CN113790958B - Polymer bionic tissue and application thereof - Google Patents
Polymer bionic tissue and application thereof Download PDFInfo
- Publication number
- CN113790958B CN113790958B CN202111018335.2A CN202111018335A CN113790958B CN 113790958 B CN113790958 B CN 113790958B CN 202111018335 A CN202111018335 A CN 202111018335A CN 113790958 B CN113790958 B CN 113790958B
- Authority
- CN
- China
- Prior art keywords
- tissue
- bionic
- suture
- high molecular
- biomimetic
- 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
- 239000011664 nicotinic acid Substances 0.000 title claims abstract description 120
- 229920000642 polymer Polymers 0.000 title claims description 41
- 239000000835 fiber Substances 0.000 claims abstract description 69
- 238000000034 method Methods 0.000 claims abstract description 42
- 230000003592 biomimetic effect Effects 0.000 claims abstract description 33
- 239000000463 material Substances 0.000 claims abstract description 12
- 229920000728 polyester Polymers 0.000 claims description 20
- 239000002861 polymer material Substances 0.000 claims description 13
- 239000004743 Polypropylene Substances 0.000 claims description 11
- -1 polypropylene Polymers 0.000 claims description 11
- 229920001155 polypropylene Polymers 0.000 claims description 11
- 239000004814 polyurethane Substances 0.000 claims description 10
- 229920002635 polyurethane Polymers 0.000 claims description 10
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 claims description 9
- 239000003365 glass fiber Substances 0.000 claims description 9
- 239000000741 silica gel Substances 0.000 claims description 9
- 229910002027 silica gel Inorganic materials 0.000 claims description 9
- 108010010803 Gelatin Proteins 0.000 claims description 7
- 239000008273 gelatin Substances 0.000 claims description 7
- 229920000159 gelatin Polymers 0.000 claims description 7
- 235000019322 gelatine Nutrition 0.000 claims description 7
- 235000011852 gelatine desserts Nutrition 0.000 claims description 7
- 238000001816 cooling Methods 0.000 claims description 6
- 238000003825 pressing Methods 0.000 claims description 6
- 238000007493 shaping process Methods 0.000 claims description 6
- 102000008186 Collagen Human genes 0.000 claims description 5
- 108010035532 Collagen Proteins 0.000 claims description 5
- 229920001436 collagen Polymers 0.000 claims description 5
- 229920002521 macromolecule Polymers 0.000 claims description 5
- 239000002729 catgut Substances 0.000 claims description 4
- 230000001788 irregular Effects 0.000 claims description 4
- 229920000620 organic polymer Polymers 0.000 claims description 4
- 229920002994 synthetic fiber Polymers 0.000 claims description 4
- 239000012209 synthetic fiber Substances 0.000 claims description 4
- 238000009864 tensile test Methods 0.000 claims description 4
- 229920005615 natural polymer Polymers 0.000 claims description 3
- 238000009958 sewing Methods 0.000 claims description 3
- 229920001661 Chitosan Polymers 0.000 claims description 2
- 239000004745 nonwoven fabric Substances 0.000 claims description 2
- 238000007711 solidification Methods 0.000 claims description 2
- 230000008023 solidification Effects 0.000 claims description 2
- 230000001419 dependent effect Effects 0.000 claims 1
- 238000002360 preparation method Methods 0.000 abstract description 11
- 238000011156 evaluation Methods 0.000 abstract description 5
- 210000001519 tissue Anatomy 0.000 description 114
- 210000003491 skin Anatomy 0.000 description 17
- 238000001514 detection method Methods 0.000 description 11
- 238000011056 performance test Methods 0.000 description 9
- 238000012360 testing method Methods 0.000 description 8
- 238000013334 tissue model Methods 0.000 description 5
- 238000005516 engineering process Methods 0.000 description 4
- 239000000126 substance Substances 0.000 description 4
- 230000008569 process Effects 0.000 description 3
- 230000000052 comparative effect Effects 0.000 description 2
- 230000007423 decrease Effects 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 239000011521 glass Substances 0.000 description 2
- 210000000056 organ Anatomy 0.000 description 2
- 238000000926 separation method Methods 0.000 description 2
- 230000007480 spreading Effects 0.000 description 2
- 238000003892 spreading Methods 0.000 description 2
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 239000012237 artificial material Substances 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 210000000988 bone and bone Anatomy 0.000 description 1
- 210000000845 cartilage Anatomy 0.000 description 1
- 210000004027 cell Anatomy 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 210000004207 dermis Anatomy 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000002615 epidermis Anatomy 0.000 description 1
- 230000004927 fusion Effects 0.000 description 1
- 238000000338 in vitro Methods 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 238000011835 investigation Methods 0.000 description 1
- 230000003902 lesion Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 210000003205 muscle Anatomy 0.000 description 1
- 210000001087 myotubule Anatomy 0.000 description 1
- 206010033675 panniculitis Diseases 0.000 description 1
- 230000035790 physiological processes and functions Effects 0.000 description 1
- 238000007920 subcutaneous administration Methods 0.000 description 1
- 210000004304 subcutaneous tissue Anatomy 0.000 description 1
- 238000012549 training Methods 0.000 description 1
- 210000003932 urinary bladder Anatomy 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N3/00—Investigating strength properties of solid materials by application of mechanical stress
