Peristaltic pump driven by piezoelectric transducers

Abstract

Peristaltic pump, intended to pump a liquid along a capillary (2), the pumping resulting from a stress exerted on the capillary, successively along a pumping direction, the pump comprising: K annular piezoelectric transducers (11k), extending around a central axis (Δ), K resonators (10k), formed of a deformable solid material, each resonator being connected to a piezoelectric transducer, and extending around the central axis, thinning towards the central axis, each resonator being configured to deform under the effect of a polarization of the piezoelectric transducer to which it is connected; a control unit (20), configured to polarize each piezoelectric transducer, the pump being characterized in that: each resonator is connected to a sleeve (3k), extending around the central axis; each resonator is arranged so that the sleeves of each resonator are aligned along a central axis.

Description

Title of the invention: Peristaltic pump operated by piezoelectric transducers Technical field

[0001] The technical field of the invention is a peristaltic pump configured to be actuated by a piezoelectric transducer. PREVIOUS ART

[0002] Most pumps use moving parts, which can lead to reliability, wear, and limited compactness issues. In the healthcare field, peristaltic pumps are commonly used. However, repeated crushing of a hose, which causes the liquid to move, can lead to premature wear of the hose.

[0003] Patent application WO2013 / 41700 describes a pump, which may be implantable, non-peristaltic, with piezoelectric actuation. A sleeve, arranged at the center of a resonator, undergoes bending, under the effect of a rotating deformation of the resonator, generated by piezoelectric transducers activated according to an ultrasonic frequency. The bending of the sleeve generates a pumping effect, which causes the expulsion of the fluid. A reduction in the cross-section of the resonator, in the vicinity of the sleeve or along the latter, makes it possible to amplify the vibrations propagating to the sleeve. Such a pump is effective. However, it has been found that the sleeve undergoes repeated bending, which can lead to wear. Furthermore, the pump is intended to be coupled to a fluid circuit. Flow control depends on the vibration amplitude of the sleeve which must be controlled by the mechanical load of the fluid circuit, which is not easy.

[0004] In particular, it is sought that the pumping principle, the frequency and the amplitude of the ultrasonic pumping vibration are less dependent on the mechanical coupling of the pump with the fluid circuit.

[0005] Another objective is to design a peristaltic pump, allowing pumping to be carried out at a controlled flow rate, with optimized energy expenditure, and which can be particularly compact. Statement of the invention

[0006] An object of the invention is a peristaltic pump, intended to pump a liquid along a capillary, with a stress exerted on the capillary, successively along a pumping direction, the pump comprising: - K annular piezoelectric transducers, extending around a central axis, each piezoelectric transducer and configured to be polarized by a polarization electrode, K being an integer greater than or equal to 2 - K resonators, formed from a deformable solid material, each resonator being connected to a piezoelectric transducer, and extending around the central axis, tapering towards the central axis, each resonator being configured to deform under the effect of a polarization of the piezoelectric transducer to which it is connected; - a control unit, configured to polarize each polarization electrode according to a polarization voltage, modulated according to a modulation frequency;

[0007] the pump being characterized in that: - each resonator is connected to a sleeve, extending around the central axis; - each resonator is arranged so that the sleeves of each resonator are aligned along a central axis; - the control unit is configured to successively polarize each resonator, according to their respective ranks, so that under the effect of the polarization, a successive deformation of each resonator occurs, the deformation propagating to the sleeve, and causing a successive deformation of the capillary (2) arranged between the sleeves, around the central axis.

[0008] The constraint may in particular be a compression and / or a displacement along the central axis.

[0009] The modulation frequency may in particular be greater than 20 kHz.

[0010] According to one possibility: - each resonator comprises a peripheral portion, delimited by two flat faces, and a central portion, extending between the peripheral portion and the sleeve, the central portion tapering towards the sleeve; - each piezoelectric transducer extends along a flat face.

[0011] According to one possibility, the planar face along which each peripheral transducer extends is delimited by a shoulder, the piezoelectric transducer being inserted by force against the shoulder, so that the shoulder bypasses the piezoelectric transducer.

