A spinning device and preparation method of hydrodynamic flexible drawing hydrogel fibers

Abstract

The application discloses a spinning device and a preparation method of water-power flexible drawing hydrogel fibers, and belongs to the field of textile materials.The spinning device of the water-power flexible drawing hydrogel fibers comprises a spinning stock solution injection mechanism, a vortex device mechanism and a coagulation drawing device mechanism.The spinning stock solution is rapidly cross-linked and solidified to form a hydrogel fiber in a coagulation bath solution rotating at a certain speed, and the hydrogel fiber is subjected to flexible drawing through a shearing tensile force field of solution circulation flow, so that the internal structure and the surface morphology of the hydrogel fiber are not damaged, and the hydrogel fiber with controllable diameter and uniform thickness can be continuously prepared.

Description

TECHNICAL FIELD

[0001] The present application relates to a kind of water power flexible drawing water gel fiber spinning device and preparation method, belong to textile material field. BACKGROUND

[0002] Hydrogel is a kind of hydrophilic polymer three-dimensional network, due to its excellent biocompatibility and moisture absorption and retention performance, has great application potential in wound dressing field.Hydrogel has excellent moisture absorption, can absorb wound exudate, maintain wound wet balance, promote wound healing.Hydrogel soft texture enables it to be in close contact with wound, prevent wound from external stimulation.Hydrogel unique porous structure can load various functional factors, provide necessary active substance supply for the rapid healing of wound.Currently, hydrogel dressing mainly includes antibacterial / antioxidant hydrogel dressing, adhesive hydrogel dressing, hemostatic hydrogel dressing, conductive hydrogel dressing and intelligent monitoring hydrogel dressing, etc.Hydrogel dressing has many excellent properties, but at the same time, there is also the problem of poor air permeability, wound cannot exchange gas with the outside world.

[0003] Hydrogel fiber has both the performance characteristics of hydrogel (high water content, high porosity) and the structural advantages of fiber (high specific surface area, good mechanical properties).The high specific surface area of hydrogel fiber makes it have excellent moisture absorption and retention, so it can effectively absorb wound exudate and maintain wound wet balance;The unique three-dimensional network structure of hydrogel fiber enables it to slowly release drug molecules and promote wound healing.Nonwoven technology has the advantages of fast production speed, simple process and wide raw material range.Therefore, hydrogel-based nonwoven materials prepared by nonwoven technology have great application prospect in wound dressing field.

[0004] Currently, the preparation methods of hydrogel fibers mainly include pre-gel solution drawing, mold polymerization, wet spinning, electrospinning, and solution jet spinning. Pre-gel solution drawing refers to drawing uniform hydrogel fibers from a gel solution. This preparation method is simple, but it has certain requirements for the viscosity of the spinning solution and the molecular weight of the polymer. Mold polymerization refers to injecting a spinning monomer solution into a mold to prepare a hydrogel fiber of a specific size by crosslinking through a specific method. The hydrogel fibers prepared by this method are uniform in thickness and adjustable in diameter, and have a wide range of applications. However, the fiber length is limited by the size of the mold, and there are problems in continuous processing. The structure and function of the hydrogel nanofiber prepared by electrospinning or solution jet spinning are similar to those of the extracellular matrix, and it has great application prospects in the field of tissue engineering scaffolds or drug delivery. However, electrospinning or solution jet spinning has the problems of slow production speed and the need to add a spinning aid in some systems. Wet spinning is the most commonly used method for preparing hydrogel fibers at present. This method can continuously prepare uniform hydrogel fibers. However, it is difficult to use traditional drawing devices to draw the gel-like hydrogel fibers, and the prepared hydrogel fibers are relatively thick, which limits the application of hydrogel fibers. Therefore, a new type of hydrogel fiber spinning device and preparation method is needed. SUMMARY

[0005] In view of the deficiencies of the prior art, the purpose of the present application is to provide a spinning device for hydrodynamic flexible drawing of hydrogel fibers and a preparation method. The spinning dope is rapidly crosslinked and solidified in the coagulation bath solution to form a hydrogel fiber, and the shearing and stretching force field of the rotating flow of the coagulation bath solution is used to flexibly draw the hydrogel fiber. This drawing method does not damage the internal structure and surface morphology of the hydrogel fiber, and can continuously prepare hydrogel fibers with controllable diameter, uniform thickness and consistent performance. Different diameters of hydrogel fibers can be prepared by adjusting the process parameters such as water flow rate, spinning speed and jet hole diameter.

