CN220955989U - Pneumatic micropump, medicine storage bin and artificial cochlea system - Google Patents
Pneumatic micropump, medicine storage bin and artificial cochlea system Download PDFInfo
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- CN220955989U CN220955989U CN202322193372.8U CN202322193372U CN220955989U CN 220955989 U CN220955989 U CN 220955989U CN 202322193372 U CN202322193372 U CN 202322193372U CN 220955989 U CN220955989 U CN 220955989U
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- pump body
- pneumatic micropump
- micropump
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Landscapes
- Reciprocating Pumps (AREA)
Abstract
The utility model discloses a pneumatic micropump, which comprises a pump body, wherein a diaphragm is arranged in the pump body, the diaphragm separates a pump cavity of the pump body into a liquid cavity and an air cavity, and a liquid outlet of the pump body is connected with the liquid cavity; the liquid cavity is used for storing liquid medicine, a reversible thermal decomposition/thermal adsorption solid substance and a driving piece are arranged in the liquid cavity, and the driving piece is used for controlling the reversible release or absorption of the solid substance; when the driving piece controls the solid matters to release gas, the membrane deforms and pushes the liquid medicine in the liquid cavity to move towards the liquid outlet of the pump body; the valve is arranged at the liquid outlet of the pump body and used for limiting the liquid medicine to flow into the liquid cavity from the liquid outlet; the pneumatic micropump has no risk of liquid leakage, has the functions of pumping and self-priming, and has the advantages of simple structure and low processing difficulty.
Description
Technical Field
The utility model belongs to the technical field of medical appliances, and particularly relates to a pneumatic micropump, a medicine storage bin and an artificial cochlea system.
Background
Micropumps are used as the 'heart' of a microfluidic system, are power sources for microfluidic transport, and are also important markers of the development level of microfluidic systems. As an important micro-execution part, the micro-pump can be widely applied to the fields of micro-injection, drug delivery systems, blood transportation and the like, and has huge market application prospect.
In the medical field, for special reasons, some patients need frequent injections of the corresponding drugs over a long period of time to meet the requirements of the body to maintain a stable and healthy corresponding function, such as continuous analgesia for surgical or painful patients, or continuous stabilization for insulin supplementation for diabetic patients. The traditional method is that medical staff or patients use needle injectors to manually inject medicine to focus (such as eyeballs, inner ears and the like) according to a certain time interval, on one hand, the human tissues are damaged, on the other hand, the medicine injection time and the medicine injection amount are difficult to adjust, and the intellectualization and automation of medicine injection cannot be realized. In addition, systemic administration may not be feasible for many drugs due to various physiological barriers of the human body (blood-labyrinthine, blood-brain, blood-retina, tear film, cornea, etc.). Systemic administration may also cause adverse reactions to other organs of the body, or some systemic disease patients may have contraindications for drugs, such as diabetes, hypertension, gastric ulcers, for whom systemic hormone therapy is not administered. Thus, implantable topical drug delivery systems are receiving increasing attention. Topical administration can be classified into passive and active modes according to the mode of release of the drug. Passive topical administration often involves the placement of a solid drug in the vicinity of a lesion in a carrier or coating loading, and the slow release of the drug component to the target site for treatment. However, passive local administration is difficult to effectively control the release process and behavior of the drug, and intelligent and automatic administration is not possible. Active local drug delivery often uses a power system to deliver drug liquid to a focus, and the power system controls the flow rate, flow rate and delivery process of the drug liquid, so that the purposes of controllable, safe, intelligent and customized drug delivery and treatment can be achieved. To meet the miniaturization of implant requirements, such powered systems are most typically micropumps.
