TWM560894U - Micropump - Google Patents

Abstract

The present invention provides a micro pump for implantation into human blood, comprising: a substrate, a plurality of flow guiding channels are prepared by a nanometer process, and the guiding channel includes an inlet channel, an outlet channel and a divergent channel, and a flow guiding actuation a unit, the nanometer process manufacturing structure is capped on the pressure chamber, and a power source is applied to actuate the volume of the compression pressure chamber to generate a fluid flow; the micro pump is implanted into the human blood to drive the communication connector of the wafer Accepting external command communication, and driving the wafer to enable the flow-guiding actuator unit and the micro-mirror, while controlling the opening of the outlet port and the valve opening of the storage outlet, and allowing the storage chamber to be stored by actuation of the actuation unit The fluid therapy drug delivers an exit port that is delivered to a blood vessel of a human in need of treatment.

Description

Micro pump

This case is about a micro pump, especially a micro pump that is thin, thin and silent.

In the current situation, the patient must use the medicine regularly or when the body feels uncomfortable, and when the patient takes the medicine, the medicine is orally or injected into the patient's body or blood vessel, and the patient must Carrying a therapeutic drug or an injection tool with you, such as missing a drug treatment, may cause irreparable harm to the patient. In addition, the patient must carry the therapeutic drug or the injection tool with him or her, and it is very inconvenient to live or go out.

Therefore, how to develop a defect that can improve the above-mentioned conventional techniques can overcome the physical condition of the patient at any time and anywhere, and immediately deliver the therapeutic drug to the blood of the human body, which is an urgent problem to be solved.

The main purpose of this case is to provide micro-pumping, which can be implanted into human blood by nanometer process design to overcome the current situation and unable to detect the human body condition at any time and timely deliver the therapeutic drug.

In order to achieve the above purpose, the present invention provides a micro pump for implantation into human blood, comprising: a substrate, a plurality of flow guiding channels formed by a nanometer process, and a recessed pressure chamber and a reservoir chamber a flow channel including an inlet channel, an outlet channel, and a branch channel, the branch channel communicating with the inlet channel, and closing the inlet channel with a first cover member, The outlet channel and the branch channel, and the first cover member is respectively provided with an inlet hole and an outlet hole corresponding to the inlet channel and the outlet channel, and the pressure chamber communicates with the inlet channel and the outlet channel respectively, and the outlet channel The storage chamber is closed by a second cover member, so that a fluid therapy drug is stored inside the storage chamber, and the storage chamber has a storage outlet connected to the branch channel; a flow guiding actuating unit, Sealing the pressure chamber with a nanometer process manufacturing structure, applying a power source to actuate and compress the volume of the pressure chamber to generate a fluid flow; and a plurality of valve switches to seal the inlet hole and the outlet by a nanometer process a drive, a drive wafer, a nanometer process and a system package on the substrate to provide power and control actuation of the flow control unit, and to provide control of the plurality of valve switches a switching state, wherein the driving chip comprises a communication connector; and a micro mirror, which is fabricated in a nanometer process and the system package is mounted on the substrate, controlled by the driving wafer; and the micro pump is implanted In the body blood, the communication connector of the driving chip receives external command communication, so that the driving chip enables the current guiding unit and the micromirror, and simultaneously controls the inlet hole and the valve of the outlet hole The opening of the switch can be displaced by the kinetic energy of the fluid flow in the human blood, and is monitored by the micro-mirror to be positioned on the human blood vessel to be treated, and the valve switch that controls the inlet hole is closed, and the outlet is controlled. The opening of the valve and the valve opening of the storage outlet is caused by the actuation of the flow guiding actuating unit to allow the fluid therapeutic drug stored in the storage chamber to be delivered to the outlet hole and delivered to the blood vessel of the human body requiring treatment.

1‧‧‧Substrate

11‧‧‧Entry channel

12‧‧‧Export channel

13‧‧‧Different channels

14‧‧‧pressure chamber

15‧‧‧Storage chamber

151‧‧‧reservoir

16‧‧‧First cover

161‧‧‧ entrance hole

162‧‧‧Exit hole

17‧‧‧Second cover

18a, 18b‧‧‧ chamber

19a, 19b‧‧‧ convex structure

2‧‧‧drain actuation unit

21‧‧‧Ship

22‧‧‧Actuating element

3, 3a, 3b, 3c‧‧‧ valve switch

31‧‧‧ Holder

311, 321, 331‧‧‧ through holes

32‧‧‧Seal

33‧‧‧ displacement parts

34‧‧‧ accommodating space

4‧‧‧Drive chip

5‧‧‧Microscope

6‧‧‧ Fluid therapy drugs

100‧‧‧ valve

100a, 100b‧‧‧through areas

101a, 101b‧‧‧ valve pieces

102a, 102b‧‧‧ extended bracket

103a, 103b‧‧‧ hollow holes

Fig. 1 is a schematic cross-sectional view showing the micropump of the first embodiment of the present invention.

