Microneedle chip capable of controlling liquid collection and delivery

Abstract

The embodiment of the utility model discloses a microneedle chip capable of controlling liquid collection and delivery, which comprises a microneedle array and a fluidic chip, the fluidic chip is provided with a compressible air bag, the air bag is connected with a microfluidic channel, one end of the microfluidic channel is communicated with a microcolumn array chamber, and the other end of the microfluidic channel is communicated with a liquid outlet. A groove with the same area as the bottom of the microneedle array is formed in the tail end of the microfluidic channel, the microneedle array is arranged above the groove, the air bag is in airtight communication with the microneedle array through the microfluidic channel, and then collection and delivery of liquid in the microneedle array are controlled by pressing or releasing the air bag. The device has the advantage of high integration, is convenient for operators to use, and is simple and clear in manufacturing process, low in cost and easy to popularize.

Description

Technical Field

[0001] The utility model relates to the field of medical equipment, and in particular to a microneedle chip capable of controlling liquid collection and delivery. Background Art

[0002] As an emerging microtechnology, microneedles have been widely used in drug delivery and sample collection. Existing microneedles usually exist independently, so they need to be assisted by other instruments to control the collection and delivery of liquids, which requires technicians to perform more cumbersome operations, reducing overall work efficiency and making it easier to cause operational errors in experiments or tasks.

[0003] To this end, various methods have been adopted in the market to solve the problem of driving force of microneedle chips in the collection and delivery links. For example, the existing patent: A portable microneedle array patch CN108653907A, proposes a solution that uses electrode sheets to form an electric field to provide driving force for the microneedle chip. However, the above solution is too expensive and the production process is relatively cumbersome, which is not conducive to practical application and popularization.

[0004] To solve this problem, this paper designs a microneedle chip that can control liquid collection and delivery. Utility Model Content

[0005] The technical problem to be solved by the embodiments of the utility model is to provide a microneedle chip capable of controlling liquid collection and delivery, comprising: a microneedle array and a fluidic chip.

[0006] The fluidic chip has a pressable airbag, which is connected to the microfluidic channel. One end of the microfluidic channel is connected to a microcolumn array chamber. The end of the microfluidic channel is provided with a groove with the same area as the bottom of the microneedle array. The microneedle array is arranged above the groove. The airbag is airtightly connected to the microneedle array through the microfluidic channel, and the collection and delivery of liquid in the microneedle array are controlled by pressing or releasing the airbag.

[0007] The bottom of the groove of the microfluidic channel has a through hole, and the groove is connected with the microfluidic channel through the through hole.

[0008] Wherein, the micro-column array chamber has a plurality of elliptical columns for supporting the microfluidic channels.

[0009] Wherein, a substrate is provided at the bottom of the fluidic chip, and the substrate adheres to and seals the microfluidic channel and the microcolumn array chamber.

[0010] The microneedle array has at least one needle body, and the interior of the needle body has a through needle channel.

[0011] Wherein, the airbag is a finger pressure type airbag.

[0012] The implementation of the utility model has the following beneficial effects: ① The integrated design of the microneedle array and the fluidic chip enables the user to control the collection and delivery of the liquid in the microneedle chip by pressing the airbag, without the need for additional instruments, and the operation is simple and convenient. ② By pressing and releasing the airbag and cooperating with the microfluidic channel and the microcolumn array chamber to form positive and negative pressure to provide driving force, the cost is lower than that of electric field drive or other electrical component drive, and it is more suitable for large-scale promotion and popularization. BRIEF DESCRIPTION OF THE DRAWINGS

[0013] Figure 1 Schematic diagram of Example 1 of the utility model, wherein A is a top view and B is a cross-sectional view;

[0014] Figure 2 It is a bar chart of the experimental effect of Example 1 of the utility model in the collection experiment of the performance experiment;

[0015] Figure 3 It is a flowchart of Embodiment 2 of the present utility model;

[0016] Figure 4 It is a schematic diagram of the microneedle array of Example 2 of the present utility model. DETAILED DESCRIPTION

[0017] In order to make the purpose, technical solutions and advantages of the utility model clearer, the utility model will be further described in detail below with reference to the accompanying drawings.

