CN110542683B - Photopolymerisable gel capable of realizing color self-feedback hardness distribution, preparation method and application - Google Patents
Photopolymerisable gel capable of realizing color self-feedback hardness distribution, preparation method and application Download PDFInfo
- Publication number
- CN110542683B CN110542683B CN201910909447.3A CN201910909447A CN110542683B CN 110542683 B CN110542683 B CN 110542683B CN 201910909447 A CN201910909447 A CN 201910909447A CN 110542683 B CN110542683 B CN 110542683B
- Authority
- CN
- China
- Prior art keywords
- gel
- hardness
- cell
- scaffold
- distribution
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
- G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
- G01N21/78—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator producing a change of colour
Landscapes
- Physics & Mathematics (AREA)
- Chemical & Material Sciences (AREA)
- Biochemistry (AREA)
- General Health & Medical Sciences (AREA)
- Plasma & Fusion (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Analytical Chemistry (AREA)
- Engineering & Computer Science (AREA)
- Chemical Kinetics & Catalysis (AREA)
- General Physics & Mathematics (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Apparatus Associated With Microorganisms And Enzymes (AREA)
- Micro-Organisms Or Cultivation Processes Thereof (AREA)
- Polymerisation Methods In General (AREA)
Abstract
The invention discloses a light polymerization gel with color self-feedback hardness distribution and a preparation method thereof, wherein the gel is used for a cell scaffold, and the preparation steps of the gel are as follows: preparing a pre-polymerization solution; pouring the prepolymerization solution into two glass sheets which are arranged in parallel, and irradiating by using 365nm ultraviolet light to polymerize the solution; in the process, 254nm and 365nm ultraviolet light can be used for regulating and controlling the mechanical property of the gel to obtain the cell scaffold with regionalized distribution of the mechanical property. The hardness and distribution of the modified cell scaffold will be visualized in color, and the hardness distribution on the scaffold is read in situ by taking a photograph. The method is applied to various cell culture systems, controls the properties of the microenvironment in real time, and guides the behavior of cells on the microenvironment in situ. Under the conditions of not opening the chip and not adding detection equipment, the mechanical parameters of the regulated cell scaffold and the relation between the cell behavior and the scaffold property are directly obtained through color analysis, and the method has great application potential.
Description
Technical Field
The invention relates to an intelligent cell scaffold for microenvironment in-situ regulation and sensing in an organ chip and a preparation method thereof, belongs to the field of biological materials, and particularly relates to a gel with photopolymerisable color and self-feedback hardness distribution, a preparation method and application thereof.
Background
An organ chip is a new technology for realizing the function of simulating human organs by three-dimensional culture of cells in an in-vitro chip. The organ chip has wide application prospect in the fields of new drug research and development, disease models, personalized medicine, aerospace medicine and the like. In 2016, organ chips were listed as "ten new technologies" by the Darwos economic forum. One of the most challenging links in drug development is how to test the effectiveness and safety of drugs. Cell and animal experiments are two experiment platforms widely used in the current drug research and development and evaluation processes, the former is difficult to simulate the human body microenvironment, and the latter is complex, expensive, time-consuming and has ethical debate. Therefore, economical, efficient animal or clinical replacement experiments are necessary. Organ chips are a new experimental method for drug evaluation which has been proposed in recent years.
The organ chip is a three-dimensional cell culture system based on a microfluid chip and mainly comprises a cover plate, a base plate, a flow channel and a cell culture area. The cell culture zone consists of cells, cell microenvironment, detection system and other parts. Wherein the microenvironment is a very important component thereof, and the microenvironment is mainly composed of the cell scaffold material and the culture medium. The cell scaffold can simulate extracellular matrix (ECM), can control cell behaviors by regulating the function of the scaffold, and becomes a key element in the fields of tissue engineering, regenerative medicine, drug screening, organ chips and the like. Among them, hydrogels having superior characteristics of easy manufacturing, high water content and variable physicochemical properties are used to mimic the properties of ECM, which has attracted much attention.
