CN109718420B - Wearable human insulin injection liquid supply device - Google Patents

Abstract

A wearable human body insulin injection and supply device is tied and fixed through an annular belt structure and is provided with a carrier, a liquid storage chamber and a flow guide actuating unit are arranged on the carrier, and a sensor and a driving chip are arranged on the carrier. The flow guide actuating unit is provided with a liquid guide channel which is communicated with a liquid storage outlet and a liquid guide outlet of the liquid storage cavity. The sensor is pressed against human skin to monitor the monitoring value of blood glucose content in sweat. The driving chip receives the monitoring value interpretation from the sensor, controls the actuation of the diversion actuation unit according to the monitoring value interpretation, and controls the opening and closing states of the valve switches of the liquid storage outlet and the liquid guide outlet. The flow guide actuating unit is driven to generate pressure gradient, so that insulin liquid in the liquid storage cavity is output to the liquid guide outlet through the liquid guide channel, flows into the microneedle patch attached below the flow guide actuating unit, and is injected into subcutaneous tissues through the plurality of branch hollow microneedles.

Description

Wearable human insulin injection liquid supply device

【Technical field】

This case is about a liquid supply device, especially a wearable human insulin injection liquid supply device used for human insulin injection.

【Background technique】

At present, the treatment methods for type 1 diabetes and type 2 diabetes are mainly supplementary hypoglycemic drugs, and the administration methods include oral administration, syringe injection and insulin pump injection. Among them, oral and syringe injection methods, patients need to use a blood glucose meter to test their own blood sugar level every day, and then take medicine according to the blood sugar level. The insulin pump system consists of an indwelling needle and an insulin pump. The indwelling needle is placed in the body and fixed on the body surface for blood collection and drug injection; the insulin pump connected to the indwelling needle controls the release of hypoglycemic drugs according to the blood sugar level.

Since insulin cannot be taken orally, it can only be injected. Syringe injections and indwelling needles of insulin pumps not only cause pain to the patient during injection, but also leave needle holes on the body surface. In particular, syringe injections often require multiple times a day, which will cause hard lumps in the subcutaneous tissue due to frequent injections. The use of the indwelling needle in the insulin pump reduces the number of injections, but the overall package has a certain volume and weight, which is inconvenient to carry around. Setting it on the body will affect the daily life and exercise of the patient.

In view of the above deficiencies, this case develops a safe, portable and painless intelligent wearable human insulin injection liquid supply device, which provides patients with injecting human insulin in their daily life to control blood sugar levels at any time, and solves the above problems of traditional injection methods. .

[Content of the invention]

In order to solve the problem that the traditional insulin injection method will cause pain and inconvenience for patients to carry around, the present case provides a wearable human insulin injection liquid supply device, which includes: a body with an accommodating space; a ring belt structure, the two ends of which are connected Two sides of the main body; a carrier, disposed in the accommodating space of the main body; a liquid storage chamber, constructed on the carrier to store insulin liquid, and has a liquid storage outlet; a flow-guiding actuating unit, It is constructed on the carrier and has a liquid guiding channel, which is communicated with the liquid storage outlet of the liquid storage chamber, and is connected with a liquid guiding outlet, so that the guiding actuation unit is driven to transmit the insulin liquid and output from the liquid guiding outlet ; A plurality of valve switches, the liquid storage outlet and the liquid guiding outlet are respectively provided with a valve switch; a micro-needle patch is attached to the bottom of the guiding actuating unit to close the liquid guiding outlet, and has a plurality of branches A hollow microneedle for minimally invasive insertion into the human skin to derive the insulin liquid and inject it into the subcutaneous tissue; a sensor, whose structure is arranged on the carrier, to resist the monitoring value of the human skin for monitoring the blood sugar content in sweat; an airbag, arranged on the ring belt structure; a micro gas pump communicated with the air bag; and a driving chip, the structure is arranged on the carrier, to control the actuation of the flow guiding actuating unit, control the switch state of the plurality of valve switches and receive the sensor Interpretation of the monitoring value; thereby, the belt structure is worn on the human skin, the driving chip is used to control the actuation of the micro gas pump to inflate the airbag, and the belt structure is closely attached to the human skin, so that the The microneedle patch can be minimally invasively inserted into the human skin with the plurality of hollow microneedles, and when the sensor detects a specific monitoring value of the blood sugar content in the sweat flowing out of the human skin, the driving chip controls the actuation of the flow guiding unit to actuate At the same time, the valve switch of the liquid storage outlet is controlled to be turned on, and the valve switch of the liquid guide outlet is turned on, and the insulin liquid stored in the liquid storage chamber is output from the liquid guide outlet, introduced into the microneedle patch, and The insulin liquid is derived from the plurality of hollow microneedles and injected into the subcutaneous tissue.