[0018] Example 1

[0019] like Figure 1 As shown, a microneedle chip capable of controlling liquid collection and delivery comprises: a microneedle array 1 and a fluidic chip 2;

[0020] The fluidic chip 2 is provided with a microfluidic channel 22, the head end of the microfluidic channel 22 is connected to a microcolumn array chamber 23, the middle of the microcolumn array chamber is provided with an airbag 21, the end of the microfluidic channel 22 is provided with a groove 221 with the same area as the bottom of the microneedle array 1, the microneedle array 1 is arranged above the groove 221 and is airtightly connected to the airbag 21 through the microfluidic channel 22, and the collection and delivery of the liquid in the microneedle array 1 is controlled by pressing or releasing the airbag 21.

[0021] The bottom of the groove 221 of the microfluidic channel 22 has a through hole 222, and the groove 221 is connected to the microfluidic channel 22 through the through hole 222, so that the microneedle array 1 set on the groove 221 forms an airtight connection relationship through the through hole 222, the microfluidic channel 22, and the microcolumn array chamber 23, and positive and negative air pressures are formed by pressing and releasing the airbag 21, thereby driving the collection and delivery of the liquid in the microneedle array 1.

[0022] More preferably, the micro-column array chamber 23 has a plurality of elliptical columns 231 . The function of the micro-column array chamber 23 is to accommodate the collected liquid. Meanwhile, the function of the columns is to prevent two pieces of PDMS from sticking together, so as to support the microfluidic channel 22 .

[0023] More preferably, a substrate 24 is provided at the bottom of the fluidic chip 2 , and the substrate 24 adheres to and seals the microfluidic channel 22 and the microcolumn array chamber 23 .

[0024] More preferably, the microneedle array 1 has at least one needle body, and the interior of the needle body has a through needle channel.

[0025] Performance experiment:

[0026] The operator first presses the air bag on the chip with his finger, then puts the OSTE hollow microneedle chip into the liquid sample (blood sample or water containing blue dye) and releases his finger. At this time, the air bag begins to recover, creating negative pressure in the microfluidic channel, causing the liquid sample to be sucked into the microfluidic channel.

[0027] For liquid delivery experiments, operators inserted blue-dyed water into the agarose gel through the OSTE hollow microneedle chip and pressed the air pockets with their fingers. Each experiment was repeated multiple times.

[0028] The weight of the liquid sample collected by the prepared OSTE hollow microneedle chip was measured, and the results are as follows Figure 2 As shown, in the collection experiment, the scheme implemented in this embodiment can collect 57.5±11.8 mg of water and 31.8±4.2 mg of blood samples; in the delivery experiment, it can be observed with the naked eye that the water containing the blue dye is uniformly transported to the agarose gel and diffused into the agarose gel, proving that it has excellent liquid collection and delivery performance.

[0029] Example 2

[0030] This embodiment mainly discloses a method for making a microneedle chip capable of controlling liquid collection and delivery. Figure 3 As shown, the specific steps include:

[0031] ① Production of microneedle array: First, design the first film mask pattern and hollow microneedle array through software, and set the microneedle diameter. The conventional microneedle diameter is 200~800 microns.

[0032] After dropping the OSTE polymer material, the first film mask is covered, and a photolithography machine is used to perform photocuring on the film mask to form an OSTE hollow microneedle array. After development, cleaning and drying, ultraviolet light post-curing treatment is performed, and then the obtained microneedle array 1 is further subjected to plasma hydrophilic treatment, and a thin layer of OSTE is dropped at the bottom, and ultraviolet light post-curing and plasma hydrophilic treatment are continued to be performed to obtain the following Figure 4 Shown is an OSTE hollow microneedle array with a base plate.