The most important challenge in the aspects of regulation and detection of the current organ chip is that the organ chip is an enclosed system after being assembled, and the microenvironment inside the organ chip cannot be regulated or detected through an enclosed cover plate or a substrate by a conventional detection means. In order to realize detection, the interface of the detection system needs to be designed on the chip in advance, which increases the complexity of the chip on one hand, and on the other hand, the spatial distribution of each parameter in the microenvironment is still difficult to detect in this way.
Disclosure of Invention
The technical problem is as follows: aiming at the defects of the prior art, the invention provides an intelligent cell scaffold with in-situ regulation and sensing functions and a preparation method thereof, wherein the intelligent cell scaffold can be used in an organ chip. The intelligent cell scaffold prepared by the method can adjust the mechanical property of the intelligent cell scaffold in a closed chip through light control, so that a cell culture area in the chip can generate an anisotropic microenvironment in real time, and different cell forms can be obtained. In addition, the mechanical property and the cell growth state of the bracket can be directly obtained through the color of the bracket under the condition of not opening the chip and not adding detection equipment, so that the effect of the cells and the bracket is easy to observe and study.
The technical scheme is as follows: in order to realize the purpose, the invention provides a gel with photopolymerisable color self-feedback hardness distribution, a preparation method and application thereof.
The invention discloses a gel with photopolymerisable color and self-feedback hardness distribution; the gel visually obtains the hardness distribution through color change. The gel can visually obtain the hardness distribution through color change, and has wide application range and simple operation. The gel can directly obtain the hardness distribution of each position of the gel through color change without additional detection equipment.
The invention discloses application of a gel with photopolymerisable color and self-feedback hardness distribution, and the gel is used for a cell scaffold. The support can realize in-situ regulation and sensing of cell growth environment.
The invention discloses a preparation method of a gel with photopolymerisable color and self-feedback hardness distribution, which comprises the following steps:
1) preparing gel pre-polymerization liquid; the specific method comprises the following steps: taking acrylamide (8-15 wt%), methylene bisacrylamide (Bis)/polyethylene glycol diacrylate (PEGDA700) (0.08-0.45 wt%), photoinitiator (2959) (0.08-0.45 wt%), monodisperse silicon dioxide particles (26-34 vol%) and the like as raw materials, taking water as a solvent, and ultrasonically mixing uniformly to prepare a pre-polymerization solution;
2) on the basis of the pre-polymerization solution prepared in the step 1), pouring the pre-polymerization solution into a slide clamp (with the thickness of a gasket being 10-125 mu m), polymerizing to form a film under the condition of 365nm ultraviolet illumination, and gradually increasing the illumination time from 10s to 30min to prepare gel films with different colors and hardness;
3) on the basis of the gel film prepared in the step 2), a gray mask is placed on the surface of the film, and the gel with regionalized distribution characteristics of hardness and color is obtained under 365nm ultraviolet illumination.
The other technical scheme of the preparation method of the invention is as follows: step 1) preparing gel pre-polymerization liquid; the specific method comprises the following steps: acrylamide (8-15 wt%), Bis/PEGDA700(0.08-0.45 wt%), photoinitiator (2959) (0.08-0.45 wt%), silicon dioxide particles (26-34 vol%), 7-acryloyloxy amino-4-methylcoumarin (2-4 wt%) and the like are used as raw materials, DMSO is used as a solvent, and the raw materials are uniformly mixed to prepare a pre-polymerization solution;
step 2) on the basis of the pre-polymerization solution prepared in the step 1), filling the pre-polymerization solution into a slide clamp (with the thickness of a gasket being 25-125 mu m), and irradiating by using 365nm ultraviolet light to prepare a light-adjustable intelligent gel film;
and 3) on the basis of the intelligent gel film prepared in the step 2), placing the film in a pre-designed organ chip, and irradiating and partially depolymerizing the film by 254nm ultraviolet light through a gray mask or different illumination time when the mechanical property of the film needs to be changed to obtain the anisotropic intelligent gel films with different hardness. The dicoumarin is depolymerized by 254nm ultraviolet light, the hardness of the gel is regulated, and the intelligent gel film with regionally distributed hardness can be obtained by carrying out patterned depolymerization on the gel by using a gray mask. For the depolymerized film, ultraviolet irradiation at 365nm can be used for recombining coumarin, so that the hardness of the gel is improved, and the hardness change is also shown in a color change mode.