【Description of drawings】

FIG. 1 is a schematic structural diagram of the wearable human insulin injection liquid supply device of the present invention.

FIG. 2 is a schematic cross-sectional view of the wearable human insulin injection liquid supply device shown in FIG. 1 .

FIG. 3 is a schematic cross-sectional view of the relevant structure of the wearable human insulin injection liquid supply device shown in FIG. 2 .

FIG. 4A and FIG. 4B are schematic diagrams of the action flow of the wearable human insulin injection liquid supply device shown in FIG. 3 .

FIG. 5 is a schematic diagram of the valve plate of the wearable human insulin injection liquid supply device of the present invention.

FIG. 6A is a schematic diagram of the valve switch structure of the wearable human insulin injection liquid supply device in the present case.

FIG. 6B is a schematic view of the valve switch shown in FIG. 6A .

FIG. 7 is a schematic diagram of the electrical connection relationship of the relevant components of the wearable human insulin injection liquid supply device of the present invention.

FIG. 8 is a schematic diagram of the wearable human insulin injection liquid supply device of the present application being worn on the user.

9A and 9B are schematic structural diagrams of the micro gas pump of the wearable human insulin injection liquid supply device of the present invention.

[implementation]

Some typical embodiments embodying the features and advantages of the present case will be described in detail in the description of the latter paragraph. It should be understood that this case can have various changes in different aspects, all of which do not depart from the scope of this case, and the descriptions and diagrams therein are essentially for illustrative purposes rather than limiting the present case.

This case is a wearable human insulin injection liquid supply device, please refer to Figure 1, Figure 2 and Figure 3,

The wearable human insulin injection liquid supply device 100 includes a main body 1 , an annular belt structure 2 , a carrier 3 , a liquid storage chamber 4 , a flow guiding actuating unit 5 , a plurality of valve switches 6 , and a microneedle patch 7 . , a sensor 8 , and a driver chip 9 . Wherein, the main body 1 has an accommodating space 11, and the two ends of the annular belt structure 2 are connected to both sides of the main body 1, so that the main body 1 is fixed on the user's body through the annular belt structure 2 (as shown in FIG. 8 ). For example, the wrist, ankle, neck and other parts are used to achieve the purpose of wearing and improve the convenience of carrying; the carrier 3 is accommodated in the accommodating space 11 of the main body 1, and a liquid storage chamber 4 is recessed in the carrier. It is used to store the liquid of human insulin, and has a liquid storage outlet 41 for exporting the insulin liquid in the liquid storage chamber 4, and the liquid storage chamber 4 is recessed on the carrier 3 and sealed with a cover plate 31; The flow guiding actuating unit 5 is constructed on the carrier 30 and has a liquid guiding channel 51 and a liquid guiding outlet 52. The liquid guiding channel 51 is communicated with the liquid storage outlet 41 of the liquid storage chamber 4, and the flow guiding actuating unit 5 operates. After the movement, a suction force is generated, and the insulin liquid inside the liquid storage chamber 4 is drawn through the liquid storage outlet 41 communicated with the liquid guiding channel 51, enters the flow guiding actuating unit 5, and is then discharged from the liquid guiding outlet 52; In this embodiment, the number of valve switches 6 is two, but it is not limited to this. The valve switches 6 are respectively disposed at the liquid storage outlet 41 and the liquid guiding outlet 52 and close them. Through the switch state of the valve switch 6 ( open/close), further control the flow of insulin liquid passing through the liquid storage outlet 41 and the liquid guiding outlet 52 to avoid the occurrence of excessive or insufficient insulin;

