EP2758664A1 - Pompe d'injection d'un fluide, et notamment micropompe utilisable pour delivrer une dose determinee - Google Patents
Pompe d'injection d'un fluide, et notamment micropompe utilisable pour delivrer une dose determineeInfo
- Publication number
- EP2758664A1 EP2758664A1 EP12762286.8A EP12762286A EP2758664A1 EP 2758664 A1 EP2758664 A1 EP 2758664A1 EP 12762286 A EP12762286 A EP 12762286A EP 2758664 A1 EP2758664 A1 EP 2758664A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- sleeve
- fluid
- injection pump
- pump according
- resonator
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Withdrawn
Links
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Classifications
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
- F04B43/04—Pumps having electric drive
- F04B43/043—Micropumps
- F04B43/046—Micropumps with piezoelectric drive
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14212—Pumping with an aspiration and an expulsion action
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B19/00—Machines or pumps having pertinent characteristics not provided for in, or of interest apart from, groups F04B1/00 - F04B17/00
- F04B19/006—Micropumps
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
- F04B43/09—Pumps having electric drive
- F04B43/095—Piezoelectric drive
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04F—PUMPING OF FLUID BY DIRECT CONTACT OF ANOTHER FLUID OR BY USING INERTIA OF FLUID TO BE PUMPED; SIPHONS
- F04F7/00—Pumps displacing fluids by using inertia thereof, e.g. by generating vibrations therein
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
- F16K31/00—Actuating devices; Operating means; Releasing devices
- F16K31/004—Actuating devices; Operating means; Releasing devices actuated by piezoelectric means
- F16K31/005—Piezoelectric benders
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
- A61M2037/0007—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin having means for enhancing the permeation of substances through the epidermis, e.g. using suction or depression, electric or magnetic fields, sound waves or chemical agents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
- A61M37/0092—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin using ultrasonic, sonic or infrasonic vibrations, e.g. phonophoresis
Definitions
- the subject of the invention is a pump for injecting a fluid, and may especially relate to a micropump injection of a given dose of the fluid.
- actuating devices for biology and health in particular injectors and microdosors, capable of locally delivering volumes below the microliter with a resolution of nanolitre of gaseous products or low viscosity liquids by ultrasonic means.
- the dose to be delivered is preferably in the form of viscous liquid (gel) or very fluid on the contrary, but may also consist of fine powder.
- the grains of the powder may be nanocapsules possibly trapped in a gel or a hydrogel. It can also be used for other applications, in particular, for the deposition of ink on surfaces or the nebulization of gasoline, perfume, deodorant or particular products in a closed chamber or a room.
- the actuating device does not have moving or deformable mechanical parts.
- the fluid can be injected continuous, the dosage being obtained in an open loop by varying the duration and amplitude of activation or in a closed loop from a target value to be reached on the remaining level of the reservoir, the level being deduced from the frequency offset of a resonance characteristic of the volume of the tank.
- the device can be used in particular metered medical devices inserted into the human body, especially in the case of chronic dispensing of drugs at very low rates and over very long periods (typically more than 10 years).
- the actuation of the micro-pumps can be achieved in various ways, for example by emitting ultrasonic waves as in the case of the present invention, but also by peristaltic effect by electrostatic effect, thermo ⁇ pneumatic or electromagnetic.
- peristaltic effect by electrostatic effect, thermo ⁇ pneumatic or electromagnetic.
- a presentation of these different actuators can be found in the document by DJ Laser and JG Santiago entitled “a review of micropumps", J. Micromech. Microeng. 14 (2004), R35-64.
- Peristaltic pumps are the most popular in pharmaceutical dosage because, on the one hand, they avoid contact with the product to be delivered, on the other hand, they are not bulky and consume little current. Nevertheless, they are reproached for the repeated crushing of the pipe allowing the displacement of the fluid, which can cause fatigue or even abrasion of the material and tearing of material.
- Devices closest to the present invention are ultrasonic pumps.
- WO 02081867 (A1) by George Keilman (priority of April 9, 2001);
- the method is based on the focusing of a longitudinal wave in a chamber comprising an inlet with a large orifice for receiving the fluid to be pumped and an outlet with a small orifice into which the fluid must be pushed.
- the device uses a broadband transducer, non-planar, focusing longitudinal waves in the outlet, the focus may lead to a phenomenon of cavitation.
- the flow rates are of the order of several hundred milliliters per minute and the powers in play of several hundred watts.
- the chamber has any shape that should not interfere with the focusing effect of the broadband power transducer.
- the chamber may however be profiled in a parabolic form to conjugate a plane wave in its focal point.
- the chamber keeps in any case a tapered shape and preferably conical and arranged so that the tapered end corresponds with the focal point of the longitudinal waves.
- Longitudinal waves are of a progressive nature and so that they are not reflected in the enclosure nor generate stationary waves, a plastic material must absorb on the side of the exit.
- the fluid enters the enclosure on the transducer side.
- the principle of such an ultrasonic pump lies in the dissipation of vibratory energy absorbed by the fluid at the focal point and leading to the expulsion through the small orifice.
- the concentration of energy is such that a cavitation phenomenon can be generated. In this case, the phase changes of the liquid by micro-cavitations mechanically promote the expulsion of the liquid to the outlet.
- the main difference between the invention of G. Keilman and the present is that in this, the structure constituting the chamber plays a fundamental role in the generation of vibratory mode at the ejection nozzle, because in the present invention the chamber is in fact a solid solid cavity conveying flexural waves. Its mechanical excitation is performed at the resonance frequency of the full cavity.
- the resonator thus formed also produces a mechanical amplification of the ejection nozzle.
- the fluid absorbs much less energy than that of G. Keilman.
- the pumping is here obtained not by dissipation of energy in the fluid but by a phenomenon of lateral compression and centrifugation generated by a particular movement of the ejection nozzle.
- broadband operation and the use of cavitation greatly reduce the energy efficiency of the acoustic pump, which is therefore not suitable for being miniaturized, implantable and exploitable with a limited energy source.
- the rise in temperature is also not acceptable in a product intended to deliver pharmaceutical products.
- Non-ultrasonic piezoelectric devices may also be encountered to achieve accurate micropump drug dosing.
- This is notably the case of patent FR 2650634 (Al) by Harald Van Lintel of August 7, 1989.
- the pumping is obtained through the deformation of a wafer using a piezoelectric pellet.
- Periodic deformation of the piezoelectric wafer causes a periodic volume variation of a pumping chamber defined in a wafer of a material capable of being machined by photolitographic methods.