2A to 2D are schematic views showing the operation flow of the micropump fluid shown in Fig. 1.

3A to 3C are schematic views showing the operation flow of the micropump fluid according to the second embodiment of the present invention.

Fig. 4 is a front elevational view showing the micropump valve diaphragm of the second embodiment of the present invention.

Fig. 5A and Fig. 5B are schematic diagrams showing the operation of the valve switch of the present invention.

Some exemplary embodiments embodying the features and advantages of the present invention are described in detail in the following description. It is to be understood that the present invention is capable of various modifications in various aspects, and is not to be construed as a limitation.

The micro-pump in this case is suitable for implantation into human blood, and at the same time, it can simultaneously detect the health status of the patient and can immediately deliver the therapeutic effect. Referring to FIG. 1 , in the first embodiment of the present invention, the micro pump includes a substrate 1 , a flow guiding actuating unit 2 , a plurality of valve switches 3 , a driving wafer 4 , and a micromirror 5 . Among them, the substrate 1, the flow guiding actuating unit 2, the plurality of valve switches 3, the driving wafer 4 and the micromirror 5 are all produced by a nanometer process technology.

The substrate 1 is made up of a plurality of flow guiding channels in a nanometer process, including an inlet channel 11, an outlet channel 12, and a branch channel 13, wherein the branching channel 13 communicates with the inlet channel 11, and the substrate 1 is sealed by the first cover member 16. Covering the inlet passage 11, the outlet passage 12, and the branch passage 13, and the first cover member 16 is provided with an inlet hole 161 corresponding to one end of the inlet passage 11, and the first cover member 16 is provided with an outlet hole 162 corresponding to one end of the outlet passage 12, and a base The material 1 is recessed with a pressure chamber 14 and a reservoir chamber 15, and the pressure chamber 14 communicates with the inlet passage 11 and the outlet passage 12, respectively, and the second cover member 17 covers the storage chamber 15 The reservoir chamber 15 is formed into a space for storing the fluid therapy drug 6, and the reservoir chamber 15 has a reservoir outlet 151 communicating with the branching channel 13 and the plurality of valve switches 3 including a valve switch 3a. The inlet port 161 is closed, a valve switch 3b is provided to close the outlet port 162, and a valve switch 3c is provided to close the port outlet 151.

Continuing to refer to FIG. 1 , the flow guiding unit 2 is structurally capped on the pressure chamber 14 and includes a carrier 21 and an actuating element 22 , wherein the actuating element 22 can be a piezoelectric element, but none of them Limited. The carrier member 21 covers the pressure chamber 14 and attaches an actuating member 22 to a surface thereof. The actuating member 22 further has a positive electrode and a negative electrode (not shown) for driving the wafer 4. The electrical connection causes the actuation element 22 to be deformed by applying a voltage to drive the reciprocating vibration of the carrier 21 in a reciprocating manner in the vertical direction, thereby compressing the volume of the pressure chamber 14 to cause the pressure chamber 14 to be generated. Pressure changes for fluid transfer. The driving chip 4 system package is disposed on the substrate 1 to provide power and control actuation of the flow guiding actuation unit 2, and controls the plurality of valve switches 3 to be in a switching state, and the driving wafer 4 has a communication connector (not shown). To receive external commands, wherein the communication connector can be wirelessly transmitted, transmitted in a Bluetooth mode, etc., but not limited thereto. In the micropump of the first embodiment of the present invention, the driving chip 4 further includes a graphene battery (not shown) for electrically connecting with the positive electrode and the negative electrode of the actuating element 22 of the flow guiding actuating unit 2 for providing Drive power. The micromirror 5 system package is mounted on the substrate 1 and controlled by the driver wafer 4 to be activated.

Referring to FIG. 2A and FIG. 2B, first, the micro pump is implanted in the patient's blood, and the external command is received by the communication connector of the driving chip 4, and the communication connector receives an external command to drive the chip. 4 controlling the flow guiding actuating unit 2 to actuate and control the activation of the micromirror 5, and simultaneously controlling the valve switch 3a of the inlet hole 161 and the valve switch 3b of the outlet hole 162 to open, thereby forming a kinetic energy displacement of the fluid flow in the blood of the patient. And monitoring through the micro-mirror 5 to locate the blood vessels that the patient needs to treat.