- G01N3/08—Investigating strength properties of solid materials by application of mechanical stress by applying steady tensile or compressive forces
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/06—Needles ; Sutures; Needle-suture combinations; Holders or packages for needles or suture materials
- A61B17/06166—Sutures
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00831—Material properties
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2203/00—Investigating strength properties of solid materials by application of mechanical stress
- G01N2203/0001—Type of application of the stress
- G01N2203/0003—Steady
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2203/00—Investigating strength properties of solid materials by application of mechanical stress
- G01N2203/0014—Type of force applied
- G01N2203/0016—Tensile or compressive
- G01N2203/0017—Tensile
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2203/00—Investigating strength properties of solid materials by application of mechanical stress
- G01N2203/0058—Kind of property studied
- G01N2203/006—Crack, flaws, fracture or rupture
- G01N2203/0067—Fracture or rupture
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2203/00—Investigating strength properties of solid materials by application of mechanical stress
- G01N2203/02—Details not specific for a particular testing method
- G01N2203/026—Specifications of the specimen
- G01N2203/0262—Shape of the specimen
- G01N2203/0278—Thin specimens
- G01N2203/028—One dimensional, e.g. filaments, wires, ropes or cables
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Surgery (AREA)
- Biomedical Technology (AREA)
- Physics & Mathematics (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Engineering & Computer Science (AREA)
- Chemical & Material Sciences (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- General Physics & Mathematics (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Materials For Medical Uses (AREA)
Abstract
The invention provides a high molecular bionic tissue, wherein the high molecular bionic tissue comprises a three-dimensional fiber grid and an elastic high molecular material, the three-dimensional fiber grid is used as a bionic tissue skeleton to be fused inside the elastic high molecular material, and the density of the high molecular bionic tissue is 0.10g/cm 3～0.15g/cm3. The invention also provides a preparation method of the high molecular bionic tissue. The present invention provides a method of evaluating the performance of a surgical suture comprising using the polymeric biomimetic tissue or biomimetic skin tissue of the present invention. The invention also provides application of the high molecular bionic tissue or the bionic skin tissue in evaluating surgical suture. The high molecular bionic tissue has good hooking capability and tensile property, is easy to hook with a barb suture, is successfully applied to the performance evaluation of medical instruments, and expands the blank in the application field of the high molecular bionic tissue.
Description
Technical Field
The invention relates to the technical field of high polymer materials, in particular to a high polymer bionic tissue and application thereof in bionic skin.
Background
The bionic tissue is an artificial material tissue which is constructed in vitro in a bionic way and has a structure and a function similar to those of organisms, has wide application in the medical field, can be used for repairing tissues and organs replacing lesions, finally realizes the normal physiological functions of the tissues and organs, and is applied to the fields of skin, bones/cartilages, bladder, blood vessels and the like at present.
Another important use of biomimetic tissue is in medical device development. Performance metrics for some medical devices need to be manifested as forces of the device against biological tissue. In such applications, it is desirable that the biomimetic tissue has more similarity to human tissue, including epidermis and subcutaneous tissue (e.g., muscle fibers, fat, etc.), but that the biomimetic tissue model does not have a porous structure, or living cells. One good example is a knotting-free surgical suture, and the product realizes wound tissue closure through a barb and tissue hooking by a method of cutting a thorn on the suture, so that the tedious operation of knotting the suture is avoided. This requires a high density of the bionic tissue, no excessive voids, and excellent hooking ability and stretching properties of the bionic tissue.
However, it should be noted that the suturing performance of the suture must be evaluated through the interaction between the suture and the bionic skin, no report on the bionic tissue of the type is found in the prior art, and no similar material can solve the technical problem.
Disclosure of Invention
Aiming at the defects of the prior art, the invention aims to provide a high molecular bionic tissue which has excellent hooking capacity and stretching performance, can be used for preparing bionic skin to realize performance evaluation of medical instruments, and more particularly can be specifically used for evaluating the performance of knotting-free surgical suture.
In order to achieve the above purpose, the technical scheme of the invention comprises:
In one aspect, the invention provides a polymer bionic tissue, which comprises a three-dimensional fiber grid and an elastic polymer material, wherein the three-dimensional fiber grid is used as a bionic tissue skeleton to be fused inside the elastic polymer material, and the density of the polymer bionic tissue is 0.10g/cm 3～0.15g/cm3.