On the basis of the steps 3) and 6), when the regulated and controlled mechanical property distribution of the gel needs to be obtained, a camera is used for imaging the gel, and the hardness distribution of the gel can be obtained by analyzing the hues of different areas on the photo.
The gel can directly obtain the hardness distribution of each position of the gel through color change without additional detection equipment. The intelligent gel capable of optically controlling in-situ regulation and sensing is used as a cell culture support, the hardness of the support can be regulated and controlled in situ through photochemical reaction, so that the attachment and growth forms of cells on the surface of the support are different, and the distribution information of the hardness of the support can be directly obtained without an external instrument. The application of the intelligent bionic cell scaffold capable of optically controlling in-situ regulation and sensing in an organ chip can regulate and control the internal cell scaffold in situ through ultraviolet irradiation under the condition of not opening the chip, so that the mechanical property of the internal cell scaffold generates in-situ and area-controllable changes, the cell behavior in the chip is influenced, and the cell morphology can be directly observed in the chip and color data can be read to obtain the information of the relationship between the cell growth state and the substrate property.
Wherein:
the further technical scheme of the invention is as follows: subjecting the prepolymerization solution obtained in the step 1) to ultrasonic treatment for 5 minutes.
The further technical scheme of the invention is as follows: the composition of the prepolymerization solution in the step 1) comprises but is not limited to substances such as acrylamide, Bis/PEGDA700, a photoinitiator (2959), silica particles, coumarin acrylate, water and DMSO (dimethyl sulfoxide).
The further technical scheme of the invention is as follows: the ultraviolet illumination condition in the step 2) refers to that the wavelength of the ultraviolet light is 365nm, and the illumination time is increased in a gradient manner from 10s to 30 min.
The further technical scheme of the invention is as follows: the ultraviolet illumination condition in the step 2) refers to ultraviolet light with the wavelength of 254nm and the illumination intensity of 0.1-10mW/cm-2The illumination time is 10s-30 min.
Has the advantages that: compared with the prior art, the invention has the following advantages:
1. the invention provides an intelligent cell scaffold for microenvironment in-situ regulation and sensing in an organ chip and a preparation method thereof. The method can be applied to cell culture scaffolds in various organ chips.
2. According to the intelligent cell scaffold for in-situ microenvironment regulation and sensing in the organ chip, disclosed by the invention, the mechanical property of the scaffold can be regulated in a closed chip through light control, so that a cell culture area in the chip can generate an anisotropic microenvironment in real time, and different cell forms can be obtained.
3. According to the intelligent cell scaffold for in-situ microenvironment regulation and sensing in the organ chip, provided by the invention, the mechanical property and the cell growth state of the scaffold can be directly obtained through colors under the conditions that the chip is not opened and detection equipment is not additionally arranged.
4. Firstly, preparing a pre-polymerization solution according to a pre-calculated formula; then, the prepolymer solution was poured into two glass plates placed in parallel and polymerized by irradiation with 365nm ultraviolet light. In the using process, the mechanical property of the gel can be regulated and controlled by 254nm and 365nm ultraviolet light, and the cytoskeleton with regionalized distribution of the mechanical property can be obtained by masking or controlling the local illumination time. Meanwhile, the hardness and the distribution of the modified cell scaffold can be displayed in a color mode, and the hardness distribution on the scaffold can be read in situ by taking a picture. The method can be applied to various cell culture systems, such as cell culture plates, microarrays and microfluidic organ chips, and can regulate the mechanical property of the bracket by light control in a closed environment, control the property of a microenvironment in real time and guide the behavior of cells on the bracket in situ. In addition, the mechanical parameters of the regulated cell scaffold and the relation between the cell behavior and the scaffold property can be directly obtained through color analysis under the conditions that the chip is not opened and detection equipment is not additionally arranged, and the method has great application potential.
Drawings
FIG. 1 is a diagram of color change and mechanical property change of an intelligent support provided by the invention under the regulation and control of ultraviolet light;
FIG. 2 is a diagram showing the use of the cell scaffold of the present invention in an organ chip;
FIG. 3 is a photograph of the cultured cells on the scaffold of the chip of FIG. 2 observed under a microscope;
FIG. 4 is a graph comparing the calculated elastic modulus fit value from the hue distribution of the gel with the elastic modulus distribution obtained by an indenter.
