CN109718420B - Wearable human insulin injection and 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 and supply device

[ technical field ] A method for producing a semiconductor device

The present invention relates to a liquid supply device, and more particularly to a wearable human insulin injection liquid supply device for human insulin injection.

[ background of the invention ]

At present, the treatment modes aiming at the first type diabetes and the second type diabetes mainly comprise the supplement of hypoglycemic drugs, and the administration modes comprise oral administration, syringe injection and insulin pump injection. In the oral administration and injector injection modes, a patient needs to use a glucometer to take blood to detect the self blood sugar level every day, and then takes medicine according to the blood sugar level. The insulin pump system consists of a remaining needle and an insulin pump, wherein the remaining needle is arranged in the body and fixed on the body surface for blood sampling and drug injection; the insulin pump connected with the indwelling needle can control and release the hypoglycemic drug according to the blood sugar level.

Insulin can not be directly taken orally, but only by injection. The indwelling needle of the syringe injection and the insulin pump not only can cause pain to patients during injection, but also can leave a needle hole on the body surface. In particular, the injection of the syringe often requires multiple times a day, which can cause subcutaneous tissue to become hard due to frequent injections. The insulin pump reduces the injection times by adopting the indwelling needle, but has certain volume and weight due to integral installation, is inconvenient to carry about, and can influence the daily life and the movement of a patient when arranged on the body.

Aiming at the defects, the scheme develops a safe, portable and painless intelligent wearable human insulin injection and supply device, provides a patient to inject human insulin in daily life so as to control the blood sugar level at any time, and solves the problem of the traditional injection mode.

[ summary of the invention ]

In order to solve the problem that the traditional insulin injection mode causes pain to patients and is inconvenient to carry, the scheme provides a wearable human body insulin injection liquid supply device, which comprises a body, a liquid storage tank and a liquid supply device, wherein the body is provided with an accommodating space; the two ends of the annular 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 guide actuating unit, configured on the carrier, having a liquid guide channel, communicating with the liquid storage outlet of the liquid storage chamber and communicating with a liquid guide outlet, so that the insulin liquid is transported and output from the liquid guide outlet after being driven by the flow guide actuating unit; 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; the driving chip is arranged on the carrier and used for controlling the actuation of the flow guide actuating unit, controlling the switching states of the valve switches and receiving the monitoring numerical interpretation of the sensor; therefore, the girdle 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 girdle structure is clung 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 by the plurality of hollow micro needles, and 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 flow guide actuating unit to actuate, and simultaneously controls the valve switch of the liquid storage outlet to open and the valve switch of the liquid guide outlet to open, so that insulin liquid stored in the liquid storage cavity is output from the liquid guide outlet and guided into the microneedle patch, and the insulin liquid is guided out by the plurality of hollow micro needles to be injected into subcutaneous tissues.

[ description of the drawings ]

Fig. 1 is a schematic structural diagram of the wearable human insulin injection and supply device.

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

Fig. 3 is a cross-sectional view of the wearable human insulin injection and supply device shown in fig. 2.

Fig. 4A and 4B are schematic diagrams illustrating an operation flow of the wearable human insulin injection and supply device shown in fig. 3.

Fig. 5 is a schematic view of a valve plate of the wearable human insulin injection and supply device.

Fig. 6A is a schematic view of a valve switch structure of the wearable human insulin injection and supply device.

Fig. 6B is a schematic diagram of the valve switch shown in fig. 6A.

FIG. 7 is a schematic diagram illustrating electrical connections between components of the wearable human insulin injection and supply device.

Fig. 8 is a schematic view of the wearable human insulin injection and supply device worn on a user.

Fig. 9A and 9B are schematic structural views of the miniature air pump of the wearable human insulin injection and supply device.

[ embodiment ] A method for producing a semiconductor device

Exemplary embodiments that embody the features and advantages of this disclosure are described in detail below. It will be understood that the present disclosure is capable of various modifications without departing from the scope of the disclosure, and that the description and drawings are to be regarded as illustrative in nature, and not as restrictive.