Micropumps are of various types and can be classified into mechanical micropumps and non-mechanical micropumps according to their structures. The non-mechanical micropump converts non-mechanical energy into kinetic energy of the microfluid, has no moving parts, and has the advantages of simple structure and continuous and stable flow, but has the defects of high processing difficulty, or special requirements (such as dielectric, conductivity and electrolyte) on the fluid, or small flow and the like. Mechanical micropumps rely on moving parts to transport and control fluids, including traditional mechanical as well as reciprocating diaphragm (vibrating diaphragm) type. Conventional mechanical micropumps mostly employ springs, pistons or micro-motors as a source of driving power, but it is difficult to achieve a fast and stable delivery speed at the same time and to miniaturize due to an unstable driving force caused by the springs or the micro-motors. Vibrating diaphragm type micropump relies on a driver to deform a diaphragm, causing changes in volume and pressure within a pump chamber, thereby delivering fluid in a directional manner, which is the main micropump type. Vibrating diaphragm micropumps can be classified into electrostatic driving, piezoelectric driving, electrically actuated polymer driving (ICPF), electromagnetic driving, hot air driving, phase change driving, bimetal effect driving, shape memory alloy driving, and the like according to the driving manner thereof. Wherein the electromagnetic drive is difficult to meet the requirement of MRI compatibility when delivering medical liquid in human body due to the existence of the permanent magnet. Phase change drives produce a change in volume primarily by evaporation/condensation of material during heating/cooling, thereby driving the diaphragm to pump fluid. Hot air drives are often also provided with air chambers, which are heated/cooled to cause the gas to expand/contract, thereby pumping the fluid.
Currently, the driving mode of pneumatic micropump mainly includes air heating/cooling, liquid evaporation/vapor condensation, and chemical reaction to produce gas (electrochemical, catalytic, and photodegradation). If the ideal gas treatment is performed, according to the ideal gas state equation pv=nrt, in the case of a fixed volume, the pressure increase of the air micropump when the air micropump is heated from 25 ℃ to 100 ℃ is 25%, and the pumping flow rate is low. The working chamber of the evaporating micropump needs to contain volatile liquid, there is a risk of leakage, and the vapor contacts the upper low temperature part to have a possibility of condensation, so that temperature uniformity in the whole working chamber needs to be ensured. In addition, air and high temperature gas at the upper end of the evaporative micropump contact the membrane, possibly leading to deterioration of the pumped fluid. Liquid is also present in the working chambers of electrochemical and catalytic gas-generating micropumps, thus risking leakage. In addition, the electrodes of the electrochemical micropump are easily corroded or detached, and it is difficult to ensure the reliability of long-term pumping. The driving force of the catalytic gas-generating micropump is continuously reduced as the reactants are consumed. The working cavity of the photodegradation gas-generating micropump is free of liquid, but the light-responsive material needs to ensure higher light absorption efficiency, the micropump needs to be designed in a light transmission/shading way, the structure is complex, and a light source component is additionally arranged for delivering liquid medicine when the micropump is implanted in a body, so that the cost is high and the difficulty is high. Finally, as the chemical reactions of the electrochemical, catalytic and photodegradation gas-generating micropump are all irreversible reactions, the micropump has the capacity of pumping fluid only and cannot self-absorb, namely the micropump is a non-reciprocating mechanical micropump.
In summary, the existing pneumatic micropump has the problems of liquid leakage, pumping only without self-priming, complex structure and low long-term reliability.
Disclosure of utility model
In order to solve the problems, the technical scheme of the utility model is as follows: the device comprises a pump body, wherein a diaphragm is arranged in the pump body, the diaphragm isolates a pump cavity of the pump body into a liquid cavity and an air cavity, and a liquid outlet of the pump body is connected with the liquid cavity; the liquid cavity is used for storing liquid medicine, a reversible thermal decomposition/thermal adsorption solid substance and a driving piece are arranged in the liquid cavity, and the driving piece is used for controlling the reversible release or absorption of the solid substance; when the driving piece controls the solid matters to release gas, the membrane deforms and pushes the liquid medicine in the liquid cavity to move towards the liquid outlet of the pump body; the liquid pump also comprises a valve which is arranged at the liquid outlet of the pump body and used for limiting the liquid medicine to flow back to the liquid cavity from the liquid outlet.
Preferably, the liquid cavity comprises an inner cavity and an outer cavity, a one-way valve used for limiting the liquid medicine to flow into the outer cavity from the inner cavity is arranged between the inner cavity and the outer cavity, the inner cavity is connected with a liquid outlet of the pump body, and the diaphragm is positioned between the inner cavity and the air cavity.
Preferably, a supporting member for supporting the membrane is arranged in the air cavity, and the supporting member has a limiting effect on the bulge of the membrane towards the air cavity.
Preferably, a thermal insulation member is provided between the support member and the solid substance.