Detailed Description
The present invention will be further illustrated with reference to the accompanying drawings and specific examples, which are carried out on the premise of the technical solution of the present invention, and it should be understood that these examples are only for illustrating the present invention and are not intended to limit the scope of the present invention.
Example 1
1) Acrylamide (7.00mg), Bis/PEGDA700(0.08mg) and photoinitiator 2959(0.08mg) were added to the water-dispersed silica nanoparticles (90 μ L, Φ 152nm, 30 vol%); obtaining a pre-polymerization solution;
2) carrying out ultrasonic treatment on the prepolymerization liquid obtained in the step 1) for 5 minutes;
3) on the basis of 2), uniformly penetrating a pre-polymerization solution into a gap between two parallel glasses separated by a capillary force, wherein the gap thickness is 25 mu m, and then exposing the pre-polymerization solution to ultraviolet light with the lambda being 365nm for 10s, 30s, 45s, 60s and 120s to photopolymerize the monomer; thereby obtaining hydrogel films of different colors and hardnesses;
4) to increase cell affinity, gelatin was grafted onto the surface of the hydrogel membrane of 3). The hydrogel films were then sterilized in 75% ethanol in petri dishes, sterile PBS for at least 3 hours and cell culture medium for 1 hour; the cell culture medium was removed and fresh cell culture medium was injected.
HeLa cells were cultured in a 24-well plate in a medium containing 10% Fetal Bovine Serum (FBS) and 1% penicillin-streptomycin at 37 ℃ with 5% CO2Culturing in atmosphere; subsequently, the pretreated cells were incubated at 2X 105Suspension of individual cells/mL on the surface of the hydrogel and incubation for 24 hours; obtaining the cell scaffold.
Example 2
1) Acrylamide (10.00mg), Bis/PEGDA700(0.2mg) and photoinitiator 2959(0.2mg) were added to the water-dispersed silica nanoparticles (90 μ Ι _, Φ 152nm, 34 vol%); obtaining a pre-polymerization solution;
2) carrying out ultrasonic treatment on the prepolymerization liquid obtained in the step 1) for 5 minutes;
3) on the basis of 2), uniformly penetrating a pre-polymerization solution into a gap between two parallel glasses separated by a capillary force, wherein the gap thickness is 50 microns, and then exposing the pre-polymerization solution to ultraviolet light with the lambda being 365nm for 10s, 30s, 45s, 60s and 120s to photopolymerize the monomer; thereby obtaining hydrogel films of different colors and hardnesses;
4) to increase cell affinity, gelatin was grafted onto the surface of the hydrogel membrane of 3). The hydrogel films were then sterilized in 75% ethanol in petri dishes, sterile PBS for at least 3 hours and cell culture medium for 1 hour; the cell culture medium was removed and fresh cell culture medium was injected.
5) HeLa cells were cultured in a 24-well plate in a medium containing 10% Fetal Bovine Serum (FBS) and 1% penicillin-streptomycin at 37 ℃ with 5% CO2Culturing in atmosphere; subsequently, the pretreated cells were incubated at 2X 105Individual cell or cellmL was suspended on the surface of the hydrogel and incubated for 24 hours; obtaining the cell scaffold.
Example 3
1) Acrylamide (14.00mg), 7-acryloyloxyamino-4-methylcoumarin (2.00mg), Bis/PEGDA700(0.45mg) and photoinitiator 2959(0.45mg) were added to dimethylsulfoxide-dispersed silica nanoparticles (120 μ L, Φ 152nm, 26 vol%); obtaining the pre-polymerized liquid.
2) Carrying out ultrasonic treatment on the prepolymerization liquid obtained in the step 1) for 5 minutes;
3) on the basis of 2), uniformly permeating the pre-polymerization solution into a space between two parallel glasses separated by a capillary force, wherein the thickness of the space is 75 microns, and then exposing the space to ultraviolet light with the lambda being 365nm for 5min to carry out photopolymerization on the monomers; a photo-controllable hydrogel film is thus obtained.
4) To increase cell affinity, gelatin was grafted onto the surface of the hydrogel membrane. The hydrogel films were then sterilized in 75% ethanol in petri dishes, sterile PBS for at least 3 hours and cell culture medium for 1 hour. The cell culture medium was removed and fresh cell culture medium was injected.