The microneedle patch 7 is attached to the bottom of the guide actuating unit 5 and closes the liquid guide outlet 52. The microneedle patch 7 has a plurality of hollow microneedles 71. When the liquid guide outlet 52 discharges the insulin liquid, the plurality of hollow microneedles 71 are formed. The needle 71 is non-invasively or minimally invasively inserted into the human skin, and the insulin liquid is injected into the subcutaneous tissue; the sensor 8 and the driver chip 9 are integrated on the carrier 1 by a micro-electromechanical process (MEMS), and the sensor 8 is structured on the carrier 3. Human skin is used to monitor sweat to obtain the monitoring value of blood sugar content; in addition, the body 1 has a through hole (not shown) on the surface adjacent to the user's skin, the through hole communicates with the accommodating space 11, and the through hole is used for the microneedle patch 7 Wear it and make contact with the user's skin.

The multiple hollow microneedles 71 of the above-mentioned microneedle patch 7 are micron-sized pinholes capable of piercing the skin,

The material can be high molecular polymer, metal or silicon, preferably silicon dioxide with high biocompatibility, the pore size of the hollow microneedle 71 is enough for insulin molecules to pass through, preferably, the hollow microneedle 71 The inner diameter is between 10 micrometers (μm) and 550 micrometers (μm), and the length of the hollow microneedles 71 is between 400 micrometers (μm) and 900 micrometers (μm), which can be inserted into the subcutaneous tissue of the human body without touching the human body. Nerves, so there is no pain at all. A plurality of hollow microneedles 71 are arranged on the microneedle patch 7 and are arranged in an array. The distance between each hollow microneedle 71 needs to be greater than 200 microns, so as not to interfere with each other, and the array is arranged in this way. A plurality of hollow microneedles 71 are used, so that one of the hollow microneedles 71 will not block and affect the function of injecting fluid, and other hollow microneedles 71 can continue to maintain the function of injecting fluid on time.

Please continue to refer to FIG. 3 , the liquid guiding channel 51 of the flow guiding actuating unit 5 includes a pressure chamber 511 , an inlet channel 512 and an outlet channel 513 , and the inlet channel 512 is used to communicate with the liquid storage outlet 41 of the liquid storage chamber 4 . , the outlet channel 513 is connected to the liquid-conducting outlet 52, the inlet channel 512 and an outlet channel 513 pass through the carrier 3 and are separated from each other, and a pressure chamber 511 is recessed on the carrier 3 to connect the inlet channel 512 and the outlet channel 513 respectively. One end of the pressure chamber 511 is sealed by the actuator 53, and the inlet channel 512 is arranged on the carrier 3 and the other end is covered with a cover member 32, so that the other end communicates with the liquid storage chamber 4 The liquid storage outlet 41 forms a sealed fluid channel, and the opening formed at the other end of the outlet channel 512 is the liquid guiding outlet 52 . In this way, the inlet channel 512 , the pressure chamber 511 , the outlet channel 513 , and the liquid guide outlet 52 are connected in series to form a fluid channel.

The above-mentioned flow-guiding actuating unit 5 further includes an actuator 53. The actuator 53 has a carrier 531 and an actuating element 532. The carrier 531 covers and seals the pressure chamber 511 and is attached to the surface of the actuator 531 for actuation. The element 532 is deformed by the actuating element 532 to drive the carrier 531 to vibrate up and down, change the volume of the pressure chamber 511, and change the pressure inside the pressure chamber 511 to generate a suction force to deliver the insulin liquid.