The high molecular bionic tissue according to the invention, wherein the thickness of the bionic tissue is 5 mm-30 mm. Preferably, the thickness of the bionic tissue is 5 mm-15 mm.
The high molecular bionic tissue according to the invention, wherein the elastic high molecular material is selected from one or more of organic high molecular materials or natural high molecular materials.
Preferably, the organic polymer material is elastic silica gel or polyurethane; the natural polymer material is collagen, gelatin or chitosan.
Preferably, the viscosity of the organic polymer material is 1500cps to 3000cps.
The high molecular bionic tissue according to the invention, wherein the fiber mesh is made of one or more of synthetic fibers, non-woven fabrics and glass fibers; all are prepared by adopting a special process.
Preferably, the synthetic fiber is one or more of polypropylene fiber and polyester fiber.
Preferably, the three-dimensional fiber grid is a porous wire or net, and the branches are mutually communicated.
Preferably, the three-dimensional fiber mesh can be perforated in a honeycomb or irregular polygonal phase.
Preferably, the three-dimensional fiber grid has a grammage of 125g/m 2～350g/m2.
The high molecular bionic tissue provided by the invention, wherein the mass ratio of the three-dimensional fiber mesh to the elastic high molecular material is 1:20-1:30.
On the other hand, the invention also provides a preparation method of the high molecular bionic tissue, which comprises the following steps:
Step 1: preparing a mould of a high molecular bionic tissue, preparing a three-dimensional fiber grid according to the shape of the mould, fixing the three-dimensional fiber grid in the mould and dispersing the three-dimensional fiber grid well to enable all branches to be communicated with each other;
Step 2: filling the cavity of the die with elastic polymer material solution in a pressurizing mode;
step 3: and standing the mould, and taking out after solidification to obtain the polymer bionic tissue with the three-dimensional fiber grid.
The method according to the present invention, wherein, in step 1, the method of preparing the three-dimensional fiber mesh comprises:
Spreading the fibers into a uniform net layer with the thickness of 10-50 mm, and sending the uniform net layer into an oven; setting the temperature of the oven to be 30-70 ℃ and the time to be 5-40 min; cooling and shaping for 5-60 min, and then pressing into a thickness of 5-30 mm to obtain the three-dimensional fiber grid.
According to the method of the present invention, in step1, the shape of the polymer bionic tissue may be, but not limited to, square, circular or irregular, depending on different tissue structures.
The method according to the present invention, wherein, in step 2, the pressurizing pressure is 0.1MPa to 0.25MPa.
The inventor of the invention discovers that the high-density bionic tissue can be obtained through a pressurizing mode, the hooking capacity and the stretching capacity of the obtained bionic tissue can be greatly increased, and the fiber mesh and the tissue main body can be fully fused.
The method according to the invention, wherein, in step 3, the stationary curing temperature is 10 ℃ to 70 ℃; preferably, the standing curing temperature is 15 ℃ to 65 ℃.
The method according to the invention, wherein, in step 3, the standing curing time is 1h to 10h; preferably, the standing curing temperature is 2 to 6 hours.
In yet another aspect, the present invention provides a biomimetic skin tissue comprising the polymeric biomimetic tissue of the present invention.
In yet another aspect, the present invention provides a method of evaluating the performance of a surgical suture, the method comprising using the polymeric biomimetic tissue or biomimetic skin tissue of the present invention.
Preferably, the method comprises the steps of:
1) Taking a suture line to be detected, and sewing two pieces of polymer bionic tissues or bionic skin tissues together according to an operation sewing method;
2) Carrying out a tensile test on the macromolecule bionic tissue or the bionic skin tissue which are sewn together;
3) The tension value at break of the suture was recorded.
Wherein the surgical suture may be selected from a common suture or a knotless suture, preferably a knotless suture. Preferably, the surgical suture is selected from absorbable or non-absorbable sutures, including but not limited to silk threads, catgut threads, chemically synthesized threads, or collagen sutures.
In yet another aspect, the present invention provides the use of a polymeric biomimetic tissue or biomimetic skin tissue as described above in evaluating a surgical suture. Wherein the surgical suture is selected from common suture or knotting-free suture, preferably knotting-free suture. Preferably, the surgical suture is selected from absorbable or non-absorbable sutures, including but not limited to silk threads, catgut threads, chemically synthesized threads or collagen sutures.
Compared with the prior art, the high molecular bionic tissue provided by the invention has the following advantages:
The high molecular bionic tissue provided by the invention has good hooking capability and tensile property, is easy to hook with the barbed suture, is successfully applied to the performance evaluation of medical instruments, expands the application field of the high molecular bionic tissue, and fills the blank of the high molecular bionic tissue in the performance evaluation field of the medical instruments.
Detailed Description
The following detailed description of the invention is provided in connection with the accompanying drawings that are presented to illustrate the invention and not to limit the scope thereof.