Preferably, the inner wall of the liquid cavity is provided with a hydrophilic coating, and the inner wall of the air cavity is provided with a heat-insulating coating.
Preferably, the driving member includes a driver including a solid material, a heat conductive member, a heating member, and a cooling member arranged in this order in a direction from the diaphragm to the bottom of the pump.
Preferably, the drive comprises at least one of the drives.
Preferably, the driving piece further comprises a controller and a power supply, wherein the controller is electrically connected with the refrigerating piece and the heating piece respectively, and the power supply is electrically connected with the controller and is used for supplying power to the refrigerating piece and the heating piece.
The medicine storage bin comprises the pneumatic micropump, wherein the pneumatic micropump is positioned in the medicine storage bin and used for pumping medicine liquid.
The artificial cochlea system comprises a medicine storage bin, wherein a liquid outlet of the medicine storage bin is connected with a liquid inlet of the pneumatic micropump, and the pneumatic micropump conveys medicine liquid in the medicine storage bin to a medicine feeding port of the artificial cochlea.
The utility model has the beneficial effects that:
1. The pneumatic micropump driving process of the present application relies on solid substances to release or absorb gas without risk of liquid leakage.
2. The pneumatic micropump has the functions of pumping and self-priming based on the reversible process of heating release and cooling absorption of the gas, and the gas release and absorption process is realized by controlling heating or refrigerating through a circuit, so that the pumping fluid can be intelligently controlled and customized, the flow rate and flow rate range are wide, the performance decline of long-term pumping is low, and the driving force is sufficient.
3. The pneumatic micropump can be connected with the existing medicine storage bin through the connector or is designed into a whole in the medicine storage bin, can replace a power system in the existing active implantation instrument with a medicine liquid delivery function and is connected through the connector, and can also be designed into a microfluidic chip, and the pneumatic micropump has the advantages of simple structure, low processing difficulty, flexible design and wide applicability.
4. The heating and cooling in the pneumatic micropump of the present application is concentrated only in a local area, and thus has less effect on the temperature of the pumped fluid, and does not cause deterioration or failure of components such as drugs in the fluid.
5. The pneumatic micropump of the application does not use ferromagnetic materials, and is particularly suitable for a power system, such as a cochlear implant system, in an active implantation instrument which is compatible with magnetic resonance and has a drug delivery function.
Drawings
FIG. 1 is a schematic diagram of the overall structure of a pneumatic micropump according to an embodiment of the present utility model;
FIG. 2 is a schematic diagram of the overall structure of a pneumatic micropump according to an embodiment of the present utility model;
FIG. 3 is a schematic diagram of a different deformation driver of a pneumatic micropump according to an embodiment of the present utility model;
FIG. 4 is a schematic diagram of the structure of a check valve in a pneumatic micropump according to an embodiment of the present utility model;
Fig. 5 is a schematic structural diagram of a pumping solution of a pneumatic micropump according to an embodiment of the present utility model;
Fig. 6 is a schematic structural diagram of a pumped liquid medicine of a pneumatic micropump according to an embodiment of the present utility model;
FIG. 7 is a schematic diagram of a pneumatic micropump according to an embodiment of the present utility model disposed in a drug storage compartment for pumping a drug solution;
Fig. 8 is a graph of liquid flow data for a pneumatic micropump according to an embodiment of the present utility model.
Detailed Description
Preferred embodiments of the present utility model will be described in detail below with reference to the accompanying drawings.
Referring to fig. 1, the pneumatic micropump of the present application includes a pump body 1, a pump cavity, and a valve 8 disposed at a liquid outlet 720 of the pump body 1 for restricting backflow of liquid medicine from the liquid outlet 720 to the liquid cavity. A diaphragm 3 is provided in the pump body 1, and the diaphragm 3 separates the pump chamber into a liquid chamber and a gas chamber 220. The liquid outlet 720 of the pump body 1 is connected with a liquid cavity, and the liquid cavity is used for storing liquid medicine. The air cavity 220 is internally provided with a solid substance 440 capable of being reversibly thermally decomposed/thermally adsorbed and a driving member for controlling the reversible release or absorption of gas from the solid substance 440; when the driving member controls the solid substance 440 to release gas, the membrane 3 deforms and pushes the liquid medicine in the liquid cavity to move towards the liquid outlet 720 of the pump body 1.