Please continue to refer to FIG. 3 and FIG. 5 , a valve plate 54 can be disposed in the inlet channel 512 and the outlet channel 513 of the flow guiding actuating unit 5 respectively, and the carrier 3 is located in a middle position of the inlet channel 512 and the outlet channel 513 respectively. A cavity 514 and a convex structure 515 are provided, wherein the convex structure 515 is disposed at the inlet channel 512 to be disposed at the bottom of the cavity 514, and the convex structure 515 is disposed at the outlet channel 512 to be disposed in the cavity 514 At the top of the valve plate 54, a plurality of through holes 541 are formed in the corresponding part of the chamber 514 to form a central part 542 connected to a plurality of connecting parts 543, so that the central part 542 can be elastically supported, so that the valve plates 54 are respectively covered At the chambers 514 of the inlet channel 512 and the outlet channel 513 , the central portion 542 is driven to abut against the protruding portion structure 515 to generate a pre-force.

Therefore, as shown in FIG. 4A , FIG. 4B and FIG. 5 , when the valve switch 6 of the liquid storage outlet 41 is turned on and the flow-directing actuating unit 5 starts to be activated, a pressure difference is generated in the flow-directing actuating unit 5 to drive the inlet channel. The central part 542 of the valve plate 54 on the 512 is upward away from the convex structure 515 at the inlet channel 512, so that the insulin liquid in the inlet channel 512 can enter the pressure chamber 511 through at least the through hole 541 of the valve plate 54, as shown in FIG. 4B. It is shown that after the insulin liquid enters the pressure chamber 511, the central portion 542 of the valve plate 54 of the outlet channel 513 is subjected to the pressure difference in the flow guiding actuating unit 5, so that the central portion 542 of the valve plate 54 on the outlet channel 513 is directed downward. Protrusions 515 away from the outlet channel 513 for insulin fluid to enter the catheter outlet 52 . With the above arrangement, when the actuator 53 is not actuated, the central portion 542 of the valve plate 54 on the inlet channel 512 and the outlet channel 513 can close and isolate the inlet channel 512 and the outlet channel 513, respectively. Insulin liquid flows countercurrently through the inlet channel 512 and the outlet channel 513 .

Please refer to FIG. 6A and FIG. 6B , the valve switch 6 includes a holding member 61 , a sealing member 62 and a displacement member 63 . The displacement member 63 is disposed between the holding member 61 and the sealing member 62 and is displaced between the two. The holding member 61 has at least two through holes 611 respectively, and the displacement member 63 is also provided with a through hole 611 corresponding to the position of the holding member 61 . The hole 631, the through hole 611 of the holding member 61 and the through hole 631 of the displacement member 63 are substantially aligned with each other, and the sealing member 62 is provided with at least one through hole 621, and the through hole 621 of the sealing member 62 and the holding member The position of the through hole 611 of the member 61 is misaligned and misaligned. The holding member 61 , the sealing member 62 and the displacement member 63 of the valve switch 6 can be made of graphene material to form a miniaturized valve member.

In the first embodiment of the valve closing 6 in this case, the displacement member 63 is a material with a charge, the holding member 61 is a bipolar conductive material, and the holding member 61 is electrically connected to a control circuit of the driving chip 9, which is used for to control the polarity (positive polarity or negative polarity) of the holder 61 . If the displacement member 63 is a material with a negative charge, when the valve switch 6 needs to be controlled to open, the driving chip 9 controls the holder 61 to form a positive electrode, and the displacement member 63 and the holder 61 maintain different polarities at this time, so that the The displacement member 63 approaches the holding member 61, which constitutes the opening of the valve switch 6 (as shown in FIG. 6B ). On the contrary, if the displacement member 63 is a material with negative charge, when the valve switch 6 must be controlled to be closed, the driving chip 9 controls the holder 61 to form a negative electrode. At this time, the displacement member 63 and the holder 61 maintain the same polarity, so that the The displacement member 63 approaches the sealing member 62, which constitutes the closing of the valve switch 6 (as shown in FIG. 6A).