The present application relates to a wearable human body insulin injection and supply device, please refer to fig. 1, fig. 2 and fig. 3,

the wearable human insulin injection and supply device 100 comprises a body 1, an annulus structure 2, a carrier 3, a liquid storage chamber 4, a flow guide actuating unit 5, a plurality of valve switches 6, a microneedle patch 7, a sensor 8 and a driving chip 9. Wherein, the body 1 has a containing space 11, and two ends of the girdle structure 2 are connected to two sides of the body 1, so that the body 1 is fixed on the body of the user through the girdle structure 2 (as shown in fig. 8), such as: the wrist, ankle, neck and other parts to achieve the purpose of wearing and improve the convenience of carrying; the carrier 3 is accommodated in the accommodating space 11 of the body 1, a liquid storage chamber 4 is concavely arranged on the carrier for storing liquid of insulin of a human body, and the carrier is provided with a liquid storage outlet 41 for leading out the insulin liquid in the liquid storage chamber 4, and the liquid storage chamber 4 is concavely arranged on the carrier 3 and sealed by a cover plate 31; the flow guide actuating unit 5 is configured on the carrier 30 and has a liquid guide channel 51 and a liquid guide outlet 52, the liquid guide channel 51 is communicated with the liquid storage outlet 41 of the liquid storage chamber 4, and after the flow guide actuating unit 5 is actuated, an absorbing force is generated to absorb insulin liquid in the liquid storage chamber 4 through the liquid storage outlet 41 communicated with the liquid guide channel 51, the insulin liquid enters the flow guide actuating unit 5 and is then discharged from the liquid guide outlet 52; the number of the valve switches 6 is two in the present embodiment, but not limited thereto, the valve switches 6 are respectively disposed at the liquid storage outlet 41 and the liquid guide outlet 52 and seal the two, and the flow rate of the insulin liquid passing through the liquid storage outlet 41 and the liquid guide outlet 52 is further controlled by the opening/closing state (on/off) of the valve switches 6, so as to avoid the occurrence of the over-dose or the insufficient insulin;

the microneedle patch 7 is attached below the flow guide actuating unit 5 and seals the liquid guide outlet 52, the microneedle patch 7 is provided with a plurality of hollow microneedles 71, when the liquid guide outlet 52 discharges insulin liquid, the hollow microneedles 71 are inserted into the skin of a human body through non-invasive or minimally-invasive insertion, and the insulin liquid is injected into subcutaneous tissues; the sensor 8 and the driving chip 9 are integrated on the carrier 1 by adopting a Micro Electro Mechanical System (MEMS), and the sensor 8 is constructed on the carrier 3 and can monitor sweat by abutting against human skin so as to obtain a monitoring value of the blood sugar content; in addition, the surface of the body 1 adjacent to the skin of the user has a through hole (not shown) which is communicated with the accommodating space 11 and through which the microneedle patch 7 passes to contact the skin of the user.

The plurality of hollow microneedles 71 of the microneedle patch 7 are micro-sized needle holes 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 micro-needle 71 is for insulin molecules to pass through, preferably, the inner diameter of the hollow micro-needle 71 is between 10 micrometers (mum) and 550 micrometers (mum), the length of the hollow micro-needle 71 is between 400 micrometers (mum) and 900 micrometers (mum), and the hollow micro-needle can be inserted into the subcutaneous tissue of the human body without penetrating into the depth to touch the nerve of the human body, thereby causing no pain at all. The hollow microneedles 71 are arranged on the microneedle patch 7 in an array manner, the distance between every two adjacent hollow microneedles 71 needs to be larger than 200 micrometers, and the interference of mutual influence on flow guiding is avoided, so that the hollow microneedles 71 arranged in the array manner do not have the function that one hollow microneedle 71 is blocked to influence the fluid injection, and the other hollow microneedles 71 can continue to have the function of fluid injection in a time-keeping manner.

Referring to fig. 3, the fluid guiding channel 51 of the fluid guiding actuation unit 5 includes a pressure chamber 511, an inlet channel 512 and an outlet channel 513, the inlet channel 512 is used for communicating the liquid storage outlet 41 of the liquid storage chamber 4, the outlet channel 513 is communicated with the fluid guiding outlet 52, the inlet channel 512 and the outlet channel 513 are communicated and separated from each other on the carrier 3, the carrier 3 is provided with a pressure chamber 511 in a concave manner to communicate with one end of the inlet channel 512 and one end of the outlet channel 513, the upper side of the pressure chamber 511 is sealed by the actuator 53, the inlet channel 512 is provided on the carrier 3 and is sealed by a sealing cover 32 at the other end, the other end is communicated with the liquid storage outlet 41 of the liquid storage chamber 4 to form a sealed fluid channel, and the opening formed at the other end of the outlet channel 512 is the fluid guiding outlet 52. Thus, the inlet channel 512, the pressure chamber 511, the outlet channel 513 and the liquid outlet 52 are connected in series to form a fluid passage.