- the pump outlet is selectively closed by a diaphragm valve which is in direct communication with another valve through the pump chamber.
- the flow rates reached are from 30 to 60 ⁇ / min for differential pressures (outlet minus entry) of the order of 60 cm of water height.
- This method is compact and suitable for insulin dosage, but it is not ultrasound and its suction principle is different from the device according to the invention which uses an alternative centrifugation possibly combined with a projection effect. This In addition, the process encounters limitations related to the possible backflow of the product.
- a drug delivery device includes an implantable osmotic pump connected to a drug-containing housing, which housing is connected to a needle, cochlear implant, or other type of component for delivery to the target tissue.
- a subcutaneous port receives a liquid from an external pump. Said port is connected to a needle or other component for administering one or more drugs to the target tissue. Strong and liquid drug formulas can be used.
- a separate drug vehicle such as saline
- can be used to dissolve a portion of the solid drug the drug-laden vehicle then being delivered to the target tissue.
- the use of solid drugs combined with a separate medication vehicle is one way to resolve the insufficient autonomy of an osmotic pump.
- the non-refillable drug is stored as solid pellets and will dissolve slowly in a neutral fluid that is refillable via a standard access port.
- a problem to be solved thus concerns the micro-assay (less than 1 microliter, ie 1 mm 3 ) and preferably the determination of a volume with a resolution of about 1 nanoliter of a product contained in a small buffer tank containing a typical total volume of the order of one milliliter, but can typically reach 10 ml.
- the reservoir can be housed in a support structure such as a case or the body of a stylus or for the medical field, in a biocompatible housing implantable subcutaneously or even behind a bone wall.
- the tank is rechargeable.
- the product is preferably a low-viscosity liquid or an initially viscous liquid but whose viscosity very locally decreases at the level of the ultrasonic mechanical amplification following a rise in temperature caused by the viscous damping of the ultrasonic vibrations in contact with the product.
- the amplitude of the vibrations can be chosen so that the heating of the fluid remains at a permissible degree, which is valuable for delicate products such as drugs.
- the dosage is triggered either automatically and repeatedly if the device has an on-board power source giving it sufficient autonomy between two dosages, or on an ad hoc basis, on command, when the device is subjected to ultrasonic radiation allowing it to extract enough energy to put it into operation.
- the energy recovery can be carried out remotely through a wall or so transcutaneous by conventional inductive method or ultrasonic method.
- the device according to the invention can accept high operating temperatures typically greater than 300 ° C in the nebulization zone.
- the ultrasonic principle used does not exploit the electrostatic forces that can be found in the electro-fluidic devices, and is not influenced by them.
- the metering device may be covered with a hydrophilic layer in the reservoir and in the supply capillary up to the ejection nozzle and hydrophobic in the area of the ejection or nebulization orifice of a droplet. .
- Another problem to solve is more generally to make the pump compatible with biological applications, and in particular to allow it to be implanted safely inside a living body with stable operation, a sufficiently small volume, and during long run times without replacement, which excludes any mechanism that could fail or require maintenance.
- Another problem to be solved is to extract a dose of a tank designed so that no static leakage flow is possible and form drops quickly enough to prevent evaporation into the environment (it stands out and the osmotic pumps) .
- the reservoir is not necessarily under pressure nor, in case of implantation, necessarily hermetic in which case anti-bacteria or anti-virus filters can protect the contents.
- a metering device able on the one hand to capture and convert vibratory energy transmitted through a wall, for example the dermis and bone, or (in other applications) a plate glass, a plastic, a concrete wall, a sheet to produce its power supply, on the other hand a high efficiency injector capable of delivering a dose of the product contained in the tank from an ultrasonic vibration injector.
- the reservoir contains a volume of about 1 ml in the form of a liquid, a gel, or a powder, capable of providing 1000 to 1 million doses.
- Audible noises generated by the actuator regardless of its use, as a measuring pen, a centrifugal injector or nebulization caused by cavitation, or as an implantable device that can be coupled to a bone wall should generally be avoided.
- the metering device operates in an ultrasonic range between 20 kHz and 20 megahertz, also to solve the problem of miniaturization to make the dosing device implantable and able to deliver small doses and finally reduce power consumption.
- the acoustic pump described in the present invention may comprise an acoustic means of transforming by a piezoelectric effect a vibratory energy transmitted to through the wall, skin or bone into electrical energy supply to the pump.
- the piezoelectric converter exploits a piezoelectric layer that can operate in receiver mode to convert vibrational energy.
- this layer deposited on the upper part of the tank opposite the ejection nozzle may also operate in emitter mode to control the level of the tank and by difference the delivered volume.
- the measurement of the dose is performed by analyzing the frequency offset of a frequency component characterizing the volume of available fluid.
- the invention in a general form, relates to a pump for injecting a fluid, comprising a reservoir or fluid, a sleeve for flowing (or extracting) the fluid from the reservoir and a device for controlling the flow, comprising a resonator arranged to apply oscillations ultrasonic flexing the sleeve, characterized in that the resonator comprises a piezoelectric transducer and a piezoelectric deformable solid which undergoes oscillation under the effect of the transducer, said deformable solid slimming towards the sleeve.
- the flow of the fluid out of the reservoir is then progressing in a channel or a thin conduit, often called capillary in the remainder of this description, which extends into the sleeve and opens out.
- the dispensing of the fluid by oscillations of the sleeve always open by a piezoelectric resonator avoids any moving part in the pump and thus allows to use it favorably in prosthesis for long periods.
- the absence of moving mechanical parts also makes the pump perfectly reliable.
- the use of bending modes of the entire sleeve by a deformable solid whose position, shape and behavior are fully known allows the quantities of fluid delivered can be determined with great precision, unlike devices where vibrations are randomly or unpredictably applied by transducers placed without principle in the device.
- the fineness of the duct of the sleeve ensures that no accidental dispensing of fluid will arrive at rest.
- the pump can be adjusted by a judicious choice of its dimensions and control parameters, notably the amplitude and the frequency of the vibrations, so as to allow very low flow rates. If necessary, a long period of use of the pump is obtained even if it is of low capacity.
- An important advantage of the invention is in the use of a solid transducer of the vibrations of the transducer to the sleeve and which tapers towards the sleeve, which makes it concentrate the vibratory energy and amplifies the deformations of the sleeve without high energy consumption.