[0006] The first purpose of the present application is to provide a spinning device for hydrodynamic flexible drawing of hydrogel fibers, which comprises a spinning dope injection mechanism, a vortex device mechanism and a coagulation drawing mechanism.

[0007] Further, the vortex device mechanism is used to form a rapidly rotating vortex in the coagulation drawing mechanism, the spinning dope injection mechanism is used to store the spinning dope and inject the spinning dope into the coagulation drawing mechanism, and the spinning dope is rapidly crosslinked in the coagulation drawing mechanism to form a hydrogel fiber.

[0008] In one embodiment, the spinning dope injection mechanism is one of a push pump injection device and a wet spinning liquid supply device.

[0009] Further, the propelling pump injection device comprises an injection pump, an injector and a connecting pipe, the injector is used to store the spinning dope, the injection pump is used to propel the flow of the spinning dope in the injector, and the connecting pipe is used to connect the injector and the coagulation drafting mechanism.

[0010] Further, the wet spinning feed device comprises a nitrogen propelling device, a liquid storage device, a screw extruder, a metering pump, a spinning nozzle, a spinneret plate and a connector, wherein the liquid storage device is used to store the spinning dope, the nitrogen propelling device, the screw extruder, the metering pump and the spinneret plate are used to control the flow and extrusion of the spinning dope, and the connector connects the solution extruded by the spinneret plate to the coagulation drafting mechanism.

[0011] In an embodiment, the vortex device mechanism is one of a magnetic stirring device, a mechanical stirring device, a ring-shaped water vortex device, a bottom impeller device and a vertical roller device.

[0012] Further, the magnetic stirring device and the mechanical stirring device form a vortex with high speed rotation through magnetic sub or stirrer; the vertical roller device forms a vortex through the rotation of the roller to drive the water flow; and the bottom impeller device forms a rotating vortex through the different rotation speeds of the large and small impellers.

[0013] In an embodiment, the coagulation drafting device is used to hold the coagulation bath solution and receive the spinning dope, and simultaneously, through the formation of a rotating vortex with a certain speed, the shearing force of the rotating solution is used to draft the spinning dope.

[0014] The above-mentioned spinning device of the water-powered flexible drafting hydrogel fiber of the present application is applied in the fields of spinning, hydrogel fiber preparation and hydrogel yarn preparation.

[0015] A second object of the present application is to provide a preparation method of a water-powered flexible drafting hydrogel fiber, comprising the following steps:

[0016] (1) dissolving sodium alginate and a high molecular polymer or a spinning monomer in water to obtain a spinning dope, and dissolving an inorganic salt in water to obtain a coagulation bath solution;

[0017] (2) the spinning injection mechanism injects the spinning dope into the coagulation drafting device mechanism through the connecting pipe, and the spinning dope is quickly cross-linked and solidified in the coagulation bath solution to form a hydrogel fiber;

[0018] (3) homogenizing the prepared hydrogel fiber to obtain a uniformly dispersed hydrogel short fiber dispersion liquid;

[0019] (4) placing the prepared hydrogel short fiber dispersion liquid to obtain a hydrogel fiber web, drying to obtain an un-reinforced hydrogel non-woven material;

[0020] (5) Unreinforced hydrogel nonwoven material was impregnated with silk fibroin solution, dried, and then fumigated with ethanol to obtain hydrogel fiber nonwoven material.

[0021] In one embodiment, the polymer polymer in step (1) is one or more of carboxymethyl cellulose, carboxymethyl chitosan, carboxymethyl starch, hyaluronic acid, gelatin, silk fibroin, chitosan, polyvinyl alcohol, and polyethylene glycol.

[0022] In one embodiment, the spinning monomer in step (1) is one or more of acrylamide, dimethacrylamide, acrylic acid, and methacrylic acid.

[0023] In one embodiment, the inorganic salt mentioned in step (1) is one or more of calcium chloride, copper chloride, ferric chloride, and zinc chloride.

[0024] Specifically, the spinning solution in step (1) can be composed of sodium alginate, sodium carboxymethyl cellulose, quercetin, and water.

