Microfluidic chip design method and device based on viscoelastic fluid binding effect

Abstract

The application discloses a microfluidic chip design method and device based on a viscoelastic fluid binding effect, and the method comprises the following steps: selecting a microfluidic channel capable of effectively utilizing viscoelastic fluid instability to bind droplets; designing the size of the selected microfluidic channel; configuring a displacement fluid according to the size of the known microfluidic channel; constructing a viscoelastic fluid dynamics model according to the known microfluidic channel; determining critical conditions of droplet oscillation binding based on the viscoelastic fluid dynamics model and experimental results; and establishing a microfluidic design criterion based on viscoelastic fluid instability to bind droplets according to the critical conditions of droplet oscillation binding. The application can precisely and controllably realize oscillation binding of droplets based on the instability characteristics and unique microfluidic channel design of the viscoelastic fluid, so that the microfluidic chip with the oscillation binding function has a wider application scenario.

Description

Technical Field

[0001] This invention relates to the fields of fluid mechanics and microfluidics, and in particular to a microfluidic chip design method and apparatus based on the viscoelastic fluid binding effect. Background Technology

[0002] Microfluidics is an advanced technology that precisely manipulates and controls microfluidics through microchannels. Its capabilities are constantly expanding, leading to its widespread application in life sciences, medicine and healthcare, energy and environment, materials science, and chemical engineering. Among these applications, the need to confine research objects using microfluidics is particularly prevalent. Specifically, studies on the mechanical response of single cells require microfluidics to confine single cells; microdroplet in-situ reactors require microfluidics to confine microdroplets; and bubble interface stability studies require microfluidics to confine bubbles. However, currently, there is no effective microfluidic method that can simultaneously, stably, and controllably confine research objects. Furthermore, there is a lack of effective theoretical guidelines to guide the design of microfluidics for achieving confinement functionality.

[0003] Viscoelastic fluids are a class of non-Newtonian fluids that simultaneously possess the properties of viscous fluids and elastic solids. Viscoelastic instability is one of the key characteristics of viscoelastic fluids, referring to the fact that even when inertial effects are negligible (i.e., Reynolds number less than 1), viscoelastic fluids can still exhibit flow instability characteristics such as turbulent streamlines and asymmetric vortices. Due to their elastic properties, when the position or shape of a viscoelastic fluid changes, it accumulates a certain amount of elastic potential energy, and under the influence of this potential energy, it tends to return to its original state; this is also known as the "memory effect" of viscoelastic fluids. Furthermore, when a viscoelastic fluid displaces or carries droplets, bubbles, or particles to form a two-phase flow, and passes through converging or abruptly converging channel structures, the flow at the viscoelastic fluid's leading edge is obstructed by the channel, highlighting its elastic characteristics. This exerts an elastic force on the droplets, bubbles, and particles in the opposite direction of the flow, resulting in a confinement effect that slows down or even stops the flow of these droplets, bubbles, and particles.

[0004] Therefore, by utilizing the unique physical properties of viscoelastic fluids, it is possible to simultaneously and effectively achieve the oscillation and confinement of droplets, bubbles, and particles. Furthermore, by constructing a viscoelastic fluid dynamics model, it is possible to establish effective microfluidic design criteria for viscoelastic fluids, and further reliably control the confinement effect based on the instability of viscoelastic fluids. This is conducive to better meeting the needs of microfluidic technology in fields such as life sciences, medicine and health, energy development, and environmental monitoring, with richer functions and a wider range of applications. Summary of the Invention

[0005] This invention addresses the problem that conventional microfluidic design methods cannot simultaneously, stably, and controllably achieve oscillatory confinement of research objects. It innovatively provides a microfluidic chip design method and device based on the confinement effect of viscoelastic fluids. The viscoelastic fluid and microfluidic technology involved in this method can be applied to simultaneously and effectively confine research objects such as droplets, cells, particles, and bubbles. The microfluidic design criteria based on a viscoelastic fluid dynamics model introduced in this method can further stabilize and reliably control the confinement effect of viscoelastic fluids, while avoiding the limitations of conventional microfluidic design methods, such as the limited availability of microchannel materials and fabrication processes, and the limited applicability of these materials.