- the piezoelectric deformable solid is a ring surrounding the sleeve and excited by a circular electrode divided into two sectors fed by the same oscillating electrical signal, but in phase opposition: this arrangement very conveniently generates the bending oscillations of the sleeve.
- the ring can be connected to the sleeve, being distinct from the tank.
- it can be connected to the sleeve; moreover, the sleeve may tap towards the free end, just as the ring may taper from a peripheral portion towards the sleeve; all these arrangements facilitate oscillations by increasing their amplitude.
- the ring may also be part of a face of the tank to which the sleeve is attached, without the operation of the invention is then very different.
- the sleeve may carry a flared nozzle at its free end to promote the delivery of the fluid by calibrated droplets.
- Delivery of the fluid can also be ensured by a flexible tube surrounding the sleeve, into which the sleeve opens, which has a free end having an opening out of the reduced section pump with respect to a main portion of the flexible tube which contains the sleeve and the resonator is arranged to apply bending oscillations also to the flexible tube: the reduced orifice of the flexible tube, possibly obtained by a heat-shrinkable effect of the flexible tube made for example of polyethylene (PE) or polytetrafluoroethylene (PTFE) or ethylene fluorinated propylene (FEP) or perfluoroalkoxy (PFA) with shrinkage coefficients of 1.7 / 1 to 1.3 / 1 when attached to the sleeve by heating to a temperature of at least 210 ° C, then plays the same role as sectional thinning of the capillary in other embodiments; the capillary can then be uniform in section without disadvantages.
- PE polyethylene
- PTFE polytetrafluor
- the sleeve can be rigidly attached to the reservoir, or it can be connected to it by a flexible connection, in the case where it is supported by the resonator.
- a particular embodiment of the invention allows a reverse operation of the pump, that is to say that a suction of ambient fluid then replaces the delivery of the fluid.
- a suction of ambient fluid then replaces the delivery of the fluid.
- the sleeve then comprises two protruding portions protruding on either side of the ring, asymmetrical and both traversed by the capillary.
- a valve system can direct the extracted fluid to a receptacle other than the main reservoir.
- control frequency will preferentially control the oscillations of one of the two portions of the sleeve, and thus the direction of flow of the fluid through the sleeve.
- the sleeve comprises two portions protruding projecting on either side of the ring, asymmetrical and both traversed by the capillary, and a median portion joining said projecting portions
- the resonator also comprises two portions which are asymmetrical and superimposed, respectively connected to said projecting portions, and between which the middle portion extends.
- the pump comprises a flexible tube surrounding each of the portions of the sleeve, which opens there respectively, each of the flexible tubes having a free end having an opening respectively out of the pump and in the reservoir, the opening having a reduced section relative to a main portion of the flexible tube which contains the portion of the sleeve, and that the resonator is arranged to apply bending oscillations also to flexible tubes.
- the flexible tubes promote the flow of the fluid in the desired direction.
- the pump may comprise a device for measuring the fluid level in the reservoir, which may comprise two sectors of the circular electrode, and a transducer located at a location of the reservoir opposite the resonator.
- the face of the reservoir to which the sleeve is attached is tapered so that the reservoir is convex, and a membrane extends into the reservoir by separating the fluid from said face. The membrane then isolates the fluid from the resonator.
- the flow can also be regulated by a free valve between a piercing of the membrane facing the sleeve and an end of the sleeve opening into the reservoir.
- the pump with an edge cap attached to the reservoir, covering the sleeve and provided with an orifice in front of the free end of the sleeve, which protects the sleeve.
- the orifice of the cover can then contain a free ball in a housing constituting the orifice, in order to regulate the delivery of the fluid to the outside.
- the hood may delimit a housing forming a reserve of an additive to the fluid, which is delivered at the same time as this one thanks to the vibrations, with a determined content of the mixture.
- the resonator is arranged to also apply axial oscillations to the sleeve. It has been found that the superposition of axial oscillations to flexural oscillations, especially when axial oscillations have a double frequency of bending oscillations, favors the flow of fluid through the capillary.
- Another way of facilitating fluid transport in the capillary is to provide the pump with a needle attached to the reservoir and extending into the capillary.
- the pump comprises a supply transducer converting electrical energy into pressure waves in an adjacent medium, a receiving transducer, also adjacent to said medium, converting the pressure waves into electrical energy. is attached to the tank, and connected to the resonator to control it.
- Figure 1 is a view of a first embodiment of the invention
- Figure 2 illustrates the electrodes
- Figure 3 illustrates a second embodiment
- Figure 4 a third mode
- Figure 5, a fourth mode
- Figure 6, a fifth mode
- Figure 8, a seventh mode
- Figure 10 a ninth mode
- Figure 13, a particular embodiment of the resonator electrodes.
- FIG. 1 illustrates the key points of the pump according to the invention.
- the pump incorporates a reservoir 1 containing a fluid coupled to a resonator 2 by a hollow sleeve 3 of flexible tube that can be conical or tapered.
- the resonator 2 is annular and surrounds the sleeve 3. It comprises a ceramic ring 70 which has on its periphery piezoelectric transducers which deform when the electrical energy is applied thereto. These transducers all include an external electrode controlled by an external power supply, an internal electrode and a layer of piezoelectric material which deforms according to the electric field applied to them by the electrodes.
- the electrodes are fixed on both sides of the piezoelectric layer, the internal electrode is also fixed to the ring 70, and the external electrode gives the outside of the resonator 2.
- the deformations of the piezoelectric layer are thus transmitted.
- the resonator 2 is distinct from the tank 1, but it is actually connected to it, for example by a cylindrical ring.
- the deformations that the transducers apply to the ring 70 of the resonator 2 are radially inward or outward according to the sign of electrical charges applied to their electrodes.
- the transducers comprise a pair of semicircular transducers 4a and 4b ( Figure 2) attached to the upper face of the ring 70, and which can be controlled by alternating current in opposite phase.
- the deformations (A) that they make to the ring 70 are therefore in opposite directions on opposite radii
- the ring 70 is deformed in the same way at the upper periphery where it is connected to the transducers 4a and 4b, but its rigidity causes these deformations to induce at the central portion 6 opposing vertical deflections (B) sectors of the ring 70, which are respectively associated with the transducers 4a and 4b, and a lateral flexion (C) of the sleeve 3, which makes it switch from one side to the other at each reversal of the current direction.
- This oscillation is an overall bending oscillation according to which all the sleeve 3 is deformed according to a proper mode or a superposition of eigen modes, generally the first eigenmode corresponding to a displacement of all the regions of the sleeve 3 in the same radial direction with increasing amplitude towards the free end, and it causes the flow of the contents of the tank 1 as will be detailed later.