Example 1: preparation and performance test of the high molecular bionic tissue of the invention
In this embodiment, the polymer bionic tissue is made of polypropylene fibers and elastic silica gel, and is a porous network structure, and all branches are mutually communicated. And the thickness of the macromolecule bionic tissue is 5mm.
In this embodiment, the polymer bionic tissue is realized by the following preparation method, which includes:
Step 1: preparing a square bionic tissue mold, wherein the thickness of the middle of the mold is 5mm, and preparing a three-dimensional polypropylene fiber grid with corresponding thickness according to the thickness of the mold as follows:
Spreading polypropylene fiber into a uniform net layer with the thickness of 10mm, and sending into an oven; baking at 35deg.C for 40min, and taking out; cooling and shaping for 10min, and then pressing into a thickness of 5mm to obtain a three-dimensional polypropylene fiber grid; the gram weight of the three-dimensional polypropylene fiber grid is 160g/m 2;
and fixing the three-dimensional polypropylene fiber grid in the die according to the shape of the die, and dispersing the three-dimensional polypropylene fiber grid well to enable all branches to be communicated with each other.
Step 2: the high polymer solution is elastic silica gel solution, the mass ratio of the elastic silica gel solution to the polypropylene fibers in the step 1 is 20:1, the silica gel solution is filled into the cavity of the die in the step 1 in a pressurizing mode, and the applied pressure is 0.1MPa.
Step 3: and (3) standing the die at 15 ℃ for 9 hours to obtain the high molecular bionic tissue with the density of 0.10g/cm 3 of the three-dimensional polypropylene fiber grid.
Wherein: the viscosity of the elastic silica gel solution is 1600cps, which is purchased from Shenzhen Hongzhejie technologies, inc.
In order to fully embody the stretching performance, 5 pieces of high molecular bionic tissues with the widths of 20mm and 12mm are respectively taken, two sides of the high molecular bionic tissues are respectively fixed on a clamp of a stretching strength machine and stretched to two sides at a certain speed until the bionic tissues are broken, the force during breaking, namely the breaking strength of the bionic tissues, is recorded, and the test results are shown in table 1.
Table 1 example 1 high molecular biomimetic tissue breaking strength
The hooking capability of the polymer bionic tissue prepared in this embodiment is mainly in terms of suture performance detection, and will be described below with reference to example 6.
Example 2: preparation and performance test of the high molecular bionic tissue of the invention
In the embodiment, the polymer bionic tissue is prepared from polyester fibers and polyurethane, and is of a porous net structure, and all branches are mutually communicated. And the thickness of the macromolecule bionic tissue is 15mm.
In this embodiment, the polymer bionic tissue is realized by the following preparation method, which includes:
Step 1: preparing a square bionic tissue mold, wherein the thickness of the middle of the mold is 15mm, and preparing a three-dimensional polyester fiber grid with corresponding thickness according to the thickness of the mold as follows:
Paving the polyester fiber into a uniform net layer with the thickness of 25mm, and sending the net layer into an oven; baking at 45deg.C for 30min, and taking out; cooling and shaping for 20min, and then pressing into a thickness of 15mm to obtain a three-dimensional polyester fiber grid; the gram weight of the three-dimensional polyester fiber grid is 225g/m 2;
And fixing the three-dimensional polyester fiber grid in the die according to the shape of the die, and dispersing the three-dimensional polyester fiber grid well to enable all branches to be communicated with each other.
Step 2: the high polymer solution is polyurethane solution, the mass ratio of the polyurethane solution to the polyester fiber in the step1 is 30:1, the silica gel solution is filled in the cavity of the die in the step1 in a pressurizing mode, and the applied pressure is 0.25MPa.
Step 3: and (3) standing the die at 65 ℃ for 2 hours, and obtaining the high molecular bionic tissue with the density of 0.15g/cm 3 of the three-dimensional polyester fiber grid after curing.
Wherein: the polyurethane solution had a density of 2500cps and was purchased from oceanic rise spring chemical technology limited.
In order to fully embody the tensile properties, 5 pieces of polymer bionic tissues having widths of 20mm and 12mm were taken, respectively, and their breaking strength was sequentially tested on a tensile strength machine using the same method as in example 1, and the test results are shown in table 2.
Table 2 example 2 high molecular biomimetic tissue breaking strength
The hooking capability of the polymer bionic tissue prepared in this embodiment is mainly in terms of suture performance detection, and will be described below with reference to example 6.