[0025] Specifically, the spinning solution composition, by weight, is 0.4–0.6 parts sodium alginate, 0.1–0.3 parts sodium carboxymethyl cellulose, 0.01–0.03 parts quercetin, and 35–45 parts water.

[0026] Specifically, the coagulation bath solution in step (1) can be composed of calcium chloride and water.

[0027] Specifically, the coagulation bath solution in step (1) may be composed of 12 to 18 parts by weight of calcium chloride and 450 to 550 parts by weight of water.

[0028] Specifically, the spinning solution in step (1) can also be composed of sodium alginate, acrylamide, chitosan quaternary ammonium salt, N,N′-methylenebisacrylamide and water.

[0029] Specifically, the spinning solution composition, by weight, may include 1-3 parts sodium alginate, 20-27 parts acrylamide, 0.1-0.2 parts chitosan quaternary ammonium salt, 0.01-0.05 parts N,N′-methylenebisacrylamide, and 80-120 parts water.

[0030] Specifically, the coagulation bath solution in step (1) can also be calcium chloride, chitosan quaternary ammonium salt, ammonium persulfate, N,N,N′,N′-tetramethylethylenediamine and water.

[0031] Specifically, the coagulation bath solution in step (1) may, by weight, consist of 10-15 parts calcium chloride, 2-5 parts chitosan quaternary ammonium salt, 8-15 parts ammonium persulfate and 350-450 parts water.

[0032] Specifically, the volume mass of N,N,N',N'-tetramethyl ethylenediamine and calcium chloride in the coagulation bath solution in step (1) is 200 μL: 10-15 g.

[0033] Further, the pushing speed in step (2) is 0.6-1 mL / min.

[0034] Further, the diameter of the needle used by the spinning injection mechanism in step (2) is 0.25-0.30 mm.

[0035] Further, the stirring speed in the vortex device mechanism in step (2) is 800-1200 rpm.

[0036] Further, the homogenization in step (3) is performed by using a homogenizer at 12000-13000 rpm for 20-30 s.

[0037] Further, the mass concentration of the silk fibroin solution in step (5) is 0.5-1.5%.

[0038] The present application provides a hydrogel fiber prepared according to the above method.

[0039] The hydrogel fiber prepared by the present application has applications in the fields of biomedical materials, wastewater treatment, and flexible sensors.

[0040] The present application has the following advantages:

[0041] (1) The present application designs a new type of hydrogel fiber spinning device, which is simple in process, wide in application range, and capable of continuously preparing hydrogel fibers of different diameters to meet the needs of different occasions.

[0042] (2) The present application uses the shearing and stretching force field of the circulating flow of the coagulation bath solution to perform flexible drawing on the hydrogel fiber, which does not damage the internal structure and surface morphology of the hydrogel fiber, and can continuously prepare hydrogel fibers of controllable diameter and uniform thickness. BRIEF DESCRIPTION OF DRAWINGS

[0043] Figure 1 FIG. 1 is a schematic diagram of the spinning device of the hydrogel fiber of Example 1.

[0044] Figure 2 FIG. 3 is a tensile property curve of the hydrogel fiber of Example 1 and Example 2.

[0045] Figure 3 FIG. 5 is a micro-morphology diagram of the hydrogel fiber prepared at a pushing speed of 0.2 mL / min in Comparative Example 1.

[0046] Figure 4The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 0.4 mL / min in Comparative Example 1.

[0047] Figure 5 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 0.6 mL / min in Comparative Example 1.

[0048] Figure 6 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 0.8 mL / min in Comparative Example 1.

[0049] Figure 7 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 1 mL / min in Comparative Example 1.

[0050] Figure 8 The diameter of the hydrogel fibers prepared at different propulsion speeds in Comparative Example 1 is shown.

[0051] Figure 9 The image shows the microstructure of the hydrogel fibers prepared at a stirring speed of 0 rpm in Comparative Example 2.

[0052] Figure 10 The image shows the microstructure of the hydrogel fibers prepared at a stirring speed of 750 rpm in Comparative Example 2.

[0053] Figure 11 The image shows the microstructure of the hydrogel fibers prepared at a stirring speed of 1000 rpm in Comparative Example 2.