In the second embodiment of the valve switch 6 of the present application, the displacement member 63 is a magnetic material, and the holding member 61 is a magnetic material whose polarity can be controlled. The holder 61 is electrically connected to the control circuit of the driving chip 9 for controlling the polarity (positive or negative) of the holder 61 . If the displacement member 63 is a magnetic material with a negative electrode, when the valve switch 6 is to be controlled to open, the holder 61 forms a positive magnetism. At this time, the driving chip 9 controls the displacement member 63 and the holder 61 to maintain different polarities, so that the displacement member 63 and the holder 61 maintain different polarities. The member 63 approaches the holding member 61, which constitutes the opening of the valve switch 6 (as shown in FIG. 6B). Conversely, if the displacement member 63 is a magnetic material with a negative electrode, when the valve switch 6 must be controlled to be closed, the driving chip 9 controls the holder 61 to form a negative magnetism, and at this time, the displacement member 63 and the holder 61 are controlled to maintain the same polarity. , so that the displacement member 63 is close to the sealing member 62, which constitutes the closing of the valve switch 6 (as shown in FIG. 6A ).

Please continue to refer to FIG. 1 and FIG. 2 , the wearable human insulin injection liquid supply device of the present application may further include an air bag 12 and a micro gas pump 13 . The air bag 12 is disposed on the inner surface of the ring structure 2 adjacent to the user. The gas pump 13 is disposed on the annular belt structure 2 in a way that communicates with the airbag 12 , and the micro gas pump 13 is electrically connected to the driving chip 9 . When the micro-gas pump 13 receives the inflation signal transmitted by the driver chip 9, it starts, and the air is sucked from the outside and transmitted to the air bag 12 for inflation, so that the hollow micro-needles 71 of the micro-needle patch 7 can be inserted into the human skin for insulin. Injection of liquid.

Please refer to FIG. 7 , which is a schematic diagram of the electrical connection relationship of the relevant components of the wearable human insulin injection liquid supply device in a preferred embodiment of the present application. The driving chip 9 is structured on the carrier 3 and is connected to the micro gas pump 13 , the diversion actuating unit 5, a plurality of valve switches 6 and the sensor 8 are electrically connected, and the sensor 8 is in contact with the human skin to monitor the blood sugar content in human sweat, and generate a corresponding monitoring value. After the driving chip 9 receives the monitoring value of the sensor 8 , and then decide whether to activate the flow guiding actuating unit 5 and the plurality of valve switches 6 to perform the injection of the insulin liquid. Wherein, the driving chip 9 may further include a graphene battery (not shown in the figure) to provide power.

Please refer to FIG. 8 , which is a schematic diagram of the wearable human insulin injection liquid supply device being worn on the user. When the micro gas pump 13 receives the inflation signal transmitted by the driver chip 9, it starts to start, and the air is sucked from the outside and transmitted. When the air bag 12 is inflated, the hollow microneedles 71 of the microneedle patch 7 can be inserted into the human skin for injection of insulin liquid.

Please refer to FIG. 9A and FIG. 9B , the above-mentioned micro gas pump 13 can be a piezoelectrically actuated micro pneumatic power device, and the micro pneumatic power device includes a micro gas transmission device 131 and a micro valve device 132 , When the gas is transmitted from the micro gas transmission device 131 to the micro valve device 132, the pressure collection or pressure relief operation is performed. The micro gas transmission device 131 includes an air intake plate 131a, a resonant plate 131b and a piezoelectric actuator 131c stacked in sequence. When the piezoelectric actuator 131c is driven, the gas flows from the air intake plate 131a. enter and transmit downward, so that the gas can flow in one direction in the micro-valve device 132, and the micro-valve device 132 includes a gas collecting plate 132a, a valve plate 132b and an outlet plate 132c stacked in sequence. An outlet end (not shown) of the outlet plate 132c is communicated with the air bag 12; when the gas is transmitted from the micro gas transmission device 131 to the micro valve device 132, it passes through the outlet end of the outlet plate 132c to It is transported to the airbag 12 for pressure collection operation, or through a pressure relief hole of the outlet plate 132c for pressure relief operation.

To sum up, the wearable human insulin injection liquid supply device provided in this case generates a pressure gradient through the actuation of the diversion actuating unit to transfer the insulin liquid in the liquid storage chamber, and finally uses the microneedle patch to inject the insulin into the liquid. The liquid is injected into the user's skin to provide the user's insulin, and the sensor is used to detect the user's blood sugar level, and the flow-directing actuation unit and the valve switch are controlled by the driver chip to adjust the flow rate and flow rate of the insulin liquid injected into the user. The airbag can reduce the distance between the user and the microneedle patch, and enable the microneedle patch to be inserted into the user's skin. The micro-air pump can also adjust the gas in the airbag to fine-tune the microneedle patch into the user's skin. depth. Therefore, the wearable human insulin injection liquid supply device of the present invention can provide the function of the pancreas as a substitute for the traditional artificial pancreas.