Example 3: preparation and performance test of the high molecular bionic tissue of the invention
In the embodiment, the polymer bionic tissue is prepared from polyester fiber and polyurethane, is of a porous net structure, and has a thickness of 8mm, wherein all branches are mutually communicated
In this embodiment, the polymer bionic tissue is realized by the following preparation method, which includes:
Step 1: preparing a square bionic tissue mold, wherein the thickness of the middle of the mold is 8mm, and preparing a three-dimensional polyester fiber grid with corresponding thickness according to the thickness of the mold as follows:
Paving the polyester fiber into a uniform net layer with the thickness of 15mm, and sending the net layer into an oven; baking at 55deg.C for 20min, and taking out; cooling and shaping for 25min, and then pressing into a thickness of 8mm to obtain a three-dimensional polyester fiber grid; the gram weight of the three-dimensional polyester fiber grid is 170g/m 2;
And fixing the three-dimensional polyester fiber grid in the die according to the shape of the die, and dispersing the three-dimensional polyester fiber grid well to enable all branches to be communicated with each other.
Step 2: the high polymer solution is polyurethane solution, the mass ratio of the polyurethane solution to the polyester fiber in the step1 is 25:1, the silica gel solution is filled in the cavity of the die in the step1 in a pressurizing mode, and the applied pressure is 0.20MPa.
Step 3: and (3) standing the die at 40 ℃ for 3 hours to obtain the high molecular bionic tissue with the density of 0.125g/cm 3 of the three-dimensional polyester fiber grid.
Wherein: the polyurethane solution had a density of 2000cps and was purchased from oceanic rise spring chemical technology limited.
In order to fully embody the tensile properties, 5 pieces of polymer bionic tissues having widths of 20mm and 12mm were taken, respectively, and their breaking strength was sequentially tested on a tensile strength machine using the same method as in example 1, and the test results are shown in table 3.
TABLE 3 example 3 high molecular biomimetic tissue breaking Strength
The hooking capability of the polymer bionic tissue prepared in this embodiment is mainly in terms of suture performance detection, and will be described below with reference to example 6.
Example 4: preparation and performance test of the high molecular bionic tissue of the invention
In the embodiment, the polymer bionic tissue is prepared from glass fiber and gelatin, is of a porous net structure, and has a thickness of 20mm, wherein all branches are mutually communicated
In this embodiment, the polymer bionic tissue is realized by the following preparation method, which includes:
Step 1: preparing a square bionic tissue mold, wherein the thickness of the middle of the mold is 20mm, and preparing a three-dimensional glass fiber grid with corresponding thickness according to the thickness of the mold as follows:
Paving glass fiber into a uniform net layer with the thickness of 35mm, and sending into an oven; baking at 65deg.C for 5min, and taking out; cooling and shaping for 60min, and then pressing into a thickness of 20mm to obtain a three-dimensional glass fiber grid; the gram weight of the glass fiber grid is 250g/m 2;
and fixing the three-dimensional glass grid in the mold according to the shape of the mold, and dispersing the three-dimensional glass grid well to enable all branches to be communicated with each other.
Step 2: the high polymer solution is gelatin solution, the mass ratio of the gelatin solution to the glass fiber in the step 1 is 25:1, the gelatin solution is filled into the cavity of the die in the step 1 in a pressurizing mode, and the applied pressure is 0.15MPa.
Step 3: and (3) standing the die at a standing temperature of 50 ℃ and a purifying temperature of 3.5h to obtain the high molecular bionic tissue with the three-dimensional glass fiber grid density of 0.116g/cm 3.
Wherein: the gelatin solution density was 1800cps, purchased from oceanic rise spring chemical technology limited.
In order to fully exhibit the tensile properties, 5 pieces of the polymer bionic tissue having a width of 20mm and 12mm were taken, respectively, and the breaking strength thereof was sequentially tested on a tensile strength machine by the same method as in example 1, and the test results are shown in table 4.
TABLE 4 example 4 high molecular biomimetic tissue breaking Strength
The hooking capability of the polymer bionic tissue prepared in this embodiment is mainly in terms of suture performance detection, and will be described below with reference to example 6.
Example 5: comparative example of Polymer bionic tissue
A polymer bionic tissue with a thickness of 8mm was prepared as well, and the model structure was the same as in example 3. The pressurizing process pressure in the step 2 in the preparation method is changed to be 0.05MPa. The density of the polymer bionic tissue prepared by the method is 0.08g/cm 3.
Compared with the polymer bionic tissue in the embodiment 3, the polymer bionic tissue obtained in the embodiment has the advantages of reduced density, uneven fusion of the three-dimensional fiber grid and the tissue main body and defects. The breaking strength of 5 pieces of the polymer bionic tissue with the width of 12mm was measured on a tensile strength machine by the same method as in example 1, and the comparison result is shown in table 5, and the breaking strength of the polymer bionic tissue of this example did not reach the effect in example 3.
TABLE 5 comparison of high molecular bionic tissue breaking strength
The hooking capability of the polymer bionic tissue prepared in this embodiment is mainly in terms of suture performance detection, and will be described below with reference to example 6.