- a second transducer having an external electrode 5 and an internal electrode to the ground is established under the ring 70, facing the transducers 4a to 4b, but its constitution is different since it is continuous on a circle and therefore subjects the ring 70 to radial axisymmetric deformations (D).
- the ring 70 has a thinned central region 6 performing a mechanical amplification of the vibration.
- the central region 6 of the resonator 2 - comprises a tubular section 7, in contact with the sleeve 3 tapered towards its free end of the sleeve, where there is an ejection nozzle 8, and not far from this free end.
- the physical principle of operation of the pump can be presented in two different ways.
- the first is to say that when the resonator 2 is in bending resonance with tilting of the whole of the sleeve 3, with a rocking movement (B and C) corresponding to the first natural bending mode, the sleeve 3 stretches by bending and some of the fluid is drawn towards the end. During the return movement, the sleeve 3 passes vertically, the stretch is then minimal.
- the sleeve 3 constitutes an arm of rotation about an axis located at the base of the sleeve.
- the tilting of the sleeve 3 a few millimeters in height, is comparable to a rotation.
- the rotation of the sleeve 3 reverses twice per ultrasonic period.
- the mass of liquid volume contained at the end of the sleeve 3 is thus subjected to both tangential and centrifugal acceleration, the force of which can be calculated and which, brought back to the inner surface of the capillary channel, defines the intrinsic suction pressure of the the pump.
- the reservoir 1 and the sleeve 3 are integrated, and the sleeve 3 is a conical tube inserted in force in the tubular section 7 of the resonator 2.
- the fluid located at the end of the sleeve 3 undergoes lateral and centrifugal acceleration who propels him out of the ejection nozzle 8 with an internal diameter of 0.5 mm.
- the height of the acceleration arm is 21 mm between the average level of the resonator 2 and the ejection nozzle 8 (dimension F).
- the resonator comprises a symmetrical thinning in its central region 6 which increases the amplitude of the vibration in a bending mode.
- the internal electrodes in contact with the ring 70 are grounded.
- the piezoelectric ceramic of the transducers 4a, 4b and 5 is excited half bridge. Their internal electrode is grounded and their external electrode excited by a sinusoidal or square symmetrical voltage.
- the piezoelectric ceramic may provide a second type of vibration to impart movement along the axis of the sleeve 3 and allow the ejection of a single droplet that would have formed at the end of the ejection nozzle 8 of flared shape; there can therefore be two stages, a first stage where the droplet slowly forms and grows at the end of the sleeve 3 to occupy the ejection nozzle 8 by means of the transducers 4a and 4b, and a second stage where the axisymmetric transducer 5 generates an axial movement and propels the drop; this operation is more weakly obtained with ejection nozzles 8 flared, forming a receptacle and covered with a hydrophobic coating which will be seen further samples.
- centrifugal pumping process lends itself well to the calculation of pump pressure or vacuum. It is assumed that the fluid is initially inserted to the end of the conical tube forming the sleeve 3.
- This first prototype is made with a resonator 2 of external diameter 50 mm and an internal radius of 2 mm of the ring 70, the tubular section 7 is pierced at 1.3 mm in diameter and at a height of 5.5 mm under the lower line of the ring 70 of the resonator 2 (dimension G). It produces a resonance frequency of 26 kHz (38 ps period) and a lateral vibration amplitude at the end of the sleeve 3 of 1.6 pm peak-to-peak, or about 5 pm peak-to-peak at the end of the sleeve 3 of height 21 mm.
- the centrifugal acceleration is therefore maximum when the tilting movement is vertical.
- a c 2 m / s 2 .
- the centrifugal acceleration reaches about 20% of the acceleration of gravity when the sleeve 3 passes through the vertical.
- This component is R / U times more powerful than the centrifugal component, about 8000 times more powerful.
- This acceleration is likely in certain cases to generate a sufficient pressure drop at the side walls to create a cavitation phenomenon on the side wall on the side of the tilting direction. But above all, it causes an inertial crushing of the fluid against the side walls of the sleeve 3, which drives it in the axial direction. The reduction of the fluid section towards the free end of the sleeve 3 is thus a condition favoring the progression of the fluid toward the end.
- capillary end is meant a capillary in which the fluid does not flow spontaneously by gravity effect, the capillary forces then being predominant.
- the gravitational force (or if necessary its projected value) is greater to the surface force whose amplitude and angle with the wall of the tube depend on the wettability of the fluid and the hydrophilic or hydrophobic surface treatment of the wall. So that there is spontaneous flow, it is enough that the diameter is sufficiently large so that the gravitational force ends up exceeding the surface force.
- the diameter of the capillary will generally be less than 1 mm, or even 0.5 mm. It will typically be between 0.1 and 0.5 mm.
- a valve may nevertheless be added, particularly in the case of a gas pressure difference to be provided between the inside of the tank and the outside environment, to prevent any unwanted flow (see an embodiment below) and any leakage by simple capillarity or even any effect of evaporation.
- the bending mode is sufficient to cause the pumping of the fluid.
- the axial mode may further affect the ejection of the fluid at the end of the nozzle 8 and according to its geometry. For a drip ejection, it will be possible to combine a bending mode to progressively form the drop at the end of the flared nozzle 8 in an axial mode to expel the drop after its formation.
- control electronics can be programmed to provide a predetermined number of 1-nanoliter squirts.
- an axial vibration at the double frequency of the bending mode causes elliptical vibration of the inner faces and may facilitate flow.
- FIG. 3 represents a slightly different embodiment of the invention, in which the sleeve, now referenced by 13, is integrated in the resonator 2. As before, it tapers towards the free end comprising the ejection nozzle 8 in order to to increase its flexibility under the effect of the lateral acceleration forces and thus to promote the ejection of the fluid, and its opposite end is connected to the resonator 2.
- a hose 14 connects the tank 1 to the end recessed or opening (if machined monolithically with the resonator) of the sleeve 13 and thus allows the flow of the liquid to the outside.
- the reservoir 1 and the sleeve 13 are provided with nozzles 15 and 16 on which the ends of the hose 14 are driven, and clamping rings 16 hold the assembly, which is, however, sufficiently flexible so that the lateral movements of the sleeve 13 are not not prevented.
- An alternative fixing solution to the clamping ring conciliating clamping without locking the sleeve 13 is to operate a heat-shrinkable flexible sheath with a shrinkage between 1.1 and 2.5.