5) The film is placed in a cell culture area of the organ chip, and then the gel is exposed to ultraviolet light with the lambda being 254nm for different time periods of 5min, 10min and 30min, so that the gel has different colors and different mechanical properties. (see fig. 2)
6) In the organ chip cell culture area, HeLa cells were cultured in a medium containing 10% Fetal Bovine Serum (FBS) and 1% penicillin-streptomycin at 37 ℃ under 5% CO2Culturing in atmosphere. Subsequently, the pretreated cells were incubated at 2X 105Suspension of individual cells/mL on the surface of the hydrogel and incubation for 24 hours; obtaining the cell scaffold.
Example 4
1) Acrylamide (15.00mg), 7-acryloyloxyamino-4-methylcoumarin (4.00mg), Bis/PEGDA700(1mg) and photoinitiator 2959(0.30mg) were added to dimethylsulfoxide-dispersed silica nanoparticles (120 μ L, Φ 152nm, 29 vol%); obtaining the pre-polymerized liquid.
2) Carrying out ultrasonic treatment on the prepolymerization liquid obtained in the step 1) for 5 minutes;
3) on the basis of 2), uniformly permeating the pre-polymerization solution into a space between two parallel glasses separated by capillary force, wherein the thickness of the space is 100 mu m, and then exposing the space to ultraviolet light with the lambda being 365nm for 5min to carry out photopolymerization on the monomers; a photo-controllable hydrogel film is thus obtained.
4) To increase cell affinity, gelatin was grafted onto the surface of the hydrogel membrane. The hydrogel films were then sterilized in 75% ethanol in petri dishes, sterile PBS for at least 3 hours and cell culture medium for 1 hour. The cell culture medium was removed and fresh cell culture medium was injected.
5) The film is placed in a cell culture area of the organ chip, and then the gel is exposed to ultraviolet light with lambda being 254nm for different time periods of 2min, 4min and 5min, so that the gel has different colors and different mechanical properties. (see fig. 2)
In the organ chip cell culture area, HeLa cells were cultured in a medium containing 10% Fetal Bovine Serum (FBS) and 1% penicillin-streptomycin at 37 ℃ under 5% CO2Culturing in atmosphere. Subsequently, the pretreated cells were incubated at 2X 105Suspension of individual cells/mL on the surface of the hydrogel and incubation for 24 hours; obtaining the cell scaffold.
Example 5
1) Acrylamide (7.00mg), 7-acryloyloxyamino-4-methylcoumarin (1.00mg), Bis/PEGDA700(1mg) and photoinitiator 2959(0.30mg) were added to dimethylsulfoxide-dispersed silica nanoparticles (120 μ L, Φ 152nm, 33 vol%); obtaining a pre-polymerization solution;
2) carrying out ultrasonic treatment on the prepolymerization liquid obtained in the step 1) for 5 minutes;
3) on the basis of 2), the prepolymer solution was uniformly infiltrated into the space between two parallel glasses spaced apart by capillary force with a gap thickness of 125 μm, and then exposed to uv light with λ -365 nm for 5min to photopolymerize the monomer. A photo-controllable hydrogel film is thus obtained.
4) An anisotropic gel was obtained by placing a dot matrix mask on the film and then exposing it to uv light at λ 254nm for 5 min.
5) To increase cell affinity, gelatin was grafted onto the surface of the hydrogel membrane. The hydrogel films were then sterilized in 75% ethanol in petri dishes, sterile PBS for at least 3 hours and cell culture medium for 1 hour. The cell culture medium was removed and fresh cell culture medium was injected.
6) HeLa cells were cultured in a 24-well plate in a medium containing 10% Fetal Bovine Serum (FBS) and 1% penicillin-streptomycin at 37 ℃ with 5% CO2Culturing in atmosphere. Subsequently, the pretreated cells were incubated at 2X 105Suspension of individual cells/mL on the surface of the hydrogel and incubation for 24 hours; obtaining the cell scaffold.