[0006] To address the aforementioned technical problems, embodiments of the present invention provide the following solutions:

[0007] On the one hand, a microfluidic chip design method based on the viscoelastic fluid binding effect is provided, including the following steps:

[0008] S1. Select a microfluidic channel that effectively utilizes the instability of viscoelastic fluids to bind droplets;

[0009] S2. Design the dimensions of the selected microfluidic channel;

[0010] S3. Configure the displacement fluid according to the known dimensions of the microfluidic channel;

[0011] S4. Construct a viscoelastic fluid dynamics model based on the known microfluidic channels;

[0012] S5. Determine the critical conditions for droplet oscillation confinement based on the viscoelastic fluid dynamics model and experimental results;

[0013] S6. Establish microfluidic design criteria for confining droplets based on the critical conditions for droplet oscillation confinement.

[0014] Preferably, in step S1, the selected microfluidic channel capable of achieving the confinement function is a confluence channel.

[0015] Preferably, in step S2, the channel dimensions are designed based on the confluence channel model, wherein the confluence channel includes a pore-throat structure, and the equivalent diameter D of the pores... p Larger than the equivalent diameter D of the larynx t ;

[0016] Wherein, the equivalent diameter D of the pores p From the pore width p w and pore depth p d express:

[0017]

[0018] Equivalent diameter D of the larynxt The width of the larynx t w and laryngeal depth t d express:

[0019]

[0020] Preferably, in step S3, nine different displacing fluids are configured, namely displacing liquids, including three Newtonian fluids, two shear-thinning fluids and four viscoelastic fluids.

[0021] Preferably, in step S4, during the process of the viscoelastic fluid displacing the droplets, the droplets are subjected to a viscous force F. v Capillary force F c and elastic force F e The combined effect of these factors, through the adjustment of viscous force F v Capillary force F c and elastic force F e The size relationship between them can be used to achieve droplet oscillation confinement; the viscoelastic fluid dynamics model is as follows:

[0022]

[0023] F e =χDeF v (3)

[0024]

[0025] In the formula, L is the length of the droplet in meters; D is the equivalent diameter of the droplet in meters; η is the viscosity of the viscoelastic fluid in Pascal-second; U is the flow velocity of the viscoelastic fluid in meters per second; τ is the relaxation time of the viscoelastic fluid in seconds; and γ is the interfacial tension coefficient between the viscoelastic fluid and the droplet in Newtons per meter. ψ and χ are the microfluidic channel shape coefficients, dimensionless, with values ​​between 0 and 1; Ca is the capillary number, dimensionless; De is the Deborah number of the viscoelastic fluid, dimensionless; Ec is the number of elastic capillaries, dimensionless.

[0026] Preferably, in step S5, the critical condition for achieving droplet oscillation confinement is:

[0027] F v =F c +F e (7)

[0028] Combining equations (1) and (7), the dimensionless expression of the critical condition for achieving droplet oscillation confinement is obtained as follows:

[0029]

[0030] Based on the experimental results, a linear fit was performed on the data, and the following relationship exists:

[0031] A = m(De - De) crit (9)

[0032]

[0033] In the formula, the subscript crit indicates the critical state; A is the dimensionless oscillation amplitude of the droplet; De crit The critical Deborah number is represented as 1 in this case; m is the microfluidic channel shape coefficient, dimensionless, and takes a value between 0 and 1; that is, the critical condition for achieving droplet oscillation is that the Deborah number of the viscoelastic fluid is equal to the critical Deborah number De. crit ;

[0034] The critical condition for achieving droplet oscillation confinement is to achieve droplet oscillation simultaneously, that is, to satisfy both equations (8) and (10):

[0035]

[0036] Preferably, in step S6, based on the critical conditions for droplet oscillation confinement determined by the viscoelastic fluid dynamics model, the viscoelastic fluid is configured by adjusting the relaxation time, viscosity, flow rate, and interfacial tension coefficient, and microfluidic design is performed by adjusting the size of the microfluidic channel.

[0037] On the other hand, a microfluidic chip design device based on the viscoelastic fluid binding effect is provided, comprising:

[0038] The channel selection module is used to select microfluidic channels that effectively utilize the instability of viscoelastic fluids to bind droplets;

[0039] The size design module is used to design the dimensions of the selected microfluidic channel;

[0040] Displacement fluid configuration module, used to configure displacement fluid according to the known dimensions of microfluidic channels;

[0041] The model building module is used to construct viscoelastic fluid dynamics models based on known microfluidic channels;

[0042] The critical condition determination module is used to determine the critical conditions for droplet oscillation confinement based on the viscoelastic fluid dynamics model and experimental results.