Referring to fig. 1, the liquid chamber includes an inner chamber 210 and an outer chamber 710, a check valve for restricting the flow of the liquid medicine from the inner chamber 210 into the outer chamber 710 is provided between the inner chamber 210 and the outer chamber 710, the inner chamber 210 is adjacent to the liquid outlet 720 of the pump body 1, and the diaphragm is located between the inner chamber 210 and the air chamber 220. Based on other considerations, the inner walls of lumen 210 and lumen 220 may be optionally treated with a functional coating, e.g., the inner walls of lumen 210 may be coated with a hydrophilic coating, which may reduce the flow resistance of the medical fluid; the inner wall of the air chamber 220 is treated with a thermal barrier coating to improve heating/cooling efficiency and reduce the effect of temperature effects on the liquid medicine in the inner chamber 210.
Referring to fig. 1 and 2, a support 450 for supporting the membrane 3 is provided in the air chamber 220, said support 450 having a limiting effect on the bulge of the membrane 3 in the direction of the air chamber 220. As shown in fig. 2A, the support 450 may be located under the membrane 3 with a certain spacing. In the case that the volume of the pumping chamber is determined, compared with the case that the supporting member 450 is in close contact with the diaphragm 3, after the liquid medicine enters the inner chamber 210 of the liquid chamber, the diaphragm 3 is deformed downward due to the gravity of the liquid medicine, so that the volume of the inner chamber 210 becomes large, and thus, the maximum pumping liquid amount of the pneumatic micro pump is improved to some extent. The degree of lifting of the maximum pumping fluid volume is related to the position of the supporting member 450, but the strength and elasticity of the diaphragm 3 are also considered, and the higher the degree of lifting of the maximum pumping fluid volume is, the higher the strength and elasticity of the diaphragm 3 are required. Fig. 2B shows an example structure when the driver 4 is not provided with a support 450, which is actually the limit case in fig. 2A. The degree of lifting of the maximum pumping liquid amount is maximized at this time, but the more severe the requirements for the membrane 3 are. For safety and reliability reasons, the drive 4 should be provided with a support 450. Finally, if the cavity 210 is positioned below the air cavity 220, the support 450 may not be provided in the driver 4. Thus, the support 450 may be flexibly selectively arranged according to the structural characteristics of the micropump.
As shown in fig. 1 and 3, the driver includes a driver 4, a controller 5, and a power supply 6. The actuator 4 sequentially arranges the refrigerating member 410, the heating member 420, the heat conducting member 430, and the solid substance 440 in the direction from the diaphragm 3 to the bottom of the pump. The controller 5 is electrically connected to the refrigerating element 410 and the heating element 420, and the power supply 6 is electrically connected to the controller 5 for supplying power to the refrigerating element 410 and the heating element 420. The driving piece can be provided with one or even a plurality of drivers 4, and the drivers 4 can be independently operated and controlled, so that the release rate of the gas can be better regulated and controlled, and the control of the flow rate is more accurate. Second, when one of the plurality of drivers 4 fails, the operation of the other drivers 4 is not affected, so that the risk resistance is higher.
There are a number of variations of the driver 4 due to the heating/cooling rate considerations. For example, the cooling element 410/heating element 420/heat conducting element 430/solid substance 440/heat conducting element 430, the cooling element 410/heat conducting element 430/solid substance 440/heat conducting element 430/heating element 420. Additionally, in the above variations, since the cooling member 410 and the heating member 420 are electrically connected to the controller 5, both sides of the cooling member 410 and the heating member 420 may be further provided with electrical insulators (not shown) to prevent the electrical short circuit. In particular, in the case of a micro pump for micro flow control processed by MEMS, each functional component in the driver 4 can be flexibly designed according to specific requirements, and heating/cooling rate, heat transfer efficiency, electrical insulation, size requirements, and the like are comprehensively considered.