This case can be modified by Shi Jiangsi, a person who is familiar with this technology, but all of them do not deviate from the protection of the scope of the patent application attached.

【Symbol Description】

100: Wearable Human Insulin Injection Liquid Supply Device

1: Main body

11: accommodating space

12: Airbag

13: Micro gas pump

131: Micro gas delivery device

131a: Air intake plate

131b: Resonant sheet

131c: Piezoelectric Actuators

132: Micro valve device

132a: Gas Gathering Plate

132b: valve piece

132c: Exit Plate

2: Ring belt structure

3: Carrier

31: Cover

32: Cover

4: Liquid storage chamber

41: Liquid storage outlet

5: Diversion actuation unit

51: Liquid guide channel

511: Pressure Chamber

512: Entryway

513: Exit Channel

514: Chamber

515: convex structure

52: Liquid guide outlet

53: Actuator

531: Carrier

532: Actuating element

54: valve plate

541: Through hole

542: Central Department

543: Connector

6: Valve switch

61: Holder

62: Seals

63: Displacement parts

611, 621, 631: Through hole

7: Microneedle patch

71: Hollow microneedles

8: Sensor

9: Driver chip.

Claims (17)

1. A wearable human body insulin injection and supply device comprises:

a body having an accommodating space;

the two ends of the ring belt structure are connected with the two sides of the body;

a carrier disposed in the accommodating space of the body;

a liquid storage cavity, configured on the carrier to store insulin liquid, and having a liquid storage outlet;

a flow guiding actuating unit, configured on the carrier, having a fluid guiding channel, communicating with the liquid storage outlet of the liquid storage chamber, and communicating with a fluid guiding outlet, where the fluid guiding channel includes a pressure chamber, an inlet channel and an outlet channel, the inlet channel communicates with the liquid storage outlet of the liquid storage chamber, the outlet channel communicates with the fluid guiding outlet, the inlet channel and the outlet channel are separated from each other and communicate with each other through the pressure chamber, and the flow guiding actuating unit is provided with an actuator to seal the pressure chamber to drive and compress the volume of the pressure chamber, so that the insulin liquid is extruded and flows and is output from the fluid guiding outlet, and valve plates are respectively disposed in the inlet channel and the outlet channel for actuating the flow guiding actuating unit to compress the pressure chamber to control the opening and closing states of the inlet channel and the outlet channel;

the liquid storage outlet and the liquid guide outlet are respectively provided with a valve switch;

a micro-needle patch attached below the flow guide actuating unit to seal the liquid guide outlet, and having a plurality of hollow micro-needles for minimally invasive insertion into human skin to guide out the insulin liquid to be injected into subcutaneous tissue;

the sensor is arranged on the carrier and is used for resisting a monitoring numerical value of blood sugar content in the sweat monitored on the skin of the human body;

the air bag is arranged on the ring belt structure;

a micro air pump communicated with the air bag; and

the driving chip is arranged on the carrier and used for controlling the actuation of the flow guide actuation unit, the actuation of the micro gas pump, the control of the switch states of the plurality of valve switches and receiving the monitoring numerical interpretation of the sensor;

therefore, the ring belt structure is worn on the skin of a human body, the driving chip controls the micro gas pump to actuate to inflate the air bag, the ring belt structure is tightly attached to the skin of the human body, the micro needle patch can be inserted into the skin of the human body in a minimally invasive way through the plurality of hollow micro needles, when the sensor monitors a specific blood sugar content monitoring value in sweat flowing out of the skin of the human body, the driving chip controls the diversion actuating unit to actuate, and simultaneously controls the valve switch of the liquid guide outlet to open and the valve switch of the liquid storage outlet to open, so that insulin liquid stored in the liquid storage chamber is output from the outlet hole, guided into the micro needle patch and guided out by the plurality of hollow micro needles to be injected into subcutaneous tissues.

