surface, the contact angle and rolling angle of platelet-rich plasma were measured on the surface of sample 5 with the best hydrophobic performance. The experimental results show that: when the plasma volume is 10 μL, the static contact angle of plasma on the sample surface is 151.9°; the rolling angle is 7.6°. Therefore, under the processing conditions of a scanning interval of 90 μm and a scanning frequency of 10 times, sample 5 not only possesses superhydrophobic properties, but also possesses superhydrophobic properties. Therefore, under the dual requirements of high efficiency and superhydrophobic performance and superhemophobic performance, it is considered that the scanning interval is 90 microns, and the number of scanning times is 10 times as the optimal etching conditions. However, when the scanning distance is too narrow (60 microns) or too wide (90 microns-150 microns, that is, greater than 90 microns and less than or equal to 150 microns), it will affect the superhydrophobic and super-hemophobic properties of the surface, and the number of scans is too many (20 times) will lead to low etching efficiency.

Embodiment 3 (Escherichia coli adhesion test)

(1) Evaluation method:

Test samples: sample 5 (G) prepared in Example 1 (only the experiment of sample 5 was carried out) and a control sample (K) not subjected to laser etching.

Method: When carrying out the E. coli adhesion test, first sterilize the surface of each sample with 75% alcohol and dry it naturally in a sterile biological safety cabinet. In order to test the sterilization of the sample surface, the air-dried sample Adhesive to the medium, and then put the adhered medium into a 37°C constant temperature biochemical incubator for overnight cultivation; then put the samples into sterile 24-well plates and add them to the well plates containing the samples OD600=0.6 bacterial PBS suspension 1mL, let it stand for 5 minutes, then suck out the bacterial solution, and then wash it three times with sterile PBS solution to clean the non-adhered E. coli; put the washed sample into a 3mL sterile In the centrifuge tube of bacteria PBS solution, ultrasonically oscillate for 30 minutes, dilute the ultrasonic oscillation liquid partly by 10 times and 100 times, and then take 100 μL of the stock solution and the two gradiently diluted ultrasonic oscillation liquids and spread them evenly on the petri dish containing BHI medium Then put the petri dish into a 37°C constant temperature biochemical incubator and incubate overnight, and judge the adhesion of E. coli on the surface of the sample by the number of colonies on the petri dish. In order to further observe the residual bacteria on the surface of the sample after ultrasonic oscillation, the sample after oscillation was removed and washed twice with sterile PBS solution, then stained with 1% crystal violet solution for 30 minutes, and finally observed by laser confocal microscope and scanning electron microscope sample surface. In order to make the experimental data more accurate, we set up two groups of experiments, and the experimental results take the average value of the two groups of experiments.

(2) Results and conclusions:

Table 3 Escherichia coli adhesion test results

As shown in Figure 7, after incubation in a 37°C constant temperature incubator for 24 hours, neither sample 5 nor the control sample formed colonies on the surface of the sticky medium, which can prove that the samples were completely alcohol-sterilized before the E. coli adhesion test. , the surface of the sample was not polluted by bacteria during the experiment. Adhesion test results show (Figure 8), the surface of sample 5 can effectively reduce the adhesion of E. The bacteriostasis rates of 100% bacterial solution were 38.8%, 39.4% and 63.6%, respectively.

Embodiment 4 (Escherichia coli biofilm experiment)

(1) Evaluation method:

Test samples: sample 5 (G) prepared in Example 1 and a stainless steel control sample (K) not subjected to laser etching treatment.

Escherichia coli biofilm experiment is to dilute the bacterial culture solution cultivated overnight to OD600=0.3, sterilize the sample with 75% alcohol and fully dry it, then put it into a sterile 24-well plate, and then take 1mL of the diluted bacterial solution Inject into wells containing samples respectively, and then place the 24-well plate in a 37°C constant temperature incubator and incubate for 16 hours, so that E. coli has enough time to grow a biofilm in the sample. After the incubation, the bacterial solution on the surface of the sample was aspirated and washed 3 times with sterile PBS solution, and then stained with 1% crystal violet solution for 30 minutes. Finally, the staining image was excited by laser confocal microscopy to determine the growth of E. coli biofilm Happening. In order to make the experimental data more accurate, two sets of experiments are set up.

(2) Results and conclusions:

As shown in Figure 9, the surfaces of sample 5 (G) and control sample (K) were thoroughly sterilized, and there was no interference from bacteria during the experiment. According to the imaging situation of laser confocal microscope in Figure 10, it can be seen that the fluorescent area of the surface of sample 5 is significantly lower than that of the control sample surface. More Escherichia coli adhered to the surface of strip groove microstructure. The formation of biofilm is positively correlated with the number of bacteria, the greater the number of bacteria, the larger the area of biofilm formation. Therefore, according to the observation results of the laser confocal microscope, it can be concluded that the strip-shaped groove ultrastructure surface (sample 5) can significantly inhibit the formation of biofilm.

Embodiment 5 (protein adhesion experiment)

(1) Evaluation method:

First put sample 5 (G) and control sample (K) into a sterile biological safety cabinet for sterilization with 75% alcohol, and then put them into sterile 24-well plates to fully dry. Take 100 mg of fibrinogen (Fib) lyophilized powder and prepare 5 ml of Fib solution with a final concentration of 20 mg/ml. Take 1mL of the configured Fib solution and inject it into the wells containing the samples, and place it at room temperature for 10min. Then the fibrin solution on the surface of the sample was sucked away, washed twice with sterile PBS solution, and then allowed to dry naturally. Finally, the composition of the substances adhered to the surface was judged by EDS energy spectroscopy, and the fibers were observed with a scanning electron microscope and an optical metallographic microscope. protein adhesion.