[0033] It should be noted that the OSTE in the present production method includes: pentaerythritol tetrathioglycolate, triallyl isocyanurate and a photoinitiator, which are mixed in a mass ratio of 13:17:2 respectively. The photoinitiator is photoinitiator Igr819. The preparation of the photoinitiator Igr819 includes the following steps: mixing triallyl isocyanurate and Igr819 powder reagent in a mass ratio of 99:1, and heating them in a drying oven at 55°C for 30 minutes.

[0034] ② Fabrication of fluidic chip: Apply photoresist on silicon wafer, bake the wafer at high temperature, cover with film mask, and use photolithography machine to photocuring to make micro-pillar array. Bake the wafer at high temperature again, develop, clean and dry, and then perform silanization treatment. Then paste a medical finger pressure airbag 21 on the wafer, put the wafer into an acrylic mold, pour PDMS into the mold, and set a groove 221 on the PDMS surface that is the same size as the bottom of the micro-needle array. Then bake at high temperature, punch a through hole 222 in the middle of the groove 221, and then perform plasma hydrophilic treatment on it and the substrate 24, and then bond the two together to obtain the fluidic chip 2.

[0035] It should be noted that the acrylic mold in this solution is a concave container formed by 3D printing, and the mold is formed by using a culture dish as a substrate and a square acrylic plate as a mold side wall. In addition, the above-mentioned PDMS material includes: polydimethylsiloxane and a curing agent, which are mixed at a mass ratio of 10:1.

[0036] ③ Combine the fluidic chip 2 and the microneedle array 1: bond the microneedle array 1 and the fluidic chip 2 together with an adhesive and then bake them at a high temperature to obtain a microneedle chip capable of controlling liquid collection and delivery as disclosed in Example 1.

[0037] Of course, the above embodiments are only for illustrating the technical concept and features of the utility model, and their purpose is to enable people familiar with the technology to understand the content of the utility model and implement it accordingly, and they cannot be used to limit the protection scope of the utility model. Any modifications made according to the spirit of the main technical solution of the utility model should be included in the protection scope of the utility model.

Claims

1. A microneedle chip capable of controlling liquid collection and delivery, characterized in that: include: Microneedle array (1) and fluidic chip (2); The fluidic chip (2) is provided with a microfluidic channel (22), the head end of the microfluidic channel (22) is connected to a microcolumn array chamber (23), the middle part of the microcolumn array chamber is provided with an air bag (21), the end of the microfluidic channel (22) is provided with a groove (221) of the same area as the bottom of the microneedle array (1), the microneedle array (1) is arranged above the groove (221) and is airtightly connected to the air bag (21) through the microfluidic channel (22), and the collection and delivery of liquid in the microneedle array (1) is controlled by pressing or releasing the air bag (21).

2. A microneedle chip capable of controlling liquid collection and delivery according to claim 1, characterized in that: The bottom of the groove (221) of the microfluidic channel has a through hole (222), and the groove is connected to the microfluidic channel (22) through the through hole (222).

3. A microneedle chip capable of controlling liquid collection and delivery according to claim 1, characterized in that: The micro-column array chamber has a plurality of elliptical columns (231) for supporting the microfluidic channel (22).

4. A microneedle chip capable of controlling liquid collection and delivery according to claim 1, characterized in that: A substrate (24) is provided at the bottom of the fluidic chip (2), and the substrate (24) is bonded to and seals the microfluidic channel (22) and the microcolumn array chamber (23).

5. A microneedle chip capable of controlling liquid collection and delivery according to claim 1, characterized in that: The microneedle array (1) comprises at least one needle body, and the interior of the needle body comprises a through needle channel.

6. A microneedle chip capable of controlling liquid collection and delivery according to claim 1, characterized in that: The airbag (21) is a finger-pressure type airbag.

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