Referring to FIG. 2C and FIG. 2D, when the micropump is implanted in the blood of the patient and is monitored by the micromirror 5 to be positioned on the blood vessel to be treated by the patient, the re-drive causes the drive wafer 4 to control the closing of the valve switch 3a of the inlet hole 161. And simultaneously controlling the opening of the valve switch 3b of the outlet hole 162 and the valve switch 3c of the storage outlet 151, such that the actuating element 22 receives the voltage and acts to cause the carrier 21 to deform and resonate, and when the carrier 21 vibrates upward, When the volume of the pressure chamber 14 is increased, the fluid therapy drug 6 flows out in response to the pressure change of the pressure chamber 14, and is collected to the pressure chamber 14 of the substrate 1 via the inlet channel 11, and then the carrier 21 vibrates downward, so that The volume of the pressure chamber 14 becomes smaller, so that the fluid therapy drug 6 conforms to the pressure change of the pressure chamber 14, and is delivered to the blood through the outlet port 162 through the outlet port 12, by repeating the above 2C The fluid pumping operation of the micropump shown in Fig. 2D causes the actuating element 22 to continuously reciprocally vibrate up and down, continuously continuing to direct the fluid therapy medicament 6 from the reservoir outlet 151 of the reservoir chamber 15 to the outlet port 162. , the delivery of fluid therapy drug 6 is delivered to the blood vessels of the patient in need of treatment.

Referring to FIGS. 3A, 3B, and 3C, in the second embodiment of the present invention, the substrate 1 may further be provided with a chamber 18a and a chamber 18b in the inlet passage 11 and the outlet passage 12, respectively. The material 1 is further provided with a convex portion structure 19a, 19b at the chamber 18a of the inlet passage 11 and the chamber 18b of the outlet passage 12, and the convex portion structure 19a is disposed at the inlet passage 11 to be disposed at the bottom of the chamber 18a. The protrusion structure 19b is disposed at the outlet passage 12, and is disposed at the top of the chamber 18b, and the micro pump may further be provided with a valve sheet 100. Referring to FIG. 4 again, the valve plate 100 retains two valve sheets 101a, 101b of the same thickness in each of the two through regions 100a, 100b, and a plurality of extension brackets 102a are disposed around the periphery of the valve sheets 101a, 101b. 102b is elastically supported, and each of the extending brackets 102a, 102b is formed with a hollow hole 103a, 103b adjacent to each other, so that the valve pieces 101a, 101b can be elastically supported by the extending brackets 102a, 102b. The deformation and displacement amount form a valve switch structure. The valve pieces 101a, 101b may be round, rectangular, square or various geometric patterns, but are not limited thereto. Referring also to FIGS. 3B and 3C, the valve piece 101a covers the inlet passage 11 and abuts against the convex structure 19a in the inlet passage 11 to generate a pre-force effect, which contributes to a larger The pre-covering effect is to prevent backflow, and the valve piece 101b covers the outlet passage 12 and fits against the convex portion structure 19b of the outlet passage 12 to generate a pre-force effect, which helps to generate a larger pre-prevention. The capping effect is applied to prevent backflow, so that the micropump of the present case does not cause a backflow between the inlet passage 21 and the outlet passage 12 of the micropump without being actuated.

Referring to FIGS. 3B, 3C, and 4, the valve pieces 101a, 101b of the valve plate 100 are actuated by the flow-guiding actuation unit 2 to compress the pressure chamber 14, thereby controlling the inlet passage 11 and the outlet. The opening or closing state of the mouth channel 12 does not cause a backflow effect. As shown in FIG. 3B, when the driving wafer 4 controls the opening of the valve switch 3c of the accumulating outlet 151, the fluid therapy drug 6 is introduced into the branching channel 13 to communicate with the inlet channel 11, and the actuating element 22 receives the voltage to generate an action. The carrier 21 is driven to deform upwardly to increase the volume of the pressure chamber 14, and the valve piece 101a of the inlet passage 21 is quickly disengaged from the contact protrusion structure 19a, and the valve piece 101b of the outlet passage 12 is also closely resisted by the suction force. The convex structure 19b is closed, and the fluid therapy drug 6 is sucked into the chamber 18a by the suction hole 103a in the inlet passage 21, and is collected to the pressure chamber 14. Next, as shown in FIG. 3C, the carrier 21 is driven to deform downwardly to make the pressure chamber 14 smaller in volume, and the valve piece 101a of the inlet passage 21 is closed by the thrust returning against the convex portion structure 19a, and no backflow is generated. The valve piece 101b of the outlet passage 12 is also opened by the thrust quickly disengaging the convex protrusion structure 19b, and the fluid therapeutic drug 6 collected in the pressure chamber 14 is squeezed into the inlet passage 21 into the chamber 18b by the hollow hole 103b, and then It is delivered by the outlet passage 12 to the outlet opening 162. By repeating the fluid transfer operation of the micropumps of the above FIGS. 3B to 3C, the pressure chamber 14 is continuously reciprocally vibrated up and down via the actuating element 22, and the fluid therapeutic drug 6 can be continuously discharged from the reservoir. The reservoir outlet 151 of the chamber 15 continues to be directed toward the outlet port 162 to effect delivery of the fluid therapy drug 6 to the blood vessel of the patient in need of treatment.