The flow-guiding actuator unit 5 further includes an actuator 53, the actuator 53 has a carrier 531 and an actuator 532, the carrier 531 covers the sealed pressure chamber 511, and the actuator 532 is attached to the surface of the carrier 531, and the actuator 532 deforms to drive the carrier 531 to vibrate up and down, thereby changing the volume of the pressure chamber 511, so that the pressure inside the pressure chamber 511 changes to generate a pumping force to deliver the liquid insulin.

As shown in fig. 3 and fig. 5, a valve plate 54 may be disposed on the inlet channel 512 and the outlet channel 513 of the flow-guiding actuating unit 5, and a chamber 514 and a protrusion structure 515 are disposed on the carrier 3 at a middle section of the inlet channel 512 and the outlet channel 513, respectively, wherein the protrusion structure 515 is disposed at the inlet channel 512 and is disposed at the bottom of the chamber 514, the protrusion structure 515 is disposed at the outlet channel 512 and is disposed at the top of the chamber 514, and the valve plate 54 is disposed with a plurality of through holes 541 corresponding to a partial region of the chamber 514 to form a central portion 542 connected to the plurality of connecting portions 543, so that the central portion 542 is elastically supported, and thus the valve plate 54 covers the chamber 514 of the inlet channel 512 and the outlet channel 513, respectively, and drives the central portion 542 to generate a pre-force effect by abutting against the protrusion structure 515.

Therefore, as shown in fig. 4A, 4B and 5, when the valve switch 6 of the liquid storage outlet 41 is opened, and the flow guiding actuating unit 5 starts to start, a pressure difference is generated in the flow guiding actuating unit 5, and the central portion 542 of the valve plate 54 on the inlet channel 512 is driven to move upward away from the protrusion structure 515 at the inlet channel 512, so that the insulin liquid in the inlet channel 512 can enter the pressure chamber 511 through the at least one through hole 541 of the valve plate 54, and as shown in fig. 4B, after the insulin liquid enters the pressure chamber 511, the central portion 542 of the valve plate 54 on the outlet channel 513 is driven by 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 moves downward away from the protrusion structure 515 at the outlet channel 513, so that the insulin liquid enters the liquid guiding outlet 52. With the above arrangement, when the actuator 53 is not operated, the central portion 542 of the valve plate 54 on the inlet channel 512 and the outlet channel 513 can be respectively sealed off from the inlet channel 512 and the outlet channel 513, so that the backflow of insulin liquid in the inlet channel 512 and the outlet channel 513 can be prevented.

Referring to fig. 6A and 6B, the valve switch 6 includes a retaining member 61, a sealing member 62, and a displacement member 63. The displacement member 63 is disposed between the holder 61 and the sealing member 62 and is displaced therebetween, the holder 61 is provided with at least two through holes 611, the displacement member 63 is provided with a through hole 631 at a position corresponding to the through hole 611 of the holder 61, the through holes 611 of the holder 61 and the through holes 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 through hole 611 of the holder 61 are misaligned. The holder 61, the sealing member 62 and the displacement member 63 of the valve switch 6 may be made of graphene material to form a miniaturized valve member.

In a first embodiment of the valve shutter 6, the displacement member 63 is a charged material, the holding member 61 is a conductive material with two polarities, and the holding member 61 is electrically connected to a control circuit of the driving chip 9 for controlling the polarity (positive polarity or negative polarity) of the holding member 61. If the displacement member 63 is made of a material with negative charge, when the valve switch 6 needs to be controlled to open, the driving chip 9 controls the holding member 61 to form a positive electrode, and the polarity of the displacement member 63 is different from that of the holding member 61, so that the displacement member 63 approaches the holding member 61 to open 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 needs to be controlled to be closed, the driving chip 9 controls the retaining member 61 to form a negative electrode, and the displacement member 63 and the retaining member 61 maintain the same polarity, so that the displacement member 63 approaches the sealing member 62, thereby closing the valve switch 6 (as shown in fig. 6A).

In a second embodiment of the present valve switch 6, the displacement member 63 is a magnetic material, and the retaining member 61 is a magnetic material with controllable polarity. 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 made of a magnetic material with a negative polarity, when the valve switch 6 needs to be controlled to be opened, the holding member 61 forms a magnetic property with a positive polarity, and the driving chip 9 controls the displacement member 63 and the holding member 61 to maintain different polarities, so that the displacement member 63 approaches the holding member 61, and the valve switch 6 is opened (as shown in fig. 6B). On the contrary, if the displacement member 63 is a magnetic material with a negative polarity, when the valve switch 6 needs to be controlled to be closed, the driving chip 9 controls the holding member 61 to form a magnetic property with a negative polarity, and at this time, controls the displacement member 63 and the holding member 61 to maintain the same polarity, so that the displacement member 63 approaches the sealing member 62, thereby closing the valve switch 6 (as shown in fig. 6A).