- FIG. 4 illustrates an alternative embodiment, in which an outlet hose 17 is pressed around the sleeve 13 and blocked on it by a other clamping ring 18; it encloses an intermediate volume 19 that the fluid occupies after leaving the nozzle 8 and before finally leaving the pump.
- the outlet hose 19 comprises a free end 20 comprising a capillary 21 through which the fluid exits the intermediate volume 19.
- the end 20 is long enough and thin to be subjected to the same horizontal oscillating movements as the sleeve 13 under the effect of the vibrations of the resonator, with amplification due to its greater length and flexibility.
- the sleeve 13 is completed by a sleeve 22 opposite and in extension, also fixed to the resonator 2, which enters the inlet hose 14 and which also has a tapering shape towards the free end (here directed towards the tank 1), but whose length is different from that of the sleeve 13.
- the resonance frequencies of the sleeves 13 and 22 are thus different, which allows to reverse the direction of pumping according to the excitation frequency, if this frequency coincides with the resonant frequency of the sleeve 22: we can then plunge the free end 20 of the outlet hose 17 in an ambient fluid so that it is sucked to the tank 1.
- the resonator 2 comprises two superimposed rings 2a and 2b interconnected by a hollow rod 25 that two sleeves 13a and 13b extend in opposite directions, a capillary 26 single through the sleeves 13a, 13b and the tube 25.
- Each of the sleeves 13a and 13b is attached to one of the respective rings 2a and 2b.
- a hose 20a or 20b is engaged on each sleeve 13a or 13b, in the same way as the outlet hose 20 of the previous embodiment.
- the fluid 20a opens into the reservoir 2, the fluid 20b outside the pump.
- the assembly is approximately symmetrical except that the rings 2a and 2b have different thicknesses and therefore different resonant frequencies.
- one of the sleeves 13a and 13b vibrates at a much greater intensity than the other, which further imposes the direction of movement of the fluid. Since the connecting tube 25 is thinner than the sleeves 13a and 13b, the acoustic coupling it produces is weak.
- FIG. 7 Another type of improvement, illustrated as a variant of FIG. 3, appears in FIG. 7: the nozzle 8 is replaced by a nozzle 28 flaring towards the outlet, which allows a drop to grow there before be ejected by temporarily increasing the vibration amplitude and thus the acceleration.
- a hydrophobic coating advantageously covers the interior of the nozzle 28 to provide this effect.
- the device can be used as a nebulizer. It should be noted that the other embodiments also make it possible to deliver constant and known flow rates, but not necessarily in the form of drops.
- the reservoir 1 here takes the form of an elongated stylet 30 in which the resonator, now 31, is recessed. It further comprises a ring 32 which constitutes here the lower face of the stylet 30, and a sleeve 33 in one piece with the wall 32, tapering downwards and the free end, and whose inner capillary also tapers .
- a flexible printed circuit 34 is wound in the wall of the tank 30 adjacent to the resonator 31 and controls electrodes 35 in accordance with the preceding embodiments.
- the stylet 30 carries a lower cover 36 which protects the resonator 31 by covering it, the shape of which is conical and which carries at its apex a ball-shaped orifice 37 situated just below the free end of the sleeve 33. Similar to what exists for ballpoint pens, the liquid delivered by the stylet 30 plies ball 38 and exits port 37 at a uniform rate.
- the bending mode of the sleeve 33 is typically associated with a resonance frequency of 600 kH.
- the excitation of the actuator lasts between 10 ps and 100 ps at periodic intervals, the flexible printed circuit 34 comprising a control clock of the excitation pulses.
- a valve 44 occupies the center of the empty volume 40 and covers the inlet of the capillary of the sleeve 33 so as to avoid a direct flow of the fluid, which would fill the empty volume 40.
- the valve 44 is provided with a rod 45 which extends through the piercing of the membrane 39 and holds it in place.
- the bending vibrations of the sleeve 33 also tilt the valve 44, which causes periodic play with the membrane 39 and the capillary of the sleeve 33, thus allowing a fractional flow of fluid, one of which small volume therefore passes through the empty volume 40 at any moment.
- FIG. 10 differs from the previous one in that it does not include the valve 44 and the membrane 39 is completed by a curved lip 46 surrounding the capillary of the sleeve 33 and isolating the empty volume 40 from the contents of the reservoir 43.
- a needle 47 further extends in the conduit of the sleeve 33 and in the reservoir 43, to the free end of the sleeve 33 and the bottom wall 47 of the reservoir 43.
- FIG. 9 is well suited to discontinuous fluid jets (especially if it is provided, as shown here, of the flared nozzle), while the embodiment of FIG. continuous fluid consisting of fine droplets.
- the surfaces of the empty volume 40 are advantageously covered with a hydrophobic layer (more generally of a non-wetting material) to combat the residence of the fluid; the inside of the sleeve 33 as well as the side and top walls of the tank 43 are instead coated with a material promoting wetting.
- the embodiment of FIG. 11 is carried out.
- the reservoir 43 is provided with a lower cover 49 resembling the cover 36 of the embodiment of FIG. 8 and which similarly covers the sleeve 33, but which ends on an orifice 50 surrounding the free end of the sleeve 33 and which forms a game with him.
- the internal volume 51 at the cover 49 is used and forms a reserve of powder which is evacuated little by little, simultaneously with the fluid contained in the reservoir 43, under the effect of the reciprocating movements of the sleeve 33, and mainly components in sense axial.
- This embodiment is shown installed on a pipe 52, the orifice 50 being disposed through a piercing thereof, the device thus regularly providing additives to the contents of this pipe 52.
- the exciter device can be separated from the rest of the pump, which is then located behind a wall 53, for example implanted under the skin or bone of a living being.
- the device is then designed for regular delivery of drug or other product for a long time, possibly several years, low dose.
- the reservoir 54 is then rechargeable and its volume 55 unoccupied by the useful fluid can be filled with pressurized gas or gas at ambient pressure.
- a receiving transducer 56 is advantageously adjacent to the wall 53 and occupies the face of the reservoir 54 which is opposite to the sleeve 33, the resonator 57 being constituted by the lower face of the reservoir 54 as well as by electrodes connected to the receiving transducer 56.
- the transducer receiver 56 depends on a supply transducer 58 placed outside, on the other side of the wall 53, which transmits the excitation energy by longitudinal waves through the wall 53.
- the power transducer 58 communicates with the receiving transducer 56 by transmitting ultrasonic waves through the intermediate medium.
- a power supply with rechargeable batteries is a possible variant.