In the first embodiment of the valve switch 3, the valve switch 3 includes a holding member 31 and a sealing member 32, as shown in FIGS. 5A and 5B. And the displacement member 33. The displacement member 33 is disposed in the accommodating space 34 formed between the holder 31 and the sealing member 32. The holder 31 has at least two through holes 311, and the displacement member 33 is also disposed corresponding to the position of the through hole 311 of the holder 31. The through hole 331, the through hole 311 of the holding member 31 and the through hole 331 of the displacement member 33 are disposed substantially in alignment with each other, and the sealing member 32 is provided with at least one through hole 321 and the through hole 321 of the sealing member 32 is The position of the through hole 311 of the holder 31 is misaligned and not aligned. When the displacement member 33 is pushed by the fluid, It will be displaced upward in the direction of the fluid flow in the direction of the arrow, so that the displacement member 33 abuts against the holder 31 while opening the through hole 321 of the sealing member 32, and the fluid can be introduced through the through hole 321 of the sealing member 32 due to the displacement member 33. The position of the through hole 331 is substantially aligned with the through hole 311 of the holding member 31, so that the through holes 331 and 311 can be electrically connected to each other to complete the opening of a valve.

Further, in the second embodiment of the valve switch 3 of the present invention, the displacement member 33 is a charged material, and the holder 31 is a two-polar conductive material. The holder 31 is electrically connected to the driving wafer 4 for controlling the polarity (positive polarity or negative polarity) of the holder 31. If the displacement member 33 is a negatively charged material, when the valve switch 3 is to be controlled to open, the driving wafer 4 controls the holding member 31 to form a positive electrode, and at this time, the displacement member 33 and the holder 31 maintain different polarities, thus causing the displacement member 33 approaches the holder 31, constituting the opening of the valve switch 3 (as shown in Fig. 5B). On the other hand, if the displacement member 33 is a negatively charged material, when the valve switch 3 is to be controlled to be closed, the driving wafer 4 controls the holding member 31 to form a negative electrode, at which time the displacement member 33 and the holder 31 maintain the same polarity to cause displacement. The member 33 approaches the seal 32 to form a closure of the valve switch 3 (as shown in Figure 5A).

Further, in the third embodiment of the valve switch 3 of the present invention, the displacement member 33 is a magnetic material, and the holder 31 is a magnetic material which can be controlled to change polarity. The holder 31 is electrically connected to the driving wafer 4 for controlling the polarity (positive or negative) of the holder 31. If the displacement member 33 is a magnetic material with a negative electrode, when the valve switch 4 has to be controlled to open, the holding member 31 forms a magnetic pole of the positive electrode, and at this time, the driving wafer 4 controls the displacement member 33 and the holder 31 to maintain different polarities, so that the displacement member 33 Adjacent to the holder 31, the opening of the valve switch 3 is formed (as shown in Fig. 5B). On the other hand, if the displacement member 33 is a magnetic material with a negative electrode, when the valve switch 3 is to be controlled to be closed, the holding member 31 forms a magnetic property of the negative electrode, and at this time, the driving wafer 4 controls the displacement member 33 and the holding member 31 to maintain the same polarity, so that The displacement member 33 approaches the seal 32, constituting the closing of the valve switch 3 (as shown in Fig. 5A).

In summary, the micro pump provided in this case is implanted in the patient's blood and driven by crystal The chip communication connector receives an external command, drives the wafer control diversion actuating unit and activates the micro mirror to start, and simultaneously controls the valve switch and the valve switch to open, thereby displacing the kinetic energy of the fluid flow in the blood of the patient. . In addition, the opening of the valve opening of the outlet port and the outlet port is controlled, and the fluid therapeutic agent stored in the reservoir chamber is delivered to the outlet hole by the actuation of the flow guiding actuating unit, and is delivered to the blood vessel of the patient in need of treatment. , 俾 achieve the transmission of fluid therapy drugs. In addition, the case is implanted into the human blood through micro-pumping, and the detection can detect the patient's needs anytime and anywhere, and immediately deliver the therapeutic drugs, thereby achieving the high-efficiency and flexible use.