As shown in fig. 1 and fig. 2, the wearable human insulin injection and supply device further includes an air bag 12 and a micro air pump 13, the air bag 12 is disposed on the inner surface of the cuff structure 2 adjacent to the user, the micro air pump 13 is disposed on the cuff structure 2 in a manner of communicating with the air bag 12, and the micro air pump 13 is electrically connected to the driving chip 9. When the micro air pump 13 starts to start after receiving the inflation signal transmitted by the driving chip 9, air is sucked from the outside and transmitted to the air bag 12 for inflation, so that the hollow microneedles 71 of the microneedle patch 7 can be inserted into the skin of the human body, so as to inject insulin liquid.

Referring to fig. 7, which is a schematic diagram illustrating electrical connection of relevant components of a wearable human insulin injection liquid supply device in a preferred embodiment of the present disclosure, a driving chip 9 is configured on a carrier 3 and electrically connected to a micro gas pump 13, a flow guide actuation unit 5, a plurality of valve switches 6 and a sensor 8, the sensor 8 is pressed against the skin of a human body to monitor the blood glucose content in sweat of the human body and generate a corresponding monitoring value, and the driving chip 9 receives the monitoring value of the sensor 8 and then determines whether to start the flow guide actuation unit 5 and the plurality of valve switches 6 for insulin liquid injection. The driving chip 9 may further include a graphene battery (not shown) for providing power.

Please refer to fig. 8, which is a schematic view showing that the wearable human insulin injection and supply device is worn on a user, and starts when the micro air pump 13 receives an inflation signal transmitted by the driving chip 9, and sucks air from the outside and transmits the air to the air bag 12 for inflation, so that the hollow microneedles 71 of the microneedle patch 7 can be inserted into the skin of the human body, so as to facilitate the injection of insulin liquid.

Referring to fig. 9A and 9B, the micro gas pump 13 may be a piezoelectric-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 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. Wherein the micro gas transmission device 131 comprises an air inlet plate 131a, a resonance plate 131b and a piezoelectric actuator 131c stacked in sequence, wherein when the piezoelectric actuator 131c is driven, the gas enters from the air inlet plate 131a and is transmitted downwards, so that the gas can flow in one direction in the micro valve device 132, and the micro valve device 132 comprises 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 airbag 12; when the gas is transmitted from the micro gas transmission device 131 to the micro valve device 132, the gas is transmitted to the airbag 12 through the outlet end of the outlet plate 132c for pressure concentration operation, or the gas is released through a pressure release hole of the outlet plate 132c for pressure release operation.

In summary, the wearable human insulin injection and supply device provided by the present application generates a pressure gradient through the actuation of the diversion actuation unit to transmit the insulin liquid in the liquid storage chamber, and finally injects the insulin liquid into the skin of the user by using the microneedle patch to provide the insulin of the user, and detects the blood glucose content of the user by using the sensor, and controls the diversion actuation unit and the valve switch to adjust the flow rate and the flow velocity of the insulin liquid injected into the user by using the driving chip. Therefore, the wearable human insulin injection and supply device can provide the function of the pancreas and can be used as a substitute for the traditional artificial pancreas.

The present disclosure may be modified by anyone skilled in the art without departing from the scope of the appended claims.

[ notation ] to show

100: wearable human insulin injection and supply device

1: body

11: containing space

12: air bag

13: miniature gas pump

131: miniature gas transmission device

131 a: air inlet plate

131 b: resonance sheet

131 c: piezoelectric actuator

132: micro valve device

132 a: air collecting plate

132 b: valve plate

132 c: outlet plate

2: ring belt structure

3: carrier

31: cover plate

32: closure member

4: liquid storage chamber

41: liquid storage outlet

5: flow-guiding actuating unit

51: drainage channel

511: pressure chamber

512: inlet channel

513: outlet channel

514: chamber

515: convex part structure

52: liquid guiding outlet

53: actuator

531: bearing part

532: actuating element

54: valve plate

541: through hole

542: center part

543: connecting part

6: valve switch

61: holding member

62: sealing element

63: displacement member

611. 621, 631: through hole

7: microneedle patch

71: hollow microneedle

8: sensor with a sensor element

9: and a driving 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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