The refrigeration member 410 in the drive 4 is a peltier or other type of refrigeration device, the refrigeration process being controllable by an electrical circuit. The heating member 420 may be one of a heating plate, a heating wire, a heating film, or the like, and other types of heating devices, and the heating process may be controlled by an electric circuit. The heat conductive member 430 mainly plays a role of heat conduction between the cooling member 410 and the heating member 420 and the solid substance 440 to achieve rapid temperature rise or temperature drop, and thus the heat conductive member 430 is required to have high heat conductivity. Since the cooling member 410 and the heating member 420 are electrically connected to the controller 5, the heat conductive member 430 may be selectively electrically insulated, or an electrical insulating member (not shown) as described above may be employed. The heat conductive member 430 is made of one of heat conductive silicone rubber, heat conductive silicone resin, aluminum oxide, silicon carbide, aluminum nitride, and the like, and a combination thereof.
The controller 5 is often programmable so that the pumping process of the medical fluid can be controlled remotely from the outside, which is particularly important for locally targeted therapy in the patient. When the pneumatic micropump is defined as an implanted micropump, the external device is in wireless connection with the implanted micropump to control the delivery of the liquid medicine through a preprogrammed delivery program, so that the purpose of customized and intelligent treatment is achieved. Additionally, the controller 5 and the power supply 6 may be configured separately or perform the corresponding functions with existing equipment. For an artificial cochlea system with the function of local drug delivery of the inner ear, the functions of the controller 5 and the power supply 6 are realized by an electronic circuit in the artificial cochlea implant, the outer cavity 710 of the micropump is connected with a drug storage bin liquid outlet of a drug storage bin in the artificial cochlea, and the liquid outlet 720 of the micropump is connected with a drug delivery channel, so that local controllable drug delivery of the inner ear is realized.
The electrical connection between the refrigerating element 410 and the heating element 420 and the controller 5 spans the pump body 1. Although there is no liquid in the air chamber 220, the outside of the pump body 1 may be in contact with liquid, for example, human tissue. To achieve complete isolation of the "wet" and "dry" structures, the electrical connection may be accomplished through ceramic feedthroughs (vias) in hermetic packaging techniques to enhance the reliability of the micropump.
In addition, the support 450 between the membrane 3 and the solid substance 440 needs to have a high strength to ensure that the gravity action of the liquid medicine above the membrane 3 does not cause the destruction of the membrane 3. Since the gas 470 acts on the membrane 3 to pump the liquid medicine, the gas 470 needs to penetrate the support 450, so the support 450 should have no adsorption effect on the gas 470. Additionally, the support 450 may be provided with micro-porous or macro-porous structures to facilitate the passage of the gas 470. The material of the supporting member 450 is one of metal/metal alloy (stainless steel, titanium and titanium alloy, platinum, iridium, platinum iridium alloy, gold or tantalum), inorganic material (ceramic, glass) or polymer material (polyetheretherketone PEEK, polycarbonate PC, parylene, polyethylene PE, polypropylene PP, polyvinylchloride PVC, polyimide PI, polytetrafluoroethylene PTFE, perfluoroethylene propylene copolymer FEP, polystyrene PS, polyurethane PU, acrylonitrile ABS, polymethyl methacrylate PMMA, polyethylene terephthalate PET), and combinations thereof. The support 450 may be further subjected to a heat-shielding coating process, or a heat-shielding member (not shown) may be provided above or below the support 450, in view of temperature-influencing effects on the medical fluid.
As shown in fig. 5, the solid substance 440 releases a gas 470 when heated and forms a solid product 460; the product 460 absorbs the gas 470 and regenerates the solid 440 upon cooling. For example, the solid substance 440 based on the above characteristics may be the thermal decomposition material 4401 or the adsorption material 4402. The thermal decomposition material 4401 may be selected from one of sodium bicarbonate, sodium carbonate, potassium bicarbonate, potassium carbonate, magnesium bicarbonate, magnesium carbonate, calcium bicarbonate, calcium carbonate, ammonium bicarbonate, ammonium carbonate, basic copper carbonate, etc., and combinations thereof. The adsorption material 4402 may be selected from one of activated carbon, graphene, carbon nanotubes, diatomaceous earth, zeolite molecular sieves, mesoporous silica, activated alumina, metal Organic Frameworks (MOFs), covalent Organic Frameworks (COFs), and the like, and combinations thereof. The main performance parameter of the solid mass 440 is the equivalent gas quantity and critical temperature. Illustratively, the equivalent gas amount of sodium bicarbonate is 0.006mol/g, the critical temperature is 50 ℃, i.e., 1g of sodium bicarbonate releases 1mol of gas 470 when heated above 50 ℃. As another example, the equivalent gas amount of ammonium bicarbonate is 0.025mol/g and the critical temperature is 58 ℃. Since the adsorption material 4402 itself has no gas 470 component, the adsorption material 4402 may be used as the solid material 440 after the adsorption treatment of the gas 470, and the adsorbed gas 470 may be selected from one of carbon monoxide, carbon dioxide, nitrogen, argon, methane, and the like, and combinations thereof. Illustratively, 1g of activated carbon adsorbs 0.001mol of gas 470 at 30 ℃, and the adsorbed activated carbon desorbs the gas at 80 ℃, i.e., the equivalent gas amount is 0.001mol/g, the critical temperature is 30 ℃ (gas 470 release temperature) and 80 ℃ (gas 470 adsorption temperature). The thermally decomposable material 4401 or the adsorbent material 4402 may be in powder form, in which case a carrier material 4403 may be used to impart a particular shape characteristic to the solid mass 440. The carrier material 4403 is silicone rubber, resin, and the like having adhesive properties.