[0043] The design criteria building module is used to establish microfluidic design criteria for confining droplets based on the critical conditions of droplet oscillation confinement.

[0044] On the other hand, an electronic device is provided, comprising a processor and a memory, wherein the memory stores at least one instruction, which is loaded and executed by the processor to implement the microfluidic chip design method described above.

[0045] On the other hand, a computer-readable storage medium is provided, wherein at least one instruction is stored in the storage medium, the at least one instruction being loaded and executed by a processor to implement the above-described microfluidic chip design method.

[0046] The beneficial effects of the technical solutions provided in the embodiments of the present invention include at least the following:

[0047] 1. This invention designs a passive method for achieving oscillation confinement function. Without introducing external force fields such as electricity, magnetism, and sound waves, it can accurately and controllably achieve droplet oscillation confinement solely based on the inherent instability characteristics of viscoelastic fluid and the unique microfluidic channel design, thus enabling microfluidic chips with oscillation confinement function to have a wider range of applications.

[0048] 2. This invention establishes the parameters for viscoelastic fluid configuration and the geometric design criteria for microfluidic channels to achieve oscillation confinement function. It clarifies the viscoelastic fluid solution configuration and the geometry and size of the microfluidic channels required to achieve specific oscillation confinement functions, providing detailed and in-depth technical guidance for the application of oscillation confinement microfluidic chips. Attached Figure Description

[0049] To more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0050] Figure 1 This is a flowchart of the microfluidic chip design method provided in the embodiments of the present invention;

[0051] Figure 2 This is a schematic diagram of a microfluidic channel design based on viscoelastic fluid to achieve oscillation confinement function, provided in an embodiment of the present invention.

[0052] Figure 3 This is a schematic diagram of the forces acting on a droplet during oscillation confinement based on viscoelastic fluid microfluidics, provided in an embodiment of the present invention.

[0053] Figure 4 This is a schematic diagram of the binding characteristics when oscillation is bound based on viscoelastic fluid microfluidics, provided in an embodiment of the present invention.

[0054] Figure 5This is a schematic diagram of the experimental results provided in the embodiments of the present invention;

[0055] Figure 6 This is a schematic diagram of the microfluidic chip design device provided in an embodiment of the present invention.

[0056] As shown in the figure, specific structures and devices are marked in the figure to clearly illustrate the structure of the embodiments of the present invention. However, this is only for illustrative purposes and is not intended to limit the present invention to the specific structure, device and environment. According to specific needs, those skilled in the art can adjust or modify these devices and environments, and such adjustments or modifications are still included in the protection scope of the present invention. Detailed Implementation

[0057] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0058] Embodiments of the present invention provide a microfluidic chip design method based on the viscoelastic fluid binding effect, such as... Figure 1 As shown, the method includes the following steps:

[0059] S1. Select a microfluidic channel that effectively utilizes the instability of viscoelastic fluids to bind droplets.

[0060] In this embodiment of the invention, the selected microfluidic channel capable of achieving the confinement function is a confluence channel. This invention innovatively proposes a confluence channel that effectively utilizes the confinement effect that can slow down or even stop the flow of droplets, bubbles, particles, etc., when viscoelastic fluid displaces or carries droplets, bubbles, particles, etc., forming a two-phase flow, and when passing through confluence channel structures such as gradual or sudden contractions.

[0061] S2. Design the dimensions of the selected microfluidic channel.

[0062] A confluence channel is a channel whose equivalent diameter decreases along the fluid flow direction, thus creating a flow effect on the fluid in the opposite direction. Here, the channel dimensions are designed based on the confluence channel model, such as... Figure 2 As shown, the confluence channel includes a pore-throat structure. Figure 2 (a) is a top view, and (b) is a side view. This pore-throat structure consists of pore 1 and throat 2. The equivalent diameter D of pore 1... p The equivalent diameter D of the larynx 2 is greater than t ;

[0063] Among them, the equivalent diameter D of pore 1 p From the pore width p w and pore depth p d express:

[0064]

[0065] Equivalent diameter D of throat 2 t The width of the larynx t w and laryngeal depth t d express:

[0066]

[0067] S3. Configure the displacement fluid according to the known dimensions of the microfluidic channel.