2. The wearable human insulin injection and supply device of claim 1, wherein the actuator comprises a supporting member and an actuating element, the supporting member covers the pressure chamber and is attached to a surface of the pressure chamber, the actuating element is deformed to drive the supporting member to vibrate up and down to compress the volume of the pressure chamber, so that the insulin liquid flows under pressure.

3. The wearable human insulin infusion and supply device of claim 2, wherein the actuator is a piezoelectric element.

4. The wearable human insulin injection and supply device of claim 1, wherein the carrier has a protrusion structure at the inlet channel and the outlet channel to generate a pre-force against the valve plate to prevent the insulin liquid from flowing backwards.

5. The wearable human insulin injection and supply device of claim 1, wherein the driving chip comprises a graphene battery to provide power.

6. The wearable human insulin infusion and supply device of claim 1, wherein the plurality of valve switches respectively comprise a retaining member, a sealing member and a displacement member, wherein the displacement member is disposed between the retaining member and the sealing member, and the retaining member, the sealing member and the displacement member respectively have a plurality of through holes, and the plurality of through holes of the retaining member and the displacement member are aligned with each other and the sealing member and the plurality of through holes of the retaining member are misaligned.

7. The wearable human insulin infusion and supply device of claim 6, wherein the displacement member is a charged material and the retaining member is a conductive material with two polarities, such that the displacement member and the retaining member maintain different polarities and approach the retaining member to open the valve switch.

8. The wearable human insulin infusion and supply device of claim 6, wherein the displacement member is a charged material and the retaining member is a conductive material with two polarities, such that the displacement member and the retaining member maintain the same polarity and approach the sealing member to close the valve switch.

9. The wearable human insulin infusion and supply device of claim 6, wherein the displacement member is a magnetic material and the retaining member is a magnetic material with a controllable polarity reversal, such that the displacement member and the retaining member maintain different polarities and approach the retaining member to open the valve switch.

10. The wearable human insulin infusion and supply device of claim 6, wherein the displacement member is a magnetic material and the retaining member is a magnetic material with a controllable polarity reversal such that the displacement member and the retaining member maintain the same polarity and approach the sealing member to close the valve switch.

11. The wearable human insulin injection and supply device of any one of claims 7 to 10, wherein the polarity of the holder is controlled by the driving chip.

12. The wearable human insulin infusion and supply device of claim 1, wherein the micro gas pump is a piezoelectric actuated micro pneumatic power device, and the micro pneumatic power device comprises a micro gas transmission device and a micro valve device, and when gas is transmitted from the micro gas transmission device to the micro valve device, pressure collection or pressure relief is performed.

13. The wearable human insulin infusion and supply device of claim 12, wherein the micro gas delivery device comprises an air inlet plate, a resonator plate and a piezoelectric actuator stacked in sequence, wherein when the piezoelectric actuator is actuated, gas enters from the air inlet plate and is delivered downward, thereby allowing one-way flow of gas in the micro valve device, and the micro valve device comprises a gas collecting plate, a valve plate and an outlet plate stacked in sequence, an outlet end of the outlet plate being in communication with the air bag; when the gas is transmitted from the micro gas transmission device into the micro valve device, the gas is transmitted to the air bag through the outlet end of the outlet plate to perform pressure collection operation, or the gas is decompressed through a pressure relief hole of the outlet plate.

14. The wearable human insulin injection and supply device of claim 1, wherein the hollow microneedles of the microneedle patch have an inner diameter of 10-550 μm.

15. The wearable human insulin injection and supply device of claim 1, wherein the length of the hollow microneedles of the microneedle patch is between 400 and 900 microns.

16. The wearable human insulin injection and supply device of claim 1, wherein the plurality of hollow microneedles are arranged in an array, and the distance between each two hollow microneedles is greater than 200 μm.

17. The wearable human insulin injection and supply device of claim 1, wherein the plurality of hollow microneedles are made of a silica material.

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