[0054] Figure 12 The image shows the microstructure of the hydrogel fibers prepared at a stirring speed of 1250 rpm in Comparative Example 2.

[0055] Figure 13 The diameter of the hydrogel fibers at different stirring speeds in Comparative Example 2 is shown.

[0056] Figure 14 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 0.25 mL / min in Comparative Example 3.

[0057] Figure 15 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 0.5 mL / min in Comparative Example 3.

[0058] Figure 16 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 0.75 mL / min in Comparative Example 3.

[0059] Figure 17 The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 1 mL / min in Comparative Example 3.

[0060] Figure 18The image shows the microstructure of the hydrogel fibers prepared at a propulsion speed of 1.5 mL / min in Comparative Example 3.

[0061] Figure 19 The diameter of the hydrogel fibers prepared at different propulsion speeds in Comparative Example 3 is shown. Detailed Implementation

[0062] The preferred embodiments of the present invention are described below. It should be understood that the embodiments are for better explanation of the present invention and are not intended to limit the present invention.

[0063] Source of raw materials

[0064] Sodium alginate, sodium carboxymethyl cellulose, acrylamide, ammonium persulfate, and N,N,N′,N′-tetramethylethylenediamine were purchased from Sinopharm Chemical Reagent Co., Ltd.; N,N′-methylenebisacrylamide was purchased from Shanghai Bailingwei Chemical Technology Co., Ltd.; silk fibroin was purchased from Suzhou Smet Biotechnology Co., Ltd.; quercetin (98% purity) and chitosan quaternary ammonium salt (98% purity) were purchased from Maclean's Reagent Co., Ltd.

[0065] Example 1

[0066] A spinning apparatus for hydrodynamically flexible drawn hydrogel fibers according to the present invention is shown in the attached document. Figure 1 The device includes a spinning solution injection mechanism, a vortex device mechanism, and a coagulation and drawing mechanism. The vortex device mechanism is used to form a vortex rotating at a certain speed in the coagulation mechanism. The spinning solution injection mechanism is used to store the spinning solution and inject the spinning solution into the coagulation mechanism. The spinning solution rapidly crosslinks in the coagulation mechanism to form hydrogel fibers.

[0067] The spinning solution injection mechanism includes an injection pump, a syringe, and a connecting tube. The syringe is used to store the spinning solution, the injection pump is used to drive the flow of the spinning solution in the syringe, the connecting tube is used to connect the syringe to the coagulation mechanism, and the coagulation and stretching device is used to hold the coagulation bath solution and receive the spinning solution.

[0068] The eddy current device is a magnetic stirring device that uses magnetic particles to form a high-speed rotating eddy current. The shear and tensile force field of the circulating coagulation bath solution flexibly stretches the hydrogel fibers.

[0069] Example 2

[0070] A method for preparing hydrodynamically flexible drawn hydrogel fibers, using the apparatus of Example 1, is described below:

[0071] (1) Weigh 0.56g sodium alginate powder and 0.24g sodium carboxymethyl cellulose powder and dissolve them in 40mL of deionized water. Add 0.02g quercetin powder, stir thoroughly and mix evenly to obtain spinning solution. Weigh 15g calcium chloride granules and dissolve them in 500mL of deionized water to obtain a calcium chloride coagulation bath solution with a concentration of 3%.

[0072] (2) The spinning solution from step (1) is loaded into a syringe and then squeezed into the calcium chloride coagulation bath solution at a pushing speed of 0.6 mL / min. The needle used for spinning has a diameter of 0.21 mm, and the magnetic stirring speed is adjusted to 1000 rpm. The hydrogel nascent fibers are stretched by the rapidly rotating water flow to continuously prepare hydrogel fibers of uniform thickness.

[0073] (3) The prepared hydrogel fibers were homogenized in a homogenizer at 13000 rpm for 30 s to obtain a uniformly dispersed hydrogel short fiber dispersion.

[0074] (4) The prepared hydrogel short fiber dispersion was placed and the short fibers settled uniformly due to gravity to obtain a hydrogel fiber network. Then, excess water was filtered out in a constant temperature and humidity chamber at 20℃ and 65% relative humidity, and then freeze-dried at -40℃ for 24h to obtain an unreinforced hydrogel nonwoven material.