Example 6
1) Acrylamide (7.00mg), coumarin acrylate (1.00mg), Bis/PEGDA700(1mg) and photoinitiator 2959(0.30mg) were added to dimethylsulfoxide-dispersed silica nanoparticles (90 μ L, Φ 152nm, 29 vol%); obtaining the pre-polymerized liquid.
2) Carrying out ultrasonic treatment on the prepolymerization liquid obtained in the step 1) for 5 minutes;
3) on the basis of 2), the solution was uniformly infiltrated by capillary force into the space between two parallel glasses spaced apart with a gap thickness of 25 μm, and then the monomers were photopolymerized by exposure to uv light at λ 365nm for 5 min. A photo-controllable hydrogel film is thus obtained.
4) A gray mask was placed on the film, and then exposed to uv light at λ 254nm for 5min, thereby obtaining an anisotropic gel.
5) To increase cell affinity, gelatin was grafted onto the surface of the hydrogel membrane. The hydrogel films were then sterilized in 75% ethanol in petri dishes, sterile PBS for at least 3 hours and cell culture medium for 1 hour. The cell culture medium was removed and fresh cell culture medium was injected.
6) HeLa cells were cultured in a 24-well plate in a medium containing 10% Fetal Bovine Serum (FBS) and 1% penicillin-streptomycin at 37 ℃ with 5% CO2Culturing in atmosphere. Subsequently, the pretreated cells were incubated at 2X 105The individual cells/mL concentration were suspended on the surface of the hydrogel and incubated for 24 hoursWhen the current is over; obtaining the cell scaffold.
Example 7
The smart stent described in examples 1-6 was used; as is evident from fig. 1, the wavelength of the reflection peak of the gel film shifts significantly after different depolymerization times. Hardness also decreases regularly with increasing degree of depolymerization. As shown in fig. 2, it is obvious that in the chip, the gel can be adjusted and controlled in hardness by light without opening the chip, and can be self-fed back by color. As is evident from FIG. 3, the results obtained by culturing cells on gels with different controlled hardness are different, and the hard gels are more suitable for cell adhesion growth. As shown in fig. 4, it is obvious that the hardness of the gel can be directly calculated by the hue of the color, and the hardness information can be read by the color when the gel is applied to the chip.
It should be noted that, for those skilled in the art, without departing from the principle of the present invention, several improvements and modifications can be made, and these improvements and modifications should also be construed as the protection scope of the present invention.
Claims (7)
1. A photopolymerisable, colorable, self-feedbackable hardness-distributing gel characterized by: the gel intuitively obtains the hardness distribution through color change, and the preparation method comprises the following steps:
step 1) preparing gel pre-polymerization liquid; the specific method comprises the following steps: taking 8-15 wt% of acrylamide, 0.08-0.45 wt% of methylene bisacrylamide/polyethylene glycol diacrylate, 0.08-0.45 wt% of photoinitiator and 26-34 vol% of silicon dioxide particles as raw materials, and taking water as a solvent, and uniformly mixing to prepare a pre-polymerization solution;
step 2) on the basis of the pre-polymerized liquid prepared in the step 1), pouring the pre-polymerized liquid into a slide clamp, wherein the thickness of a gasket is 10-125 mu m, and polymerizing the pre-polymerized liquid into a film under the condition of ultraviolet illumination to prepare gel films with different colors and hardness;
and 3) on the basis of the gel film prepared in the step 2), placing a gray mask on the surface of the film, and obtaining the gel with regionalized distribution characteristics of hardness and color under 365nm ultraviolet illumination.
2. A photopolymerisable, colorable, self-feedbackable hardness-distributing gel as claimed in claim 1, wherein: subjecting the prepolymerization solution obtained in the step 1) to ultrasonic treatment for 5 minutes.
3. The gel of claim 1, wherein: the ultraviolet illumination condition in the step 2) refers to that the wavelength of the ultraviolet light is 365nm, and the illumination time is increased in a gradient manner from 10s to 30 min.
4. The gel of claim 1, wherein: the ultraviolet illumination condition in the step 2) refers to ultraviolet light with the wavelength of 254nm and the illumination intensity of 0.1-10mW/cm-2The illumination time is 10s-30 min.
5. Use of a photopolymerisable colour self-feedback hardness-distributing gel according to any one of claims 1 to 4, characterized in that: the gel with the photopolymerisable color self-feedback hardness distribution is used for a cell culture scaffold.