[0012] According to one possibility, each resonator is coupled to at least one annular piezoelectric transducer, the annular piezoelectric transducer extending around the resonator, so as to generate a radial compression of the resonator, in the direction of the central axis.

[0013] Each piezoelectric transducer can be force-fitted around the resonator to which it is connected.

[0014] According to one possibility, each resonator is coupled to two piezo-transducers

[0015]

[0016]

[0017]

[0018]

[0019] annular electric transducers, extending around the resonator, and offset in a direction parallel to the central axis, the central unit being configured to power the piezoelectric transducers so as to cause a displacement of the sleeve, along the central axis and / or a compression of the sleeve perpendicular to the central axis. According to one possibility, each piezoelectric transducer having a dipole moment: - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in the same direction, in which case the control unit is configured to supply said piezoelectric transducers in phase; - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in two opposite directions, in which case the control unit is configured to supply said piezoelectric transducers in phase opposition; - so as to generate radial compression of the sleeve predominant over a displacement of the sleeve along the central axis. According to one possibility, each piezoelectric transducer having a dipole moment: - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in the same direction, in which case the control unit is configured to supply said piezoelectric transducers in phase opposition; - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in two opposite directions, in which case the control unit is configured to supply said piezoelectric transducers in phase; - so as to cause a displacement of the sleeve, along the central axis, predominating over a compression of the sleeve. According to one possibility, the control unit is configured to power said piezoelectric transducers according to a predetermined phase shift, between 0° and 180°, so as to obtain a predetermined ratio between the displacement of the sleeve along the central axis on the compression of the sleeve. The pump may include the capillary, for example the capillary being force-fitted between each sleeve. The capillary may be rigid The invention will be better understood by reading the description of the exemplary embodiments presented in the remainder of the description, in conjunction with the figures listed below. FIGURES

[0020] Figures 1A and 1B show one embodiment of a peristaltic pump.

[0021] [Fig. 2] represents a variant of the configuration described in connection with the figures IA and IB

[0022] [Fig.3A] shows another embodiment of a peristaltic pump.

[0023] [Fig.3B] shows an example of an annular piezoelectric transducer.

[0024] [Fig.4] shows another embodiment of a peristaltic pump. PRESENTATION OF SPECIAL METHODS OF IMPLEMENTATION

[0025] [Fig. 1 A] describes a peristaltic pump, in which a pumping effect is obtained by applying progressive compression along a capillary 2. The capillary 2 is coaxial with a central axis

[0026] The pump comprises K resonators 10k, k being a rank assigned to each resonator. The minimum number of resonators is 2, and the optimal number of resonators is between 3 and 5. In the example shown, K = 4. There are thus 4 identical resonators 10i, 102, 103, 104, aligned along the central axis. Each resonator extends in an annular shape, between a peripheral part, comprising flat portions, of constant thickness, and a part thinning towards the central axis. Each resonator thins, preferably progressively, down to a sleeve 3k, cylindrical, and extending around the central axis. The progressive thinning makes it possible to increase the deformation forces transferred to the sleeve.

[0027] The capillary 2 is arranged along the central axis, between each sleeve. Preferably, the capillary 2 is rigid so that it can be force-fitted into the sleeves. Force-fitting minimizes losses at the interfaces in the form of parasitic reflection of mechanical energy or dissipation by friction. In addition, force-fitting does not require a clamping means. The capillary may be formed from the same material as the resonator.

[0028] Each resonator has a 15k shoulder, allowing the transducer to which it is coupled to be gripped, so as to exert a prestress. Thus, each shoulder bypasses the piezoelectric transducer that it grips. Each piezoelectric transducer can thus be held without glue, by simple mechanical stress. This makes it possible to avoid degradation, over time, of a bond, under the effect of aging.