The membrane 3 should have a water-impermeable nature to ensure that the liquid medicine in the cavity 210 does not leak into the air cavity 220. Secondly, the membrane 3 has better flexibility and higher strength, and the membrane 3 cannot break in the up-and-down reciprocating vibration process. In addition, for the membrane 3 with low flexibility, the membrane 3 may have a non-planar structure such as curved surface, corrugation, saw tooth or fold, so that the vibration amplitude of the membrane 3 may be increased. When the membrane 3 with high elasticity is selected, the membrane 3 can be in a planar structure, and still has higher vibration amplitude at the moment, but the processing and manufacturing difficulties are relatively lower. The membrane 3 may be a single-layer membrane or a composite membrane to meet various functional requirements, and the membrane 3 is made of one of copper-zinc-aluminum, copper-aluminum, nickel-titanium, polyimide (PI), parylene (Parylene), polytetrafluoroethylene (PTFE), polyethylene terephthalate (PET), epoxy (SU-8), silicone rubber (Silicone), polydimethylsiloxane (PDMS), natural/synthetic rubber, thermoplastic elastomer (TPE), styrene-ethylene-butylene-styrene block copolymer (SEBS), styrene-ethylene-propylene-styrene block copolymer (SEPS), and the like, and a combination thereof. The membrane 3 may also be subjected to a functional coating treatment, for example, a waterproof coating is provided on the side of the membrane 3 located in the cavity 210, and a thermal insulation coating is provided on the side located in the cavity 220, so that the leakage risk of the liquid medicine and the influence of the temperature effect can be further reduced.
The valve 8 is mainly used for controlling the flow direction of the liquid medicine, namely, the liquid medicine flows from the inner cavity 210 to the liquid outlet 720. Referring to fig. 4, fig. 4A is a conventional one-way valve 810. When the pressure on the left side of the check valve 810 is greater than the pressure on the right side, the check valve 810 is opened to the right side and the liquid medicine flows to the right side; and when the pressure on the left side of the check valve 810 is smaller than the pressure on the right side, the check valve 810 is closed to the left side, preventing the liquid medicine from flowing to the left side. The valve 8 of the present application may also be an expanding shrink tube 820. Fig. 4B is an expanded shrink tube 820. In the expansion-contraction tube 820 structure, the tube diameter on the left side is smaller than the tube diameter on the right side, and thus the internal pressure on the left side is larger than the internal pressure on the right side, so that the net flow direction of the liquid medicine is rightward. Numerous solutions exist for valves in micropump or delivery devices, and thus the present application is described by way of example only and not by way of limitation.