[0075] (5) The hydrogel fiber web was impregnated with a 1% silk fibroin solution, then frozen at -40°C for 24 hours. The moisture in the material was then removed by freeze-drying and the silk fibroin was further cross-linked and reinforced by ethanol fumigation to obtain a silk fibroin bond-enhanced hydrogel fiber nonwoven material.

[0076] Example 3

[0077] A method for preparing hydrodynamically flexible drawn hydrogel fibers, using the apparatus of Example 1, is described below:

[0078] (1) Weigh 1.82g sodium alginate, 25g acrylamide and 0.18g chitosan quaternary ammonium salt and dissolve them in 100mL deionized water. Then add 0.03g N,N′-methylenebisacrylamide and stir thoroughly to dissolve to obtain spinning solution. Dissolve 12g anhydrous calcium chloride in 400mL deionized water. Then add 4g chitosan quaternary ammonium salt, 10g ammonium persulfate and 200μL N,N,N′,N′-tetramethylethylenediamine and stir to dissolve to obtain coagulation bath solution.

[0079] (2) The spinning solution was loaded into a syringe and then extruded into the coagulation bath solution at a speed of 1 mL / min. The needle used for spinning had a diameter of 0.26 mm and the magnetic stirring speed was adjusted to 1000 rpm. The hydrogel nascent fibers were stretched by the rapidly rotating water flow to continuously prepare hydrogel fibers of uniform thickness. The fibers were then soaked in the coagulation bath solution for 4 h to fully crosslink and obtain hydrogel fibers with a double network structure.

[0080] (3) The prepared hydrogel fibers were homogenized in a homogenizer at 13000 rpm for 30 s to obtain a uniformly dispersed hydrogel short fiber dispersion.

[0081] (4) The prepared hydrogel short fiber dispersion was placed in a container, and the short fibers settled uniformly due to gravity to obtain a hydrogel fiber web. Then, it was dried in a constant temperature and humidity chamber at 20℃ and 65% relative humidity to remove excess moisture, and then freeze-dried at -40℃ for 24h to obtain an unreinforced hydrogel nonwoven material.

[0082] (5) The hydrogel nonwoven material was reinforced by using a 1% silk fibroin solution and further crosslinked and reinforced by ethanol fumigation to obtain a silk fibroin-reinforced hydrogel-based nonwoven material.

[0083] Example 4

[0084] The mechanical properties of the hydrogel fibers of Examples 1 and 2 were tested using an XQ-2 fiber tensile strength tester. The test conditions were: clamping distance 20 mm and tensile speed 10 mm / min.

[0085] The results obtained are as follows Figure 2 As shown, the tensile strength of the hydrogel fiber in Example 2 is much greater than that in Example 1.

[0086] Compare with Example 1

[0087] In Example 2, the propulsion speed was adjusted to 0.2 mL / min, 0.4 mL / min, 0.6 mL / min, 0.8 mL / min, and 1 mL / min, while other parameters remained unchanged, resulting in hydrogel fibers of different diameters. The morphologies of the hydrogel fibers prepared at different propulsion speeds are shown below. Figure 2 As shown, the fiber diameter increases with increasing propulsion speed.

[0088] Table 1. Hydrogel fiber diameters obtained at different propulsion speeds in Example 2.

[0089] Advance rate mL / min 0.2 0.4 0.6 0.8 1 Diameter pm 32.6±5.8 53.1±4.4 65.2±8.7 76.3±9.8 92.5±9.6

[0090] Constructing hydrogel fiber nonwoven materials for wound dressings requires selecting hydrogel fibers of appropriate diameter. When the hydrogel fiber diameter is greater than 75 μm, the pore size of the nonwoven material is large, resulting in loose adhesion between fibers and difficulty in forming a stable nonwoven material. When the hydrogel fiber diameter is less than 55 μm, the pore size of the nonwoven material is small, resulting in tight adhesion between fibers and low water or oxygen transport efficiency. Therefore, while keeping other parameters constant, the reaction rate should be adjusted to 0.6 mL / min to obtain a nonwoven material with moderate pore size, stability, and high water or oxygen transport efficiency.

[0091] Compare with Example 2

[0092] In Example 2, the magnetic stirring speed was adjusted to 0 rpm, 750 rpm, 1000 rpm, and 1250 rpm, while other parameters remained constant, resulting in hydrogel fibers of different diameters. The morphologies of the hydrogel fibers prepared at different magnetic stirring speeds are shown below. Figure 3 As shown, the fiber diameter becomes thinner as the magnetic stirring speed increases.