- the efficiency of the energy recovery is essentially due to the efficiency of the piezoelectric conversion of the materials used and is then a function of the dispersion of the acoustic energy during its propagation in an optionally heterogeneous semi-infinite medium.
- mechanical impedance matching is called when two different acoustic propagation media have to be coupled.
- the difficulty of the coupling comes from the small coupling surface, while in other cases, the difficulty is due to the very different nature of the two media, solid for one, liquid for the other. The problem that must be solved presents these two difficulties. We will describe them a little more quantitatively.
- the first notion is that of mechanical impedance. For an infinite medium, this rupture is characterized by the notion of intrinsic impedance of the media, Z i, product of the density p by the velocity V of the acoustic waves that propagate there:
- the velocity V may be that V L of the longitudinal waves or V T of the transverse waves.
- the reflection coefficient of the acoustic power R of a sinusoidal plane acoustic wave at normal incidence at the interface is:
- the transmission factor T of the acoustic intensity is:
- the media have very different impedances, the majority of an incident wave emitted from the medium 1 is reflected at the interface without reaching the medium 2.
- the damping of acoustic waves is also a factor to be taken into consideration.
- a is often given in dB / cm. This coefficient increases with the square of the frequency f and is inversely proportional to the cube of the speed of the waves.
- the velocity of the longitudinal waves being almost twice as great as the velocity of the transverse waves, the damping of transverse waves in a viscous medium is much greater than that of the longitudinal waves. Soft plastics fall into this category.
- the insertion rate reflects the effectiveness of the emitting piezoelectric transducer pressed against the skin to convert electrical energy into mechanical energy that propagates through the skin and bone to a piezoelectric antenna equipping the metering device.
- the insertion rate characterizes the ability of the assembly to maintain the resonance across the piezoelectric receiver at a high amplitude while it is charged under low electrical impedance. We are looking for the highest insertion rate.
- the output impedance Rs of the function generator is 50 Ohms.
- the PZT1 transducer converts a portion of the electrical signal into a mechanical wave that propagates to the PZT2 transducer. The latter reciprocally converts the mechanical signal into an electrical signal V L measured via an oscilloscope probe across a 50 Ohm resistive load.
- the input / output IT insertion rate is
- the input / output insertion rate can be close to the conversion rate in energy K 2 33 of a piezoelectric transducer, ie 46% and 49% for the PZ26 and PZ27 materials respectively from Ferroperm.
- the acoustic wave sees its wave front deform and the input / output insertion rate degrade. This is all the more true as the working frequency is higher.
- the wavelength of acoustic waves in the body is of the order of 1.5 mm.
- the thickness of tissue / bone to be crossed must be quite short and the acoustic antenna extended enough laterally for a sufficient proportion of the emitted power to be recovered.
- the working frequency and the shape of the receiving antenna must be such as to prevent inadvertent coupling with other sources of acoustic waves present in
- the acoustic wave source to activate the dispenser should be emitted at a key rate (the key that can be changed by the patient or only by a physician) for the dosing device to deliver the dose.
- the excitation device 58 is a piezoelectric power supply transducer emitting a pressure wave in the wall 53, and taken up by the control transducer 56 and reconverted into electrical energy supplied to the electrodes of the resonator 57.
- an astable oscillator with a frequency of 19 kHz is used to create a high voltage of 90 V by periodically opening and closing a transistor T1 which charges an inductance inductance of value lmH and of series resistance 60 Ohms.
- the rise in current load of the choke lasts at least 40 ps (three times the time constant).
- This high voltage is then used to excite the actuating transducer 56 at a frequency of 600 kHz by means of the NMOS and PMOS transistors which switch in phase opposition, the one (Source) the PMOS serving to carry the voltage of the transducer actuator at 90V while the other the NMOS (Sink) used to empty the electric charges.
- the two capacitors in series total a capacity of 10 to 100 times the value of the static capacity of one actuator is about 100 nF.
- the burst at 600 kHz comprises N periods, N being between 1 and 60. The burst is re-transmitted at a rate of 1 kHz to allow the maintenance of high voltage.
- the cyclic excitation ratio of the actuator does not exceed 10%. In the case of implantable devices, lower voltages will be exploited.
- the power transducer is placed against the wall 57.
- a pressure wave is generated in the medium that propagates to the receiving transducer 56.
- the transmission is effective if the two transducers have the same resonance frequency and if the excitation of the pressure wave is performed at this frequency, and finally if the two transducers are parallel. Several tens of milliwatts are then available at the terminals of the receiver transducer 56.
- the excitation of the supply transducer 58 can be carried out intermittently.
- the all or nothing modulation of the signal transmitted according to a particular frame can be used to code a reset key of the decoded metering device via a digital analog conversion AO of the microcontroller.
- This one has a digital analog conversion input (or via a capture / compare mode).
- the reception in the near field is via a receiver transducer 56 identical to the supply transducer 58 resonating at the same resonance frequency (1 to 4 MHz).
- One aspect is full-wave rectification of the received signal and storage of energy in a capacitor. While the power transducer 58 is operating, the output voltage across the capacitor at the output of the Schottky diode rectifier bridge slowly increases until the voltage reaches the start threshold of the microcontroller.
- the capacity of the capacitor at the output of the rectifier bridge 59 is sufficient to allow a single excitation of the transducer of the resonator 57 and an economic mode operation of the microcontroller for counting the elapsed time since the last dosing.
- the transducer of the resonator 57 can not be reactivated before a security delay.
- To restart a dosing operation it is necessary on the one hand that the safety time has elapsed, on the other hand activate the power supply transducer 58 against the electrical wall 53.
- the power of the microcontroller is made from the signal rectified piezoelectric.
- the capture / compare mode of the microcontroller allows it to possibly read the encryption key and change the safety time or reactivate the dosage.
- the microcontroller controls the opening and closing of 2 transistors using Source and Sink signals.
- the Pmos transistor controls the high voltage of the transducer of the resonator 57 while the other signal Sink controls the grounding of the transducer of the resonator 57 and the emptying of the electrical charges.
- These charging and discharging operations are performed at a frequency of 600 kHz corresponding to the radial resonance of the resonator transducer 57.
- the latter can also be excited in a bending mode by cutting the electrode 4 into two half-rings.
- the electrode at tank contact 54 is uniform and is not operated.
- the transducer of the resonator 57 has a much smaller thickness, typically 0.2 mm, than the power transducer 58, because it is simply a radial mode, but especially it is desired to impose an intense electric field and vibrate the tank bottom 54 according to a bending mode.