The working process of the pneumatic micropump is as follows: when the pneumatic micropump is powered and the heating member 420 is activated by the controller 5, heat is transferred to the solid substance 440 via the heat conducting member 430, and when the temperature exceeds the critical temperature of the solid substance 440, the solid substance 440 generates a solid product 460 and releases a gas 470, the pressure of the air chamber 220 increases gradually along with the release of the gas 470, and the movement of the air-impermeable membrane 310 is driven, so that the liquid medicine in the inner cavity 210 is pushed to be pumped out from the liquid outlet 720. When heating is stopped, the product 460 is cooled down in a natural cooling manner or in a manner that the controller 5 starts the refrigerating member 410 to cool down, the product 460 absorbs the gas 470 and regenerates the solid substance 440, and the pressure in the air cavity 220 gradually decreases along with the absorption of the gas 470, so as to drive the air-impermeable membrane 310 to move, thereby pushing the liquid medicine to be self-absorbed into the inner cavity 210 from the liquid inlet 710, and preparing for the next pumping of the liquid medicine. The above procedure constitutes a single pumping. When the low-frequency pumping is needed, the natural cooling mode can be selected in the cooling process, so that the energy consumption of the micropump is reduced; when high frequency pumping is required, the time interval between pumping is shortened by starting the cooling of the refrigerating element 410, thereby improving pumping efficiency. Thus, flexible selection can be performed according to the requirements. By selecting a solid substance 440 with a large equivalent amount of gas, increasing the specific surface area of the solid substance 440, increasing the heating rate and heating temperature of the heating element 420, etc., the pumping flow rate, that is, the generation rate and flow rate of the gas 470 are positively correlated.
Fig. 5 shows the pumping process of the liquid medicine when the pneumatic micro pump is connected to the medicine storage bin 9 through the outer chamber 710 and pumps the liquid medicine. In fig. 5, the medicine storage bin 9 is included, the medicine storage bin includes a bin body 910, a medicine bin liquid outlet 930, and a medicine bin injection port 940, the fluid 920 is stored in the bin body 910, and the medicine bin injection port 940 can be used for supplementing the fluid 920 into the medicine storage bin 9. In fig. 5A and 5B, after the drug outlet 930 of the drug storage bin 9 is connected to the liquid inlet 710 of the micro pump, the drug solution flows into the inner cavity 210 of the micro pump due to the gravity of the drug solution in the drug storage bin 9. By heating the solid substance 440 by the controller 5, the solid substance 440 generates a solid product 460 and releases a gas 470, and the gas 470 pushes the gas-impermeable membrane 310 upward, thereby pumping out the medical fluid, at this time, the volume of the inner chamber 210 becomes smaller and the volume of the air chamber 220 increases, as shown in fig. 5C. After pumping is completed, the product 460 is cooled by the controller 5, the product 460 gradually absorbs the gas 470 and is reformed into the solid substance 440, at this time, the pressure in the air cavity 220 gradually decreases, the air-impermeable membrane 310 moves downward, and the medicine is self-sucked from the medicine storage bin 9 into the inner cavity 210, so as to prepare for the next medicine pumping. The above completes one pumping process of the liquid medicine.
Referring to fig. 6, for a micro pump without the support 450, the pumping process of the liquid medicine after it is connected with the medicine storage bin 9 is shown. The maximum pumping fluid amount of the pneumatic micropump without the support 450 is higher than that of the pneumatic micropump with the support 450 in fig. 5. In fig. 6B, the air-impermeable membrane 310 moves downward due to the gravity of the liquid medicine in the inner cavity 210 and the flexibility of the air-impermeable membrane 310, so that more liquid medicine can be contained in the inner cavity 210. The amplitude of the up-and-down movement of the air-impermeable membrane 310 increases, thereby increasing the amount of liquid pumped.
Referring to fig. 7, the micropump may further be disposed in the medicine storage compartment 9 and pump the medicine liquid, and the medicine storage compartment 9 includes a compartment body 910, a medicine compartment liquid outlet 930, and a medicine compartment injection port 940, and the medicine liquid is stored in the compartment body 910, and the medicine compartment injection port 940 may be used to supplement the medicine liquid into the medicine storage compartment 9. The pumping process of the liquid medicine is similar to that described above, and will not be repeated.