6. A gel with adjustable light concentration and color self-feedback hardness distribution is characterized in that: the gel intuitively obtains the hardness distribution through color change, and the preparation method comprises the following steps:
step 1) preparing gel pre-polymerization liquid; the specific method comprises the following steps: taking 8-15 wt% of acrylamide, 0.08-0.45 wt% of methylene bisacrylamide/polyethylene glycol diacrylate, 0.08-0.45 wt% of photoinitiator, 26-34 vol% of silicon dioxide particles and 2-4 wt% of 7-acryloxy amino-4-methylcoumarin as raw materials, and taking DMSO as a solvent, and uniformly mixing to prepare a pre-polymerization solution;
step 2) on the basis of the pre-polymerization solution prepared in the step 1), pouring the pre-polymerization solution into a slide clamp, wherein the thickness of a gasket is 10-125 mu m, and irradiating by using ultraviolet light to prepare a light-adjustable intelligent gel film;
and 3) on the basis of the intelligent gel film prepared in the step 2), irradiating by ultraviolet with the wavelength of 254nm through a gray mask or different illumination time to depolymerize dicoumarol so as to obtain the anisotropic intelligent gel film with different hardness.
7. The gel of claim 6, wherein: subjecting the prepolymerization solution obtained in the step 1) to ultrasonic treatment for 5 minutes.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910909447.3A CN110542683B (en) | 2019-09-25 | 2019-09-25 | Photopolymerisable gel capable of realizing color self-feedback hardness distribution, preparation method and application |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910909447.3A CN110542683B (en) | 2019-09-25 | 2019-09-25 | Photopolymerisable gel capable of realizing color self-feedback hardness distribution, preparation method and application |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN110542683A CN110542683A (en) | 2019-12-06 |
| CN110542683B true CN110542683B (en) | 2022-03-11 |
Family
ID=68714473
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201910909447.3A Active CN110542683B (en) | 2019-09-25 | 2019-09-25 | Photopolymerisable gel capable of realizing color self-feedback hardness distribution, preparation method and application |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN110542683B (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112485247B (en) * | 2020-11-20 | 2022-04-26 | 南京鼓楼医院 | Structure color microfiber of heterostructure, preparation method of microstructure color microfiber and myocardial cell detection method |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1362442A (en) * | 2001-01-04 | 2002-08-07 | 中国科学院化学研究所 | Prepn of ordered porous material comprising ordered polymer and inorganic heterocomplex and its derivative |
| JP2005169243A (en) * | 2003-12-10 | 2005-06-30 | Fujikura Ltd | Gas separation membrane and method for producing the same |
| CN101315369A (en) * | 2008-07-08 | 2008-12-03 | 东南大学 | Color and shape compositely encoded hydrogel multi-component immune detection method |
| CN102590185A (en) * | 2012-01-11 | 2012-07-18 | 东南大学 | Colloidal crystal gel label-free visual detection method with aptamer as identification unit |
| CN102675531A (en) * | 2011-03-07 | 2012-09-19 | 孟子晖 | Molecularly-imprinted photonic crystal for detecting organophosphorus toxicants |
| CN104672485A (en) * | 2015-02-13 | 2015-06-03 | 华中科技大学 | Photonic crystal thin film as well as preparation method and application thereof |
| CN105294955A (en) * | 2015-10-23 | 2016-02-03 | 华中科技大学 | Photo-curing hydrogel for multi-cell sorting and stem cell area-selecting differentiation and preparation method thereof |
-
2019
- 2019-09-25 CN CN201910909447.3A patent/CN110542683B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1362442A (en) * | 2001-01-04 | 2002-08-07 | 中国科学院化学研究所 | Prepn of ordered porous material comprising ordered polymer and inorganic heterocomplex and its derivative |
| JP2005169243A (en) * | 2003-12-10 | 2005-06-30 | Fujikura Ltd | Gas separation membrane and method for producing the same |