- the bending mode tilts the sleeve 33.
- This tilting causes a movement of the fluid (liquid or gel or powder) to the outside of the dispenser.
- the fluid is thus expelled by tilting and the bending movement of the end of the sleeve 33.
- the fact that the end of the sleeve 33 is free is critical because it is because the end of the sleeve 33 is free relative at its base that the fluid is sucked into the capillary and expelled outwards.
- a protective piece of the end of the measuring tube is provided.
- the bending mode of the tube is typically associated with a resonance frequency of 600 kHz.
- the excitation of the actuator lasts between 10 ps and 100 ps. It is performed when the voltage across the input capacitor rectifier is sufficient to wake up the microcontroller. The latter then starts its real time clock via a quartz at 32768 Hz.
- the microcontroller has a frequency generator (FLL loop) him to produce the 600 kHz excitation signal of the resonator transducer 57. Once the excitation of the transducer of the resonator 57 is performed, the microcontroller goes into low power mode, the only obligation being the measurement of the time elapsed since the activation of the resonator transducer 57.
- the microcontroller records in a non-volatile memory, for example its flash memory, the time elapsed since the last excitation. This allows the microcontroller with each new issue to check the value of the register and verify that the security time has been respected.
- the transducers of the resonators can be four in number on a circle without escaping the teaching of the invention.
- the transducers 60a and 60b opposite and extending over important sectors of circle, close to a semicircle, have the main role of excitation of the resonator and the sleeve, or in lateral flexion mode, by excitation in opposition phase, or in speaker operation mode (uniform bending leading to a lateral displacement of the sleeve) by a phase excitation, as mentioned.
- Two similar transducers 60c and 60d, located between the main transducers 60a and 60b, of smaller angular expansion and opposed to each other, are here used in conjunction with a receiving transducer 61 opposite the resonator and therefore situated in the solid bottom wall.
- the auxiliary transducers 60c and 60d emit a wave towards this receiving transducer 61, which remains permanently in receiving mode and which measures a resonance frequency variation, which is characteristic of the quantity of liquid present. in the tank.
- a characteristic height of the reservoir being of the order of 5 to 10 mm
- the ⁇ / 2 resonance frequency in the water will be of the order of 150 to 300 kH.
- the variation of the resonance frequency will give the indication of the height of the liquid remaining in the reservoir, that is to say of the volume expelled.
- the resolution on the measurement of the delivered volume will be of the order of 100 nl.
- Even finer measurements can be made by measuring the amplitude of the signal received for a few frequencies located on either side of the resonance peak, and finding the position of the peak vertex by quadratic interpolation.
- This operation can be performed intermittently, for example at a rate of 1000 shots at programmable intervals of one second to several hours, each shot consisting of a burst of thirty periods at the maximum allowed voltage at the resonant frequency of bending of the tank bottom (vibration out of plane).
- the resonance frequency of the actuator is typically 600 kHz, a period of 1.7 ps.
- the excitation burst is of the order of thirty periods, so as to reach the maximum vibration amplitude of the tank bottom (about 50 ps), which sets the duty cycle at 5% for a rate 1000 shots per second. The remaining 95% of time is devoted to the preparation of the high voltage excitation voltage.
- the control electronics are wired to a circuit board with a Kapton-type flexible plastic substrate.
- the flexible PCB is made with electronic components for surface mounting the height of which does not exceed 2 mm.
- the PCB wraps around the tank. For a tank with an outside diameter of 10 mm and a height of 10 mm, the flexible PCB can occupy an area of about 40 mm x 10 mm.
- This surface is sufficient to house a rectifier bridge, a regulator, a microcontroller with digital analog conversion to measure the amplitude of the signal received by the upper transducer for controlling the volume of the tank, a high voltage oscillator generator astable and diode bridge as well as switching transistors for excitation of the actuator transducer.
- the excitation signal could be symmetrical (this is not the case here because there is only one high voltage, for example, 90 volts empty: the firing therefore oscillates in a burst comprising N pulses between 0 and +90 volts re-emitted at a rate of 1 kHz, this frequency may be highly noticeable inside the ear) by providing a second high voltage symmetrical to the first and an actuation of the resonator transducer 57 between + 90V and -90V (empty) and + 30V to -30V (charged by the transducer).
- the burst has a sufficient number of pulses (N> 10)
- the audible noise of the intermittent excitation burst can be further reduced by the application of an apodization window of the burst (weighting of
- the transducer of the resonator 57 must be able to be excited with the highest possible electric field, ie of the order of 400 to
- the transducer can easily bend and deform in a mode allowing the transfer of the fluid at the outlet of the metering device
- the excitation voltage may remain low, of the order of a few volts for implantable applications and from 10 V to 30 V for non-implanted applications.
- the receiving transducer 56 will transfer the energy to the resonator 57 by a silicone coated wire. No magnets are used, with the advantage of not disturbing magnetic resonance imaging for clinical applications.
- the excitation of the electrodes for the loudspeaker mode, by an axial movement of the ring of the resonator, may allow the measuring device to also serve as a hearing aid, by reconstructing an analog signal at the the inside of the ear by a modulation of the beats of the ring of the resonator.
- the delivered volume can be determined in open loop and thus modified according to the needs of the moment, so controlled and perfectly reliable.
- the temperature rise produced by the pump of the invention is very small.
- the pump can be implanted using a cochlear implant technique in the middle ear; the use of the outlet hose of FIG.
- the main reservoir may be very flat, of a few millimeters thick for a diameter of the order of a centimeter, or on the contrary the device may be placed in a remote element of the reservoir, which is connected to it for example by a cannula which can be thin or elongated (for example 5 mm in diameter or more and a length of the order of a centimeter or more).
- the use of ultrasound makes the invention silent.
- the extraction is facilitated if the bending motion at the resonator resonator resonance frequency is superimposed off-plane movement of the resonator (in speaker mode) at the double frequency 2fo, which generates a peristaltic movement of the inner face of the sleeve dosing.
- the acceleration required for the flow and dosing of the product is several thousand “g”: the accelerations normally encountered, of a few "g" at the most, can in no case induce leaks.
- the device devoid of moving mechanical parts and materials that can degrade quickly under mechanical stress, such as polymers, ages well.
- DDS category "Drug Delivery System” DDS category "Drug Delivery System”
- inking pens or deodorization or industrial dosing devices from 1 to 2 compounds or reagents on a particular flow.