Fig. 8 shows the flow rate of the micro pump for 3 pumping processes under different pumping parameters. A: the temperature is T 1, the heating time is T 1, and the cooling mode is natural cooling; b: the temperature is T 1, the heating time is T 1, and the cooling mode is that the refrigerating piece 410 refrigerates; c: the temperature is T 1, the heating time is T 2, and the cooling mode is that the refrigerating piece 410 refrigerates; d: the temperature is T 2, the heating time is T 1, and the cooling mode is that the refrigerating piece 410 refrigerates. Wherein T 2>T1,t2>t1. When the heating temperature does not reach the critical temperature, the solid substance 440 does not release the gas 470 at this time, so that no pumping of the medical fluid is performed. And when the heating temperature exceeds the critical temperature and is maintained at a specific temperature, the solid substance 440 releases the gas 470 at a substantially steady rate and pumps the medical fluid. As can be seen from comparison of a and B, the forced cooling mode shortens the time interval between two pumps because the cooling effect of the refrigerating element 410 is higher than that of natural cooling. That is, the frequency of pumping can be increased by increasing the refrigerating efficiency. From the comparison of B and C, it can be found that under the condition of unchanged temperature, the heating duration can be prolonged to improve the flow rate of the liquid medicine pumped for a single time, and the flow rates of the two liquid medicines are basically the same, but the longer the heating duration is, the time required for cooling can be correspondingly prolonged. In B and D, the heating temperature is increased to obviously increase the flow rate of the liquid medicine, so that the flow rate of single pumping is larger under the condition of the same heating duration, but the increase of the heating temperature can prolong the cooling time on one hand and can increase the temperature effect on the other hand. In summary, controlling the heating rate, heating temperature, cooling rate, cooling temperature, heating duration, cooling duration, etc. can control the single pumping flow rate, pumping flow rate and frequency, and temperature effect of the micropump.
Finally, it is noted that the above-mentioned preferred embodiments are only intended to illustrate rather than limit the utility model, and that, although the utility model has been described in detail by means of the above-mentioned preferred embodiments, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the utility model as defined by the appended claims.
Claims (10)
1. The pneumatic micropump comprises a pump body, and is characterized in that a diaphragm is arranged in the pump body, the diaphragm isolates a pump cavity of the pump body into a liquid cavity and an air cavity, and a liquid outlet of the pump body is connected with the liquid cavity; the liquid cavity is used for storing liquid medicine, a reversible thermal decomposition/thermal adsorption solid substance and a driving piece are arranged in the liquid cavity, and the driving piece is used for controlling the reversible release or absorption of the solid substance; when the driving piece controls the solid matters to release gas, the membrane deforms and pushes the liquid medicine in the liquid cavity to move towards the liquid outlet of the pump body; the liquid pump also comprises a valve which is arranged at the liquid outlet of the pump body and used for limiting the liquid medicine to flow back to the liquid cavity from the liquid outlet.
2. A pneumatic micropump according to claim 1, wherein the fluid chamber comprises an inner chamber and an outer chamber, a one-way valve is disposed between the inner chamber and the outer chamber for restricting the flow of fluid from the inner chamber into the outer chamber, the inner chamber is connected to the fluid outlet of the pump body, and the diaphragm is disposed between the inner chamber and the air chamber.
3. A pneumatic micropump according to claim 2, wherein a support member for supporting the membrane is provided in the air chamber, said support member having a restraining effect on the membrane's bulge in the direction of the air chamber.
4. A pneumatic micropump according to claim 3, wherein a thermal insulation is provided between the support member and the solid substance.
5. A pneumatic micropump according to claim 1, wherein the inner wall of the fluid chamber is provided with a hydrophilic coating and the inner wall of the fluid chamber is provided with a thermal barrier coating.
6. A pneumatic micropump according to claim 1, wherein the driving means comprises a driver comprising a solid substance, a heat conducting means, a heating means and a cooling means arranged in this order in the direction from the diaphragm to the bottom of the pump.
7. A pneumatic micropump according to claim 6, wherein said driver comprises at least one of said drivers.
8. The pneumatic micropump of claim 6, wherein the driving member further includes a controller and a power source, the controller is electrically connected to the cooling member and the heating member, respectively, and the power source is electrically connected to the controller for supplying power to the cooling member and the heating member.
9. A drug reservoir comprising the pneumatic micropump of any of claims 1-8, wherein the pneumatic micropump is located within the drug reservoir for pumping a drug solution.
10. A cochlear implant system comprising the pneumatic micropump of any of claims 1-8, wherein the cochlear implant system comprises a drug storage compartment and a drug administration port, a liquid outlet of the drug storage compartment is connected to a liquid inlet of the pneumatic micropump, and the pneumatic micropump delivers the drug solution in the drug storage compartment to the drug administration port of the cochlear implant.
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