Example 6 detection of the hooking Capacity of Polymer bionic tissues
The high molecular bionic tissues prepared in examples 1 to5 are used for detecting the performance of absorbable synthetic knotting-free suture, and the application is realized through the following steps:
Step 1: taking a knotting-free suture line to be detected (commercially available quick TM suture line, 2-0 thread number), and suturing the two pieces of high-molecular bionic tissue detection models according to an operation suturing method;
Step 2: the upper and lower pieces of the stitched detection model are respectively clamped on a clamp of a tensile strength machine (Shanghai Xiang Jie instrument and meter science and technology Co., ltd., model XJ 830S), a tensile test is carried out, two bionic tissue models are stretched to two sides according to a certain speed, the maximum tension value is recorded, the magnitude of the tension value can be used for measuring the hooking capacity of knotting-free sutures and bionic tissues, and meanwhile, the tension value is an evaluation mode for the knotting-free suture performance. The results are shown in Table 6 below:
table 6 comparison of biomimetic models and suture hooking capacities results of examples 1to 5
The high molecular bionic tissue and the knotting-free suture line have certain hooking capability. As the density decreases, so does the hooking capability. When the density of the high molecular bionic tissue model is within a certain range, the high molecular bionic tissue model is often broken near the middle of the knotting-free suture line in a tensile test. Examples 1 to 4 record the maximum tensile force at which the suture breaks, i.e. the breaking strength of the suture. However, when the hooking capability of the tissue is poor, the knotted suture thread will slip from the bionic tissue, at this time, the tension value recorded by the tension strength machine will gradually decrease after slipping, the maximum tension value is recorded, and the force is often less than the breaking strength of the suture thread.
The bionic tissue of example 5 had a too low density and a too low hooking force, and was subject to slipping.
Example 7 comparative example of the hooking Capacity of bionic tissue to animal tissue, commercially available model
Model one: a bionic tissue model prepared as in example 3;
model two: selecting skin with the back of a fresh pig of 8mm plus or minus 2mm (needing artificial treatment and having errors) from the pig skin tissue, wherein the skin tissue of the part is thicker, which is beneficial to suture;
model three: commercially available medical bionic skin and muscle suture training module (blue butterfly medical model factory).
Using the method of example 6, the results of comparing the hooking ability of the biomimetic tissue, animal tissue, commercially available model and suture are shown in Table 7 below.
TABLE 7 hooking capability ratio results
The commercially available bionic model (flat plate model of blue butterfly medical model factory) has almost no hooking capability because the inside of the model does not have a fiber structure, and the model can completely slip without knotting.
Because the suture position of the pigskin tissue is the subcutaneous dermis layer, the pigskin tissue needs to be ensured to be fresh, the materials are uniformly obtained, the suture operation error rate is higher, the hooking force is insufficient, and the slipping phenomenon exists.
The fiber mesh in the bionic tissue has good self-adhesion and hooking capability with the suture, the fibers are tightly combined, no chemical adhesive is contained, and the fibers can be well fused in the tissue main body. The three-dimensional fiber grid is constructed to enable the fiber structure in the tissue to be more vivid and easy to hook with the suture line, the suture line is not easy to slip in the test process after the suture line is sutured, and the hooking force of the suture line can be tested more truly.
Example 8 repeatability of the suture Performance test method
5 Knotting-free sutures were taken, the same analyst repeatedly performed suturing on the bionic skin in example 3, and the maximum force of separation of the bionic skin was tested, the test results are shown in table 8, the results show that the suturing performance test was 5 times, RSD% =7.6%, and the repeatability of the visible method was good.
Table 8 suture performance test method repeatability
EXAMPLE 9 intermediate precision of suture Performance test method
5 Knotting-free sutures are taken respectively, the bionic skin in the embodiment 3 is repeatedly sutured by adopting a method of replacing detection personnel and detection equipment, the maximum force of separation of the bionic skin is tested, the test results are shown in the table 9, the RSD% investigation is carried out respectively with the results of the embodiment 8, and the results show that the intermediate precision of the suturing performance test method is good.
TABLE 9 intermediate precision of suture Performance detection methods
The test data and the relative standard deviation of each group of examples 8-9 are combined, and no significant difference exists, namely the bionic tissue is suitable for detecting the suturing performance of the knotting-free suture and is stable enough.
The foregoing description of the preferred embodiments of the invention is not intended to be limiting, but rather is intended to cover all modifications, equivalents, alternatives, and improvements that fall within the spirit and scope of the invention.
Claims (27)
1. A high molecular bionic tissue, wherein the high molecular bionic tissue comprises a three-dimensional fiber grid and an elastic high molecular material, the three-dimensional fiber grid is used as a bionic tissue skeleton to be fused inside the elastic high molecular material, and the density of the high molecular bionic tissue is 0.10 g/cm 3~0.15 g/cm3; wherein the elastic polymer material is selected from one or more of organic polymer materials or natural polymer materials; the organic polymer material is elastic silica gel or polyurethane; the natural polymer material is gelatin or chitosan,
The method for preparing the three-dimensional fiber mesh comprises the following steps:
Paving the fibers into a uniform net layer with the thickness of 10 mm-50 mm, and feeding the uniform net layer into an oven; setting the temperature of the oven to be 30-70 ℃ and the time to be 5-40 min; and cooling and shaping for 5-60 min, and then pressing into a thickness of 5-30 mm to obtain the three-dimensional fiber grid.
