EP3532121A1 - Circulatory assistance system - Google Patents
Circulatory assistance systemInfo
- Publication number
- EP3532121A1 EP3532121A1 EP17800722.5A EP17800722A EP3532121A1 EP 3532121 A1 EP3532121 A1 EP 3532121A1 EP 17800722 A EP17800722 A EP 17800722A EP 3532121 A1 EP3532121 A1 EP 3532121A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- rotor
- assistance system
- circulatory assistance
- cam
- stator
- 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- Withdrawn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
Classifications
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F01—MACHINES OR ENGINES IN GENERAL; ENGINE PLANTS IN GENERAL; STEAM ENGINES
- F01C—ROTARY-PISTON OR OSCILLATING-PISTON MACHINES OR ENGINES
- F01C13/00—Adaptations of machines or engines for special use; Combinations of engines with devices driven thereby
- F01C13/04—Adaptations of machines or engines for special use; Combinations of engines with devices driven thereby for driving pumps or compressors
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/205—Non-positive displacement blood pumps
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/247—Positive displacement blood pumps
- A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/247—Positive displacement blood pumps
- A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
- A61M60/258—Piston pumps
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/424—Details relating to driving for positive displacement blood pumps
- A61M60/438—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being mechanical
- A61M60/441—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being mechanical generated by an electromotor
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/562—Electronic control means, e.g. for feedback regulation for making blood flow pulsatile in blood pumps that do not intrinsically create pulsatile flow
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04C—ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT PUMPS
- F04C18/00—Rotary-piston pumps specially adapted for elastic fluids
- F04C18/22—Rotary-piston pumps specially adapted for elastic fluids of internal-axis type with equidirectional movement of co-operating members at the points of engagement, or with one of the co-operating members being stationary, the inner member having more teeth or tooth equivalents than the outer member
Definitions
- the invention relates to the field of implantable prostheses, and more particularly to circulatory assistance systems such as heart pumps.
- Heart failure is a major public health problem in developed countries to the point of affecting approximately 5.7 million Americans with an incidence of 670,000 patients per year. Its impact in terms of morbidity and mortality is estimated at 300,000 deaths and 2.4-3.5 million hospitalizations per year.
- Circulatory support systems have therefore found their place by offering a temporary or permanent alternative to grafting.
- artificial hearts for example comprising a centrifugal pump, pneumatic ventricles heterotopic, electromechanical implantable ventricles, continuous flow pumps or artificial hearts
- An artificial heart is a prosthesis made from synthetic and / or biological materials, used in the treatment of people with irreversible heart failure.
- none of the