| CN101315369A (en) * | 2008-07-08 | 2008-12-03 | 东南大学 | Color and shape compositely encoded hydrogel multi-component immune detection method |
| CN102675531A (en) * | 2011-03-07 | 2012-09-19 | 孟子晖 | Molecularly-imprinted photonic crystal for detecting organophosphorus toxicants |
| CN102590185A (en) * | 2012-01-11 | 2012-07-18 | 东南大学 | Colloidal crystal gel label-free visual detection method with aptamer as identification unit |
| CN104672485A (en) * | 2015-02-13 | 2015-06-03 | 华中科技大学 | Photonic crystal thin film as well as preparation method and application thereof |
| CN105294955A (en) * | 2015-10-23 | 2016-02-03 | 华中科技大学 | Photo-curing hydrogel for multi-cell sorting and stem cell area-selecting differentiation and preparation method thereof |
Non-Patent Citations (4)
| Title |
|---|
| "Highly sensitive mechanochromic photonic gel";Ri Hong et al.;《RSC Advances》;20171230;第7卷;第33258-33262 * |
| "Mechanochromic Photonic Gels";Edwin P. Chan et al.;《ADVANCED MATERIALS》;20131230;第29卷;第3934-3945页、附图5 a)-c)、附图8c)-d、附图9b)-c) * |
| "Photo-Dimerization Induced Dynamic Viscoelastic Changes in ABA Triblock Copolymer-Based Hydrogels for 3D Cell Culture";Ryota Tamate et al.;《CHEMISTRY OF MATERIALS》;20160811;第28卷;第6401-6405页 * |
| "Recent advances in colloidal photonic crystal sensors: Materials";Jue Hou et al.;《nanotoday》;20180831;第22卷;第132-144 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN110542683A (en) | 2019-12-06 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Tse et al. | Preparation of hydrogel substrates with tunable mechanical properties | |
| Winston et al. | A system to reproduce and quantify the biomechanical environment of the cell | |
| US10954489B2 (en) | Liver-mimetic device and method for simulation of hepatic function using such device | |
| JP6202621B2 (en) | Cell culture substrate and method for producing the same | |
| US8741645B2 (en) | Test kit comprising a culture instrument with a cell pattern and a gel suitable to embed cell pattern | |
| EP3000836B1 (en) | Photodegradable crosslinking agent | |
| CN110542683B (en) | Photopolymerisable gel capable of realizing color self-feedback hardness distribution, preparation method and application | |
| Murray et al. | Bioimprinted polymer platforms for cell culture using soft lithography | |
| Wang et al. | Gene-modified cell detachment on photoresponsive hydrogels strengthened through hydrogen bonding | |
| Richter et al. | Spatially controlled cell adhesion on three-dimensional substrates | |
| JP2010088316A (en) | Cell culture substrate and cell culture method | |
| Ahmadi et al. | Photo-and thermo-responsive extracellular matrix mimicking nano-coatings prepared from poly (N-isopropylacrylamide)-spiropyran copolymer for effective cell sheet harvesting | |
| Nishiguchi et al. | In Situ 3D-Printing using a Bio-ink of Protein–photosensitizer Conjugates for Single-cell Manipulation | |
| JPH04278083A (en) | Method for forming massive cell body controlled in cell number and cell culture substrate for use therein | |
| Sumaru et al. | Photoresponsive Aqueous Dissolution of Poly (N-Isopropylacrylamide) Functionalized with o-Nitrobenzaldehyde through Phase Transition | |
| JP6721881B2 (en) | Cell scaffold material, cell model, and method for producing cell scaffold material | |
| US8592139B2 (en) | Test method using cells and test kit therefor | |
| De Volder et al. | Biomaterials for studies in cellular mechanotransduction | |
| Starly et al. | UV-Photolithography fabrication of poly-ethylene glycol hydrogels encapsulated with hepatocytes | |
| Rommel | Continuous production of functional microgel building blocks for biocompatible 3D scaffolds | |
| Hughes et al. | Development of a tunable 3D wrinkled platfom for designing cellular three-dimensional communication networks | |
| Samal et al. | Direct deep UV lithography to micropattern PMMA for stem cell culture | |
| DuPont Jr | Shape-shifting surfaces for rapid release and direct stamping of organized micro-tissues | |
| Lee | Polyacrylamide Photo-responsive Hydrogels and Its Application in Cell Biology | |
| González-Henríquez et al. | Wrinkled Surfaces Designed for Biorelated Applications |
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 |