(2) Results and conclusions:

As shown in Figure 11, EDS energy spectrum analysis was carried out on the substances adhered to the surface of the strip-shaped groove microstructure (sample 5) and the original surface (control sample). It can be concluded from the atomic percentage that the substance adhering to the surface of each sample is protein. According to the observation results in Figure 12, it can be seen that the adhesion of fibrin on the surface of the strip-shaped groove microstructure is in the form of filaments and films with a small distribution area, while the adhesion on the original surface is in the form of blocks and sheets with a distribution area of larger. Further observation by an optical metallographic microscope ( FIG. 13 ), it can be seen more intuitively that a small amount of fibrin adheres to the surface of the strip-shaped groove microstructure compared to the original surface. Therefore, it can be concluded that the strip-groove microstructure surface can inhibit the adhesion of fibrin.

Embodiment 6 (platelet adhesion test)

(1) Evaluation method

The standby sample 5 (G) and the control sample (K) were sterilized by 75% alcohol in a sterile biological safety cabinet and fully dried. The sterilized samples were put into the wells of the 24-well plate, and 1 mL of platelet-rich plasma was dropped into the wells containing the samples, and then the well plates were incubated in a 37°C incubator for 3 hours. After the incubation, use a pipette gun to suck up excess plasma in the well plate, wash it three times with normal saline, and then fix it with 2.5% glutaraldehyde at room temperature for 2 hours; fix the fixed samples with 50%, 70% and 100% % ethanol/water gradient solution for sequential dehydration for 20 minutes. The dehydrated samples were dried in a CO ₂ critical dryer for 1.5 hours, and then sprayed with gold, and the morphology and aggregation deformation of platelets were observed by scanning electron microscopy (SEM).

(2) Results and conclusions:

As shown in FIG. 14 , the strip-groove microstructure surface (sample 5) and the pristine surface (control sample) were photographed and observed at three positions at a field of view of 500× by using a scanning electron microscope. It can be seen from the picture that there is basically no platelet adhesion in the groove on the surface of the strip-shaped groove microstructure, and only a small amount of platelets adhere to the protrusions of the microstructure; while a large number of platelets adhere to the original surface, and some areas have been Aggregate adhesion of platelets is present. Therefore, it can be concluded that the strip-groove microstructured surface (sample 5) can significantly inhibit the adhesion of platelets compared to the pristine surface (control sample).

In the description of this specification, descriptions referring to the terms "one embodiment", "some embodiments", "example", "specific examples", or "some examples" mean that specific features described in connection with the embodiment or example , structure, material or characteristic is included in at least one embodiment or example of the present disclosure. In this specification, the schematic representations of the above terms are not necessarily directed to the same embodiment or example. Furthermore, the described specific features, structures, materials or characteristics may be combined in any suitable manner in any one or more embodiments or examples. In addition, those skilled in the art can combine and combine different embodiments or examples and features of different embodiments or examples described in this specification without conflicting with each other.

Although the embodiments of the present disclosure have been shown and described above, it can be understood that the above embodiments are exemplary and should not be construed as limitations on the present disclosure, and those skilled in the art can understand the above-mentioned embodiments within the scope of the present disclosure. The embodiments are subject to changes, modifications, substitutions and variations.

Claims

A method for finely processing a surgical instrument, characterized in that a microstructure of strip grooves is formed on the surface of the surgical instrument by laser etching.
The method according to claim 1, characterized in that nanosecond pulse laser is used for the laser etching.
The method according to claim 2, wherein the parameters for etching by the nanosecond pulsed laser include: etching power 20w, scanning speed 600mm/s, frequency 20KHz, number of scans 10 or 20, scanning The pitch is 60 microns-150 microns.
The method according to claim 3, wherein the scanning pitch is 60 microns, 90 microns, 120 microns or 150 microns.
The method according to any one of claims 1-4, characterized in that the microstructure is a plurality of parallel grooves.
The method according to claim 5, characterized in that each of the plurality of parallel grooves has a width of 40 microns to 60 microns and a depth of 60 microns to 70 microns.
The method according to claim 5, wherein the width of each of the plurality of parallel grooves is 60 microns, 90 microns, 120 microns or 150 microns, and the depth is 20 microns-50 microns.
The method according to any one of claims 1-7, further comprising: using a chemical modification method to perform low surface energy modification on the surface of the microstructure, so as to form a self-cleaning surface.
The method according to claim 8, wherein the chemical modification method comprises: using absolute ethanol to clean the surface of the surgical instrument forming the microstructure, and then soaking the surface of the surgical instrument in 5mmol/ L of PFDTES methanol solution for 10 hours, and placed in a constant temperature blast drying oven at 150 ° C for 1 hour to solidify, take it out and wait for it to cool.
The method according to any one of claims 1-9, characterized in that, the surface having the microstructure has superhydrophobic and superphobic properties.
The method according to any one of claims 1-10, wherein the surface having the microstructure has anti-bacterial adhesion properties, anti-biofilm growth properties, anti-protein adhesion properties and anti-platelet adhesion properties. Attached performance.
The method according to any one of claims 1-11, characterized in that the bacteriostatic rate of the surface with the microstructure is not lower than 40%.