[0029] Each 10k resonator is coupled to an annular piezoelectric transducer 1 lk. [Fig.lB] shows a detail of the mechanical coupling of an annular piezoelectric transducer 1 lk, connected to a 10k resonator. The piezoelectric transducer 1 lk comprises a layer of a piezoelectric material 13k extending between at least one electrode 12k and a counter electrode 14k on the other hand. When the resonator 10k is made of an electrically conductive material, the electrode 12k preferably has a slightly smaller external diameter, for example from 0.2mm to 0.5mm, than the counter electrode 14k of to avoid an electrical short circuit between the 12k and 14k electrodes via the 15k shoulder. The 10k resonator is symmetrical about the central axis A. The 10k resonator is annular, around the central axis A. It thins towards the latter. Thus, its thickness, defined parallel to the central axis A, decreases as a function of the distance from the central axis A. The thinning makes it possible to increase the amplitude of the vibrations propagating in the resonator, towards the sleeve.

[0030] In this configuration, the piezoelectric transducers have a small thickness, typically between 0.05 mm and 5 mm, preferably 0.5 mm for a radius} of 25 mm and 0.2 mm for a radius r of less than 10 mm, which maximizes the electric field, the latter being able to be of the order of 300 V / mm. This makes it possible to increase the mechanical stress, the latter being directly proportional to the electric field.

[0031] Each layer of 13k piezoelectric material may be formed from a PZT (Lead Zirconate Titanate) type material, in particular the references PZ26, PZ27, PZ46 and PZ29 from Ferroperm. Preferably, the coefficients d33 and d31, which account for the coefficient of the deformation observed for an applied electric field (also perceived as a density of charges collected for an applied stress), are respectively: - at least 200 pC / N and preferably above 570 pC / N for the coefficient d33 quantifying the response of the piezoelectric material in a direction parallel to the direction of the applied electric field. - and at least 50 pC / N and preferably of the order of -240 pC / N. for d31, which quantifies the response of the piezoelectric material in a direction perpendicular to the direction of the applied electric field.

[0032] The external radius R of each 10k resonator, defined around the central axis A, can extend up to 50 mm, or more. The flat portion of each resonator extends beyond a first radius less than the external radius R previously defined. Below the first radius RB each resonator has a portion thinning in the direction of the central axis A. The first radius Ri is for example equal to 50% of the external radius R of the resonator.

[0033] Each resonator may extend with a thickness preferably less than 5 mm, for example 1 or 2 mm. The thickness is defined parallel to the longitudinal axis.

[0034] The 10k resonator extends to a first cylindrical sleeve 3k, coaxial with the central axis A. The diameter D of the sleeve 3k is for example between approximately 0.2 mm and 2 mm and preferably close to 1 mm. The sleeve 3k is preferably formed by an extension of the 10k resonator, the resonator and the sleeve forming a monolithic part. The radius of the sleeve forms an internal radius of the first 10k resonator. The height of each 3k sleeve is preferably less than one wavelength of the waves propagating in the sleeve. The height of each 3k sleeve is preferably equal to half a wavelength. The wavelength depends on the thickness of the sleeve and the resonant frequency. In practice, the height of the sleeve is less than 1 mm and preferably less than or equal to the thickness of the resonator in the portion applied against the piezoelectric transducer.

[0035] This allows the sleeve of each resonator to be as close as possible to the sleeve of another resonator, without being in direct contact. The spacing between two adjacent sleeves may be at least 0.05 mm.

[0036] Each resonator is formed from a deformable solid material, which may be of the metal type (titanium, stainless steel, aluminum or aluminum alloy, brass, or other copper-based alloy, or nickel-based alloy), inorganic material (glass), organic material (PEEK), alumina.

[0037] The pump comprises a control unit 20, connected to each first electrode 12k so as to apply a frequency-modulated bias voltage to them. The modulation frequency depends on the size and material forming each resonator. The frequency is the same for each piezoelectric transducer. When the radius of each resonator is 25 mm, the modulation frequency may be approximately 25 kHz. When the radius of each resonator is 12.5 mm, the modulation frequency may be approximately 50 kHz. When the radius of each resonator is 6.5 mm, the modulation frequency may be approximately 100 kHz. In all cases, the modulation frequency is preferably ultrasonic, so as to avoid generation of an audible sound.

[0038] Each 14k counter-electrode is connected to a fixed potential, which may be common to all the counter-electrodes (for example a ground), or independent of the potential to which another electrode is connected, each independent potential being for example a floating ground.

[0039] Each 10k resonator is configured to be deformed by a compression wave acting on each sleeve, so as to radially compress the capillary. Under the effect of compression, the internal diameter of each sleeve oscillates according to a radial compression resonance frequency. According to one possibility, each sleeve can move parallel to the axis of the capillary according to a radial bending resonance frequency.

[0040] More precisely, the dimensions of the resonator being finite, a surface element located on the internal wall delimiting each sleeve oscillates by describing an ellipse at each resonance period. The major axis sz of the ellipse is parallel to the central axis A according to a radial resonance frequency of bending. There is therefore a slight effect of bearing printed on the capillary. The 10k resonator can vibrate at its fundamental frequency or at a harmonic frequency. In the latter case, the ratio between the major axis sz and the minor axis sr of the traversed ellipse becomes closer to 1. The motion becomes more circular for a higher harmonic frequency.

[0041] The resonators can be separated from each other by spacers 4. This helps to stiffen the stack.

[0042] The thickness of the stack can be between 5 mm and 10 mm.

[0043]

[0044]

[0045] The transducers are phase-shifted along the longitudinal axis A, so that the com pressure moves along the central axis. The time shift is 7, where T corresponds to the period during which each transducer was actuated. The resonance frequency is estimated to be at most 150 kHz for a fundamental frequency. [Fig. 2] illustrates a variant of the embodiment described in connection with figures 1A and 1B, in which the stack is housed in a housing. Each end of the capillary is conical, which facilitates connection with a flexible capillary 5, for example made of silicone. In this example, the assembly formed by the resonators is held on a base 6a onto which a cover 6b is clipped. Figures 3A and 3B illustrate an embodiment close to the embodiment of Figures 1A and 1B, in which each piezoelectric transducer is a ring arranged around the resonator to which it is coupled. Such a configuration is conducive to the generation of symmetrical Lamb waves propagating radially, converging towards the central axis. This makes it possible to concentrate the compression forces at the sleeve. In this case, the ellipse traveled by the displacement of a surface element of the sleeve at the interface with the capillary has its major axis oriented perpendicular to the central axis A of the capillary. The transducers are phase-shifted (or activated according to a time shift) along the central axis A, so that the compression associated with the major axis of the ellipse moves along the central axis. The phase shift or time shift is T, where T corresponds to the period during which each transducer was activated.

[0046] The use of piezoelectric transducers arranged at the periphery of resonators makes it possible to increase the frequency, the latter being able to resonate in thickness resonance at a high frequency, in practice beyond the megahertz or a lower frequency if a radial compression resonance of the thinned disk is used. This makes it possible to use a thinner capillary close to a tenth to a few tenths of a millimeter. Such a configuration is suitable for the delivery of low doses of active ingredient, or for an implanted pump or for dispensing small volumes of fluids such as catalysts or expensive products or for contributions slow and well-controlled movements of powders or various products (gas, lubricant, etc.) necessary for a particular production or maintenance.

[0047] In [Fig.3B], an annular piezoelectric transducer is shown: the 12k electrode and the 14k counter electrode are annular, as is the 13k piezoelectric layer. In this example, the thickness of the 13k piezoelectric layer is 1 mm, the diameter of the 12k electrode being, for example, 22 mm. In order to ensure electrical insulation between the 12k electrode and the 10k resonator to which it is attached, the 13k piezoelectric layer may be beveled (bevel not shown) to a depth of at least 0.1 mm on the edges of the 12k external electrode. In the radial direction, the width of the piezoelectric layer may be between 0.5 mm and 1 mm. The resonance frequency for a thickness of 1 mm is approximately 2 MHz.

[0048]

[0049] [Fig.4] shows a configuration close to that described in connection with Figures 3A and 3B. In this configuration, each resonator is coupled to two annular piezoelectric transducers 1 lb 21 b activated in phase opposition, and arranged around the resonator. Such a configuration is conducive to the generation of antisymmetric Lamb waves propagating radially, converging in the thinned region causing shearing of the capillary 2, the shear propagating in a predetermined direction. In this case, the ellipse traveled by a surface element at the interface between the sleeve and the capillary has a major axis sz parallel to the central axis D of the capillary. As in the previous embodiment, the transducers coupled to two adjacent resonators are phase-shifted along the longitudinal axis A, so as to propagate the shear stress from near to far along the capillary. The time phase shift (or offset) is 2% T, where T corresponds to the period during K of which each transducer was actuated. During the same phase, the first transducer 1 lk of a 10k resonator is activated, so as to induce buckling in one direction of the resonator in its central region, while the second transducer 21k of a 10k resonator is activated, so as to induce buckling in the same direction of the resonator and must therefore be phase shifted by ji, at the central axis. This is obtained if the external electrodes 12k of the transducers 1 lk and 21k are subjected to the same electrical excitation voltage and if the electric dipole moments of the piezoelectric materials 1 lk and 23k are in opposite directions as indicated by the arrows crossing the transducers which are reported in [Fig.4]. This gives a pumping by peristaltic shear effect, due to the progressiveness of the shear of the capillary 2, which causes a displacement of the fluid by viscosity and incompressibility of the fluid along the central axis. The pumping efficiency is reinforced by a displacement component sr in the plane of each resonator, corresponding to the minor axis of the displacement ellipse and inducing a compression of the capillary tube. The symmetric SO and antisymmetric AO acoustic modes initiated at the periphery of the resonators in Figures 3A and 4 both include compression displacement components sr and shear sz of the capillary corresponding to the major and minor axes of the ellipse traveled by a displacement vector, but with a dominant compression in sr for the symmetric mode and shear in sz for the antisymmetric mode. These two vibration modes are considered peristaltic.

[0050] The configuration shown in [Fig.4] also makes it possible to form symmetrical acoustic modes SO, as shown diagrammatically in [Fig.3A], when the external electrodes 12k of the two piezoelectric transducers 1 lk, 21k connected to each resonator 10k are in phase opposition and if the electric dipole moments of the piezoelectric transducers 1 lk and 21k are in opposite directions as shown in [Fig.4],

[0051] When the dipole moments of the transducers 1 lk and 21k are oriented in the same direction, and the excitation voltages are in phase opposition, an antisymmetric vibration mode A0 is obtained as previously described. When the excitation voltages are in phase, a symmetric vibration mode S0 is obtained.

[0052] A symmetrical vibration mode has the effect of compressing the capillary and producing a displacement of the capillary / sleeve interface traveling in an ellipse with a major axis orthogonal to the D axis. This vibration is transmitted in the wall of the capillary in the form of a bending wave with axial symmetry relative to the D axis.

[0053] An antisymmetric vibration mode has the effect of producing a displacement of the capillary / sleeve interface whose major axis of the ellipse is parallel to the axis D, which results in shearing of the capillary while respecting the axial symmetry with respect to the axis A.

[0054] It follows that if the electrical phase shift between the two transducers 1 lk and 21k is varied from 0 to 180°, there is a continuous transition from a predominant generation of a symmetrical deformation mode to a predominant generation of an antisymmetrical mode relative to the median plane of the 10k resonator. The two symmetrical and antisymmetrical vibration modes are created simultaneously but in different proportions depending on the phase shift and with distinct phase velocities, greater for the symmetrical mode than for the antisymmetrical mode. Knowing that these vibration modes can coexist simultaneously and elastically in the resonator, it is sufficient to impose a particular electrical excitation phase shift of between 0 and 180°C to obtain a vibration of the wall of the capillary so that each surface element of the capillary moves along an ellipse, the major axis of which is likely to vary from an orientation perpendicular to the D axis to an orientation parallel to the D axis depending on the phase shift that will have been chosen between the two transducers 1 lk and 21k.

[0055] Whatever the configurations, the peak / peak bias voltage can vary for example from a few volts to several hundred volts, the voltage playing on the amplitude of the out-of-plane deformation component of the resonator. The amplitude of this deformation component plays on the volume of fluid at the internal interface of the capillary undergoing the elliptical rolling effect which causes it to be driven and therefore on the pumping pressure.

Claims

Claims

1. Peristaltic pump, intended to pump a liquid along a capillary (2), the pumping resulting from a stress exerted on the capillary, successively along a pumping direction, the pump comprising: - K annular piezoelectric transducers (1 lk), extending around a central axis (A), each piezoelectric transducer and configured to be polarized by a polarization electrode (12k), K being an integer greater than or equal to 2 - K resonators (10k), formed of a deformable solid material, each resonator being connected to a piezoelectric transducer, and extending around the central axis, thinning towards the central axis, each resonator being configured to deform under the effect of a polarization of the piezoelectric transducer to which it is connected; - a control unit (20), configured to polarize each polarization electrode according to a polarization voltage, modulated according to a modulation frequency;the pump being characterized in that: - each resonator is connected to a sleeve (3k), extending around the central axis; - each resonator is arranged so that the sleeves of each resonator are aligned along a central axis; - the control unit (20) is configured to successively polarize each resonator, according to their respective ranks, so that under the effect of the polarization, a successive deformation of each resonator occurs, the deformation propagating to the sleeve, and causing a successive deformation of the capillary (2) arranged between the sleeves, around the central axis.;

2. A pump according to claim 1, wherein the stress is compression and / or displacement along the central axis.

3. A pump according to claim 1, wherein the modulation frequency is greater than 20 kHz.

4. A pump according to any preceding claim, in which: - each resonator comprises a peripheral portion, delimited by two flat faces, and a central portion, extending between the peripheral portion and the sleeve, the central portion tapering towards the sleeve; - each piezoelectric transducer extends along a flat face.

5. A pump according to any preceding claim, wherein the planar face along which each peripheral transducer extends is defined by a shoulder (15k), the piezoelectric transducer being force-fitted against the shoulder, such that the shoulder bypasses the piezoelectric transducer.

6. A pump according to any preceding claim, wherein each resonator is coupled to at least one annular piezoelectric transducer, the annular piezoelectric transducer extending around the resonator, so as to cause radial compression of the resonator, towards the central axis.

7. A pump according to claim 6, wherein each piezoelectric transducer is force-fitted around the resonator to which it is connected.

8. A pump according to any preceding claim wherein each resonator is coupled to two annular piezoelectric transducers, extending around the resonator, and offset in a direction parallel to the central axis, the central unit being configured to power the piezoelectric transducers so as to cause a displacement of the sleeve, along the central axis and / or a compression of the sleeve perpendicular to the central axis.

9. Pump according to claim 8, wherein each piezoelectric transducer has a dipole moment: - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in the same direction, in which case the control unit is configured to power said piezoelectric transducers in phase; - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in two opposite directions, in which case the control unit is configured to power said piezoelectric transducers electrical in phase opposition; - so as to generate a radial compression of the sleeve predominant over a displacement of the sleeve along the central axis.

10. Pump according to claim 8 in which each piezoelectric transducer has a dipole moment: - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in the same direction, in which case the control unit is configured to supply said piezoelectric transducers in phase opposition; - the dipole moments of the piezoelectric transducers coupled to the same resonator are oriented in two opposite directions, in which case the control unit is configured to supply said piezoelectric transducers in phase; - so as to generate a displacement of the sleeve, along the central axis, predominating over a compression of the sleeve.

11. Pump according to claim 8, wherein the control unit is configured to power said piezoelectric transducers according to a predetermined phase shift, between 0° and 180°, so as to obtain a predetermined ratio between the displacement of the sleeve along the central axis on the compression of the sleeve.

12. Pump according to one of the preceding claims, comprising the capillary (2), the capillary being inserted by force between each sleeve.

13. A pump according to claim 12, wherein the capillary is rigid.

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