[0068] In this step, nine different displacing fluids are prepared, including three Newtonian fluids, two shear-thinning fluids, and four viscoelastic fluids.

[0069] This invention innovatively uses Newtonian fluids and shear-thinning fluids as control examples to determine that the factor causing droplet oscillation constraint is the instability of viscoelastic fluids. By configuring various viscoelastic fluids, the accuracy of the linear relationship between droplet oscillation and the deborah number is further demonstrated.

[0070] S4. Construct a viscoelastic fluid dynamics model based on the known microfluidic channels.

[0071] Taking droplet oscillation confinement in a pore-throat microchannel as an example, Figure 3 and Figure 4 These are schematic diagrams of the droplet's force and confinement characteristics when oscillation confinement is achieved based on viscoelastic fluid microfluidics, as provided in this embodiment of the invention. Due to the instability of the viscoelastic fluid, the viscoelastic fluid 3 can achieve an oscillation confinement effect on the droplet 4 along the flow direction.

[0072] During the process of viscoelastic fluid displacing droplets, the droplets are subjected to viscous force F. v Capillary force F c and elastic force F e The combined effect of these factors, through the adjustment of viscous force F v Capillary force F c and elastic force F e The size relationship between them can be used to achieve droplet oscillation confinement; the viscoelastic fluid dynamics model is as follows:

[0073]

[0074] F e =χDeF v (3)

[0075]

[0076] In the formula, L is the length of the droplet in meters; D is the equivalent diameter of the droplet in meters; η is the viscosity of the viscoelastic fluid in Pascal-second; U is the flow velocity of the viscoelastic fluid in meters per second; τ is the relaxation time of the viscoelastic fluid in seconds; and γ is the interfacial tension coefficient between the viscoelastic fluid and the droplet in Newtons per meter. ψ and χ are the microfluidic channel shape coefficients, dimensionless, with values ​​between 0 and 1; Ca is the capillary number, dimensionless; De is the Deborah number of the viscoelastic fluid, dimensionless; Ec is the number of elastic capillaries, dimensionless.

[0077] Among them, the Deborah number (De) represents the ratio of elastic force to viscous force; the capillary number (Ca) represents the ratio of viscous force to capillary force on the displaced droplet; and the elastic capillary number (Ec) represents the ratio of the Deborah number to the capillary number.

[0078] S5. Determine the critical conditions for droplet oscillation confinement based on the viscoelastic fluid dynamics model and experimental results.

[0079] In this step, the critical condition for achieving droplet oscillation confinement is:

[0080] F v =F c +F e (7)

[0081] Combining equations (1) and (7), the dimensionless expression of the critical condition for achieving droplet oscillation confinement is obtained as follows:

[0082]

[0083] Based on the experimental results, such as Figure 5 The figure shows the distribution of viscoelastic fluids with Ec = 1475, Ec = 604, Ec = 115, and Ec = 102, respectively. The dashed lines in the figure represent the linear fit of all data, and the following relationships exist:

[0084] A = m(De - De) crit (9)

[0085]

[0086] In the formula, the subscript crit indicates the critical state; A is the dimensionless oscillation amplitude of the droplet; De crit The critical Deborah number is represented as 1 in this case; m is the microfluidic channel shape coefficient, dimensionless, and takes a value between 0 and 1; that is, the critical condition for achieving droplet oscillation is that the Deborah number of the viscoelastic fluid is equal to the critical Deborah number De. crit ;

[0087] Here, the dimensionless oscillation amplitude A is the ratio of the droplet oscillation amplitude to the equivalent diameter of the pore portion of the microfluidic channel.

[0088] The critical condition for achieving droplet oscillation confinement is to achieve droplet oscillation simultaneously, that is, to satisfy both equations (8) and (10):

[0089]

[0090] S6. Establish microfluidic design criteria for confining droplets based on the critical conditions for droplet oscillation confinement.

[0091] Based on the critical conditions for droplet oscillation confinement determined by the viscoelastic fluid dynamics model in the previous step, the viscoelastic fluid is configured by adjusting parameters such as relaxation time, viscosity, flow rate, and interfacial tension coefficient. Microfluidic design is then carried out by adjusting the size of the microfluidic channel.

[0092] This invention presents a novel passive method for confining droplet oscillations. This method does not require the introduction of external force fields such as electricity, magnetism, or sound waves. It relies solely on the inherent instability characteristics of viscoelastic fluids and a unique microfluidic channel design to precisely and controllably achieve droplet oscillation confinement, thus enabling microfluidics with oscillation confinement capabilities to have a wider range of applications.