2. The polymeric biomimetic tissue according to claim 1, wherein the thickness of the polymeric biomimetic tissue is 5 mm-30 mm.
3. The polymeric biomimetic tissue according to claim 2, wherein the thickness of the polymeric biomimetic tissue is 5 mm-15 mm.
4. The polymeric biomimetic tissue according to any one of claims 1-3, wherein the viscosity of the organic polymeric material is 1500 cps-3000 cps.
5. The polymer bionic tissue according to any one of claims 1 to 3, wherein the fiber mesh is one or more of synthetic fiber, nonwoven fabric, and glass fiber.
6. The polymer bionic tissue according to claim 5, wherein the synthetic fiber is one or more of polypropylene fiber and polyester fiber.
7. A polymeric biomimetic tissue according to any one of claims 1-3, wherein the three-dimensional fiber mesh is porous, filiform or reticular, and the branches are interconnected.
8. The polymer bionic tissue according to claim 7, wherein the three-dimensional fiber mesh is perforated in a honeycomb or irregular polygonal phase.
9. A polymeric biomimetic tissue according to any one of claims 1-3, wherein the three-dimensional fiber mesh has a grammage of 125 g/m 2~350 g/m2.
10. The polymeric biomimetic tissue according to any one of claims 1-3, wherein the mass ratio of the three-dimensional fiber mesh to the elastic polymeric material is 1:20-1:30.
11. The method for preparing a polymer biomimetic tissue according to any one of claims 1 to 10, comprising the steps of:
Step 1: preparing a mould of a high molecular bionic tissue, preparing a three-dimensional fiber grid according to the shape of the mould, fixing the three-dimensional fiber grid in the mould and dispersing the three-dimensional fiber grid well to enable all branches to be communicated with each other;
Step 2: filling the cavity of the die with elastic polymer material solution in a pressurizing mode;
step 3: and standing the mould, and taking out after solidification to obtain the polymer bionic tissue with the three-dimensional fiber grid.
12. The method according to claim 11, wherein in step 1, the shape of the polymeric biomimetic tissue is dependent on different tissue structures; the shape of the macromolecule bionic tissue is square, round or irregular.
13. The method according to claim 11, wherein in step 2, the pressurizing pressure is 0.1 MPa to 0.25 MPa.
14. The method according to claim 11, wherein in step 3, the stationary curing temperature is 10 ℃ to 70 ℃.
15. The method according to claim 11, wherein in step 3, the standing curing time is 1 to 10 hours.
16. A biomimetic skin tissue comprising the polymeric biomimetic tissue according to any one of claims 1 to 10.
17. A method of evaluating the performance of a surgical suture, the method comprising using the polymeric biomimetic tissue of any one of claims 1 to 10 or the biomimetic skin tissue of claim 16.
18. The method of claim 17, comprising the steps of:
1) Taking a suture line to be detected, and sewing two pieces of the high molecular bionic tissue or the bionic skin tissue together according to an operation suture method;
2) Carrying out a tensile test on the macromolecule bionic tissue or the bionic skin tissue which are sewn together;
3) The tension value at break of the suture was recorded.
19. The method of claim 17 or 18, wherein the surgical suture is selected from a plain suture or a knotless suture.
20. The method of claim 19, wherein the surgical suture is a knotless suture.
21. The method of claim 17 or 18, wherein the surgical suture is selected from absorbable sutures or non-absorbable sutures.
22. The method of claim 17 or 18, wherein the suture is selected from a silk thread, a catgut thread, a chemically synthesized thread, or a collagen suture.
23. Use of the polymeric biomimetic tissue according to any one of claims 1 to 10 or the biomimetic skin tissue according to claim 16 for evaluating a surgical suture.