Landscapes
- Engineering & Computer Science (AREA)
- General Engineering & Computer Science (AREA)
- Mechanical Engineering (AREA)
- Health & Medical Sciences (AREA)
- Biomedical Technology (AREA)
- Anesthesiology (AREA)
- Vascular Medicine (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
Abstract
Description
Claims
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
FR1158458A FR2980535B1 (fr) | 2011-09-22 | 2011-09-22 | Pompe d'injection d'un fluide, et notamment micropompe utilisable pour delivrer une dose determinee |
PCT/EP2012/068693 WO2013041700A1 (fr) | 2011-09-22 | 2012-09-21 | Pompe d'injection d'un fluide, et notamment micropompe utilisable pour delivrer une dose determinee |
Publications (1)
Publication Number | Publication Date |
---|---|
EP2758664A1 true EP2758664A1 (fr) | 2014-07-30 |
Family
ID=46889054
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP12762286.8A Withdrawn EP2758664A1 (fr) | 2011-09-22 | 2012-09-21 | Pompe d'injection d'un fluide, et notamment micropompe utilisable pour delivrer une dose determinee |
Country Status (4)
Country | Link |
---|---|
US (1) | US20140377091A1 (fr) |
EP (1) | EP2758664A1 (fr) |
FR (1) | FR2980535B1 (fr) |
WO (1) | WO2013041700A1 (fr) |
Families Citing this family (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7553295B2 (en) | 2002-06-17 | 2009-06-30 | Iradimed Corporation | Liquid infusion apparatus |
US8105282B2 (en) | 2007-07-13 | 2012-01-31 | Iradimed Corporation | System and method for communication with an infusion device |
DE102013108948B4 (de) * | 2013-08-19 | 2018-02-01 | Uwe Nakoinz | Vorrichtung zur Beförderung von Flüssigkeiten mit Hilfe einer Piezo-Antriebsvorrichtung |
FR3022024B1 (fr) * | 2014-06-10 | 2016-07-15 | Commissariat Energie Atomique | Capteur de temperature, unite electronique interagissant avec un tel capteur, procede et programme d'ordinateur associes |
WO2018112786A1 (fr) * | 2016-12-21 | 2018-06-28 | 无锡源清天木生物科技有限公司 | Dispositif de commande d'écoulement de liquide et procédé de commande de micro-écoulement pour une commande de micro-écoulement |
CN106671371A (zh) * | 2016-12-22 | 2017-05-17 | 苏州市职业大学 | 一种柱塞式精密注射装置 |
US11268506B2 (en) * | 2017-12-22 | 2022-03-08 | Iradimed Corporation | Fluid pumps for use in MRI environment |
CN110307351A (zh) * | 2019-07-10 | 2019-10-08 | 广东工业大学 | 一种压电陶瓷限流阀 |
NL2026780B1 (en) | 2020-10-27 | 2022-06-21 | Univ Delft Tech | Precise fluid manipulation in the femtolitre range |
Family Cites Families (17)
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US2512743A (en) * | 1946-04-01 | 1950-06-27 | Rca Corp | Jet sprayer actuated by supersonic waves |
US3173612A (en) * | 1963-02-12 | 1965-03-16 | Macrosonics Corp | Method of producing aerosols, sprays and dispersions and device therefor |
US3271622A (en) * | 1963-07-05 | 1966-09-06 | Little Inc A | Piezoelectric ballast apparatus |
US3452360A (en) * | 1967-07-28 | 1969-06-24 | Gen Precision Systems Inc | High-speed stylographic apparatus and system |
US4308546A (en) * | 1978-03-15 | 1981-12-29 | Gould Inc. | Ink jet tip assembly |
EP0344008B1 (fr) * | 1988-05-26 | 1994-08-17 | Kohji Toda | Organe d'actionnement de type vibrant |
FR2650634B1 (fr) | 1989-08-07 | 1994-04-15 | Debiopharm | Micropompe perfectionnee |
EP0584775B1 (fr) * | 1992-08-25 | 1997-12-17 | Canon Kabushiki Kaisha | Procédé de fabrication d'un dispositif piézoélectrique laminé et sa méthode de polarisation et moteur actionné par des ondes vibratoires |
US6749406B2 (en) | 2001-04-09 | 2004-06-15 | George Keilman | Ultrasonic pump with non-planar transducer for generating focused longitudinal waves and pumping methods |
US6958040B2 (en) * | 2001-12-28 | 2005-10-25 | Ekos Corporation | Multi-resonant ultrasonic catheter |
DE102005025640A1 (de) * | 2005-06-03 | 2006-12-07 | Scienion Ag | Mikrodispenser und zugehöriges Betriebsverfahren |
US8191732B2 (en) * | 2006-01-23 | 2012-06-05 | Kimberly-Clark Worldwide, Inc. | Ultrasonic waveguide pump and method of pumping liquid |
US8267905B2 (en) | 2006-05-01 | 2012-09-18 | Neurosystec Corporation | Apparatus and method for delivery of therapeutic and other types of agents |
US7748664B2 (en) * | 2006-08-23 | 2010-07-06 | Lockheed Martin Corporation | High performance synthetic valve/pulsator |
EP2068809A1 (fr) * | 2006-09-29 | 2009-06-17 | Eilaz Babaev | Dispositif ultrasonique d'administration de liquides et procédés d'utilisation de l'énergie ultrasonique pour administrer des liquides dans le corps |
US9024507B2 (en) * | 2008-07-10 | 2015-05-05 | Cornell University | Ultrasound wave generating apparatus |
US10537725B2 (en) * | 2010-03-05 | 2020-01-21 | Cornell University | Ultrasound-assisted convection enhanced delivery of compounds in vivo with a transducer cannula assembly |
-
2011
- 2011-09-22 FR FR1158458A patent/FR2980535B1/fr active Active
-
2012
- 2012-09-21 EP EP12762286.8A patent/EP2758664A1/fr not_active Withdrawn
- 2012-09-21 WO PCT/EP2012/068693 patent/WO2013041700A1/fr active Application Filing
- 2012-09-21 US US14/345,510 patent/US20140377091A1/en not_active Abandoned
Non-Patent Citations (2)
Title |
---|
None * |
See also references of WO2013041700A1 * |
Also Published As
Publication number | Publication date |
---|---|
WO2013041700A1 (fr) | 2013-03-28 |
FR2980535B1 (fr) | 2018-03-09 |
US20140377091A1 (en) | 2014-12-25 |
FR2980535A1 (fr) | 2013-03-29 |
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