[0093] Table 2. Hydrogel fiber diameters obtained at different magnetic stirring speeds in Example 2.

[0094] Agitation rate rpm 0 750 1000 1250 Diameter pm 167.6±15.2 84.8±6.1 65.2±8.7 55.3±6.5

[0095] Constructing hydrogel fiber nonwoven materials for wound dressings requires selecting hydrogel fibers of appropriate diameter. When the hydrogel fiber diameter is greater than 75 μm, the pore size of the nonwoven material is large, resulting in loose adhesion between fibers and difficulty in forming a stable nonwoven material. When the hydrogel fiber diameter is less than 55 μm, the pore size of the nonwoven material is small, resulting in tight adhesion between fibers and lower efficiency in moisture or oxygen transport. Therefore, while keeping other parameters constant, the magnetic stirring speed should be adjusted to 1000 rpm.

[0096] Compare with Example 3

[0097] The propulsion speed in Example 3 was adjusted to 0.25 mL / min, 0.5 mL / min, 0.75 mL / min, 1 mL / min, and 1.5 mL / min, while keeping other parameters constant, to obtain hydrogel fibers of different diameters. The morphologies of the hydrogel fibers prepared at different propulsion speeds are shown below. Figure 4 As shown, the fiber diameter increases with increasing propulsion speed.

[0098] Table 3. Hydrogel fiber diameters obtained at different propulsion speeds in Example 3.

[0099] Advance rate mL / min 0.25 0.5 0.75 1 1.5 Diameter pm 19.8±5.5 20.9±7.1 27.0±7.8 27.4±9.1 57.1±10.6

[0100] The dual-network hydrogel fibers in Example 3 are composed of interwoven cross-linked networks, resulting in looser adhesion between fibers. Therefore, it is necessary to select hydrogel fibers with finer diameters to construct the nonwoven material. Thus, while keeping other parameters constant, the reaction rate should be adjusted to 0.75–1 mL / min.

[0101] Although the present invention has been disclosed above with reference to preferred embodiments, it is not intended to limit the present invention. Anyone skilled in the art can make various modifications and alterations without departing from the spirit and scope of the present invention. Therefore, the scope of protection of the present invention should be defined by the claims.

Claims

1. A method for preparing hydrodynamically flexible drawn hydrogel fibers, characterized in that, Includes the following steps: (1) Sodium alginate, acrylamide, chitosan quaternary ammonium salt, and N,N′-methylenebisacrylamide are dissolved in water to obtain a spinning solution, and calcium chloride, chitosan quaternary ammonium salt, ammonium persulfate, and N,N,N′,N′-tetramethylethylenediamine are dissolved in water to obtain a coagulation bath solution. The spinning solution, by weight, comprises 1-3 parts sodium alginate, 20-27 parts acrylamide, 0.1-0.2 parts chitosan quaternary ammonium salt, 0.01-0.05 parts N,N′-methylenebisacrylamide, and 80-120 parts water; the coagulation bath solution, by weight, comprises 10-15 parts calcium chloride, 2-5 parts chitosan quaternary ammonium salt, 8-15 parts ammonium persulfate, and 350-450 parts water. (2) The spinning injection mechanism injects the spinning solution into the coagulation and stretching device through the connecting tube at a propulsion speed of 0.6 to 1 mL / min. The spinning solution is rapidly cross-linked and solidified in the coagulation bath solution at a stirring speed of 800 to 1200 rpm to form hydrogel fibers. (3) Homogenize the prepared hydrogel fibers to obtain a uniformly dispersed hydrogel short fiber dispersion; (4) The prepared hydrogel short fiber dispersion was allowed to stand to obtain a hydrogel fiber web, which was then dried to obtain an unreinforced hydrogel nonwoven material. (5) Unreinforced hydrogel nonwoven material was impregnated with silk fibroin solution, dried, and then fumigated with ethanol to obtain hydrogel fiber nonwoven material.

2. A hydrogel fiber prepared according to the method of claim 1.

3. The application of the hydrogel fiber described in claim 2 in the fields of preparing biomedical materials, wastewater treatment, and flexible sensors.

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