24. Use according to claim 23, wherein the surgical suture is selected from a plain suture or a knotless suture.
25. The use of claim 24, wherein the surgical suture is a knotless suture.
26. Use according to claim 23, wherein the surgical suture is selected from absorbable or non-absorbable sutures.
27. Use according to claim 23, wherein the surgical suture is selected from a silk thread, a catgut thread, a chemically synthesized thread or a collagen suture.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111018335.2A CN113790958B (en) | 2021-09-01 | 2021-09-01 | Polymer bionic tissue and application thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111018335.2A CN113790958B (en) | 2021-09-01 | 2021-09-01 | Polymer bionic tissue and application thereof |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN113790958A CN113790958A (en) | 2021-12-14 |
| CN113790958B true CN113790958B (en) | 2024-06-14 |
Family
ID=79182509
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202111018335.2A Active CN113790958B (en) | 2021-09-01 | 2021-09-01 | Polymer bionic tissue and application thereof |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN113790958B (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115634313B (en) * | 2022-09-30 | 2023-12-22 | 北京航空航天大学 | Elastomer with high anisotropy coefficient and preparation method and application thereof |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103656728A (en) * | 2013-11-01 | 2014-03-26 | 深圳清华大学研究院 | Wound repairing material and preparation method thereof |
| WO2015177926A1 (en) * | 2014-05-23 | 2015-11-26 | 株式会社レジーナ | Artificial skin for suture training and method for manufacturing same |
| CN105944143A (en) * | 2016-06-06 | 2016-09-21 | 东华大学 | Bionic tissue based on acellular matrix-cell-three-dimensional fiber network and preparation method of bionic tissue |
Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB0516846D0 (en) * | 2005-08-17 | 2005-09-21 | Knight David P | Meniscal repair device |
| KR100875189B1 (en) * | 2005-08-26 | 2008-12-19 | 이화여자대학교 산학협력단 | Fibrous three-dimensional porous support for tissue regeneration using electrospinning and its preparation method |
| US8314211B2 (en) * | 2009-04-07 | 2012-11-20 | George Falus | Tissue sealant for use in non compressible hemorrhage |
| CN106693065B (en) * | 2017-02-06 | 2019-07-19 | 清华大学深圳研究生院 | A kind of gradient structure engineering rack production method |
| GB201708233D0 (en) * | 2017-05-23 | 2017-07-05 | Orthox Ltd | Implantable tissue repair devices and methods for manufacturing the same |
| CN112078923A (en) * | 2019-06-14 | 2020-12-15 | 沈阳恒生医用科技有限公司 | Be applied to packing carton of medical line body |
| CN112402695B (en) * | 2020-11-27 | 2022-09-20 | 南方科技大学 | In-situ mineralized bionic bone hydrogel composite material with oriented structure and preparation method and application thereof |
-
2021
- 2021-09-01 CN CN202111018335.2A patent/CN113790958B/en active Active
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103656728A (en) * | 2013-11-01 | 2014-03-26 | 深圳清华大学研究院 | Wound repairing material and preparation method thereof |
| WO2015177926A1 (en) * | 2014-05-23 | 2015-11-26 | 株式会社レジーナ | Artificial skin for suture training and method for manufacturing same |
| CN105944143A (en) * | 2016-06-06 | 2016-09-21 | 东华大学 | Bionic tissue based on acellular matrix-cell-three-dimensional fiber network and preparation method of bionic tissue |
Also Published As
| Publication number | Publication date |
|---|---|
| CN113790958A (en) | 2021-12-14 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JP6297666B2 (en) | Irregularly uniform three-dimensional tissue scaffold of absorbent and non-absorbable materials | |
| RU2606745C2 (en) | Prosthesis and its production method | |
| CN105960207B (en) | Recessed surgical fastening device | |
| ES2732070T3 (en) | Hydrogelifying fibrous structure | |
| JP6411445B2 (en) | Irregularly uniform three-dimensional tissue scaffold of absorbent and non-absorbable materials | |
| CN113790958B (en) | Polymer bionic tissue and application thereof | |
| Meng et al. | Suture retention strength of P (LLA-CL) tissue-engineered vascular grafts | |
| WO2006102756A1 (en) | Anisotropic hydrogels | |
| CN101163451A (en) | Absorbable/biodegradable composite yarns and property-modulated surgical implants therefrom | |
| CN203226924U (en) | Double-layer antistick medical herniorrhaphy sheet | |
| CN109009280A (en) | Tissue for the fixed repair system of soft tissue and method enhances tack | |
| Ingle | Mechanical Performance and Finite Element Analysis of Bi-directional Barbed Sutures. | |
| AU2015249131A1 (en) | Prosthetic porous knit | |
| JPH02945B2 (en) | ||
| Hu et al. | Biocompatibility of braided poly (L‐lactic acid) nanofiber wires applied as tissue sutures | |
| Trocchia et al. | A re-exploration of the use of barbed sutures in flexor tendon repairs | |
| Dattilo Jr | Knotless bi-directional barbed absorbable surgical suture | |
| CN202051754U (en) | Medical suture | |
| CN102112160A (en) | Base material for revascularization | |
| CN213190318U (en) | Absorbable tissue repair mesh | |
| KR102309056B1 (en) | Medical thread and manufacturing method thereof | |
| CN111297512A (en) | Absorbable tissue repair mesh and preparation method thereof | |
| CN105126174A (en) | Bioabsorbable medical material and preparation method thereof | |
| Cong | Studies of barbed surgical sutures associated with materials, anchoring performance and histology | |
| Huang | A Comparison of the Properties and Performance of Polyvinylidene Fluoride and Polypropylene Barbed Sutures in Tendon Repair. |
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 |