This case has been modified by people who are familiar with the technology, but it is not intended to be protected by the scope of the patent application.

Claims (13)

A micropump for implanting human blood, comprising: a substrate, a plurality of flow guiding channels formed by a nanometer process, and a recessed pressure chamber and a storage chamber, the flow guiding channel comprising An inlet channel, an outlet channel and a branch channel, the branch channel communicating with the inlet channel, and covering the inlet channel, the outlet channel and the branch channel with a first cover member, and the first cover member corresponds to the inlet An inlet hole and an outlet hole are respectively disposed in the passage and the outlet passage, and the pressure chamber respectively communicates with the inlet passage and the outlet passage, and the storage chamber is closed by a second cover member to make the storage chamber The chamber is configured to store a fluid therapy drug, and the reservoir chamber has a storage outlet connected to the branch channel; a flow guiding unit is mounted on the pressure chamber by a nanometer manufacturing structure, and is applied The power source is actuated to compress the volume of the pressure chamber to generate a fluid flow; a plurality of valve switches are used to seal the inlet hole, the outlet hole, and the storage outlet in a nanometer process; and a driving wafer is fabricated in a nanometer process And a package is mounted on the substrate to provide power and control actuation of the flow-guiding actuation unit, and to provide a switching state for controlling the plurality of valve switches, the drive wafer including a communication connector; and a micro-mirror, Formed in a nanometer process and the system package is mounted on the substrate, controlled by the driving chip; the micro pump is implanted into human blood, and the communication connector of the driving chip receives external command communication, so that The driving chip enables the flow guiding actuating unit and the micromirror, and simultaneously controls the opening of the inlet hole and the outlet opening of the valve opening to displace and transmit the kinetic energy of the fluid flow in the human blood. The microscopic mirror is positioned to be positioned on the blood vessel of the human body requiring treatment, and the valve switch for controlling the inlet hole is closed, and the opening of the valve switch of the outlet port and the outlet is controlled to control the opening of the valve. The fluid therapeutic drug stored in the reservoir is delivered to the outlet port for delivery to the blood vessel of the subject in need of treatment. The micropump according to claim 1, wherein the flow guiding unit comprises a carrier member and an actuating member, the carrier member covers the pressure chamber, and the actuation is attached to a surface An element for applying a power source to the actuating element to cause deformation deformation of the carrier to cause the fluid to be squeezed between the inlet passage and the outlet passage. The micropump of claim 2, wherein the actuating element is a piezoelectric element. The micropump according to claim 1, further comprising a valve piece respectively disposed in the inlet passage and the outlet passage, wherein the pressure chamber is controlled by the actuation of the flow guiding actuation unit to control the The switching state of the inlet channel and the outlet channel. The micropump according to claim 4, wherein the substrate has a convex structure at the inlet passage and the outlet passage to generate a pre-force to contact the valve plate to prevent the fluid from flowing backward. The micropump of claim 1, wherein the drive wafer comprises a graphene battery to provide a power source. The micro pump according to claim 1, wherein the communication connector wirelessly transmits and receives communication and transmits communication. The micro pump according to claim 4, wherein the valve switch comprises a holding member, a sealing member and a displacement member, wherein the valve plate is disposed between the holding member and the sealing member, and the holding The sealing member and the valve plate respectively have a plurality of through holes, and the plurality of through holes on the holding member and the displacement member are substantially aligned with each other, and the plurality of through holes of the sealing member and the holding member are disposed. To form a misalignment misalignment. The micro pump according to claim 8, wherein the displacement member is a charged material, and the holder is a bipolar conductive material to maintain the displacement member and the holder in different polarities. Approaching the retaining member constitutes opening of the valve. The micro pump according to claim 8, wherein the displacement member is a charged material, and the holder is a bipolar conductive material to maintain the displacement member and the holder. The same polarity, and approaching the seal, constitutes the closing of the valve. The micropump according to claim 8, wherein the displacement member is a magnetic material, and the holding member is a magnetic material of controlled polarity, so that the displacement member and the holder are maintained differently. The polarity, which is close to the holder, constitutes the opening of the valve. The micro pump according to claim 8, wherein the displacement member is a magnetic material, and the holder is a magnetic material of controlled polarity, so that the displacement member maintains the same as the holder. The polarity, while approaching the seal, constitutes the closure of the valve. The micropump of any one of clauses 9 to 12, wherein the holder controls its polarity by the drive wafer.