[0093] This invention establishes a viscoelastic fluid parameter configuration and microfluidic channel geometry design guideline for achieving oscillation confinement function. It clarifies the viscoelastic fluid solution configuration and microfluidic channel geometry and size required to achieve specific oscillation confinement functions, providing detailed and in-depth technical guidance for the application of oscillation confinement microfluidic chips.

[0094] Accordingly, embodiments of the present invention also provide a microfluidic chip design device based on the viscoelastic fluid binding effect, such as... Figure 6 As shown, the device includes:

[0095] The channel selection module is used to select microfluidic channels that effectively utilize the instability of viscoelastic fluids to bind droplets;

[0096] The size design module is used to design the dimensions of the selected microfluidic channel;

[0097] Displacement fluid configuration module, used to configure displacement fluid according to the known dimensions of microfluidic channels;

[0098] The model building module is used to construct viscoelastic fluid dynamics models based on known microfluidic channels;

[0099] The critical condition determination module is used to determine the critical conditions for droplet oscillation confinement based on the viscoelastic fluid dynamics model and experimental results.

[0100] The design criteria building module is used to establish microfluidic design criteria for confining droplets based on the critical conditions of droplet oscillation confinement.

[0101] The apparatus of this embodiment can be used to perform Figure 1 The technical solutions of the method embodiments shown are similar in principle and in effect, and will not be described again here.

[0102] Embodiments of the present invention also provide an electronic device, which may vary considerably due to different configurations or performance. It may include one or more processors (central processing units, CPUs) and one or more memories, wherein the memory stores at least one instruction, which is loaded and executed by the processor to implement the steps of the microfluidic chip design method described above.

[0103] In an exemplary embodiment, a computer-readable storage medium is also provided, such as a memory including instructions that can be executed by a processor in a terminal to complete the microfluidic chip design method described above. For example, the computer-readable storage medium may be a ROM, random access memory (RAM), CD-ROM, magnetic tape, floppy disk, or optical data storage device, etc.

[0104] It should be noted that, in this document, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or terminal device that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or terminal device. Unless otherwise specified, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or terminal device that includes said element.

[0105] The use of terms such as "an embodiment," "an embodiment," "an exemplary embodiment," and "some embodiments" in the specification indicates that the described embodiment may include a specific feature, structure, or characteristic, but not every embodiment necessarily includes that specific feature, structure, or characteristic. Furthermore, when a specific feature, structure, or characteristic is described in connection with an embodiment, implementing such a feature, structure, or characteristic in conjunction with other embodiments (whether explicitly described or not) should be within the knowledge of those skilled in the art.

[0106] Generally, terms can be understood at least partly from their use in context. For example, depending at least partly on the context, the term "one or more" as used herein can be used to describe any feature, structure, or characteristic in a singular sense, or a combination of features, structures, or characteristics in a plural sense. Additionally, the term "based on" can be understood not necessarily to convey an exclusive set of factors, but rather, alternatively, depending at least partly on the context, to allow for the presence of other factors that are not necessarily explicitly described.

[0107] This invention encompasses any substitutions, modifications, equivalent methods, and solutions made within the spirit and scope of this invention. To provide the public with a thorough understanding of this invention, specific details are described in detail in the following preferred embodiments; however, those skilled in the art will fully understand the invention even without these details. Furthermore, to avoid unnecessary misunderstanding of the essence of this invention, well-known methods, processes, procedures, components, and circuits are not described in detail.

[0108] Those skilled in the art will understand that all or part of the steps in the methods of the above embodiments can be implemented by a program instructing related hardware. The program can be stored in a computer-readable storage medium, such as ROM / RAM, magnetic disk, optical disk, etc.

[0109] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A method for designing a microfluidic chip based on the viscoelastic fluid binding effect, characterized in that, The method comprises the following steps: S1, selecting a microfluidic channel capable of effectively utilizing viscoelastic fluid instability to bind droplets; S2, designing the size of the selected microfluidic channel; S3, configuring a displacement fluid according to the size of the known microfluidic channel; S4, constructing a viscoelastic fluid dynamics model according to the known microfluidic channel; In the process of viscoelastic fluid displacing droplet, the droplet is affected by the combined action of viscous force F v , capillary force F c and elastic force F e , and the oscillation constraint of the droplet can be realized by adjusting the size relationship among the viscous force F v , the capillary force F c and the elastic force F e . The viscoelastic fluid dynamics model is as follows: F e = χDEF v (3) In the formula, L is the length of the droplet, unit: meter; D is the equivalent diameter of the droplet, unit: meter; η is the viscosity of the viscoelastic fluid, unit: Pa·s; U is the flow rate of the viscoelastic fluid, unit: m / s; τ is the relaxation time of the viscoelastic fluid, unit: s; γ is the interfacial tension coefficient between the viscoelastic fluid and the droplet, unit: N / m; Ψ, χ are the microfluidic channel shape coefficients, dimensionless, taking values between 0 and 1; Ca is the capillary number, dimensionless; De is the Deborah number of the viscoelastic fluid, dimensionless; Ec is the elastic capillary number, dimensionless; S5, determining the critical condition of droplet oscillation binding based on the viscoelastic fluid dynamics model and experimental results; S6, establishing a microfluidic design criterion based on viscoelastic fluid instability to bind droplets according to the critical condition of droplet oscillation binding.

2. The microfluidic chip design method of claim 1, wherein, In the step S1, the microfluidic channel capable of achieving the binding function belongs to a confluence type channel.

3. The microfluidic chip design method of claim 2, wherein, In the step S2, the channel size is designed according to the converging channel model, the converging channel includes pore-throat structure, the equivalent diameter D p of the pore is greater than the equivalent diameter D t of the throat wherein the equivalent diameter D of the pores is p represented by the pore width p w and the pore depth p d is represented by: The equivalent diameter D of the throat t is expressed by the throat width t w and the throat depth t d is expressed by:

4. The microfluidic chip design method of claim 1, wherein, In the step S3, nine different displacement fluids, namely displacement liquids, are configured, including three Newtonian fluids, two shear thinning fluids and four viscoelastic fluids.

5. The microfluidic chip design method of claim 1, wherein, In the step S5, the critical condition for realizing droplet oscillation binding is: F v = F c + F e (7) By simultaneously solving formula (1)-(7), the dimensionless expression of the critical condition for realizing droplet oscillation binding is: According to the experimental results, the data is linearly fitted, and the following relationship exists: A = m(De - De crit ) (9) where the subscript crit denotes the critical state; A is the dimensionless oscillation amplitude of the droplet; De crit represents the critical Deborah number, which is 1 in this case; m is the microfluidic channel shape factor, dimensionless, and takes values between 0 and 1; i.e. the critical condition for the onset of oscillation confinement of the droplet is that the De number of the viscoelastic fluid equals the critical Deborah number De crit ; The critical condition for realizing droplet oscillation binding is to realize droplet binding and droplet oscillation at the same time, that is, to simultaneously satisfy formula (8) and (10):

6. The microfluidic chip design method of claim 1, wherein, In the step S6, the critical condition of droplet oscillation binding determined based on the viscoelastic fluid dynamics model is used to configure the viscoelastic fluid by adjusting the relaxation time, viscosity, flow rate and interfacial tension coefficient, and to perform microfluidic design by adjusting the size of the microfluidic channel.

7. A microfluidic chip design device based on the viscoelastic fluid binding effect, for implementing the method according to any one of claims 1 to 6, characterized in that, It comprises: A channel selection module for selecting a microfluidic channel capable of effectively utilizing viscoelastic fluid instability to bind droplets; A size design module for designing the size of the selected microfluidic channel; A displacement liquid configuration module for configuring a displacement fluid according to the size of the known microfluidic channel; A model construction module for constructing a viscoelastic fluid dynamics model according to the known microfluidic channel; A critical condition determination module for determining the critical condition of droplet oscillation binding based on the viscoelastic fluid dynamics model and experimental results; A design criterion construction module for establishing a microfluidic design criterion based on viscoelastic fluid instability to bind droplets according to the critical condition of droplet oscillation binding.

8. An electronic device, comprising: The electronic device comprises a processor and a memory, and the memory stores at least one instruction, which is loaded and executed by the processor to implement the microfluidic chip design method of any one of claims 1-6.

9. A computer readable storage medium, the storage medium storing at least one instruction, the at least one instruction being loaded and executed by a processor to implement the microfluidic chip design method of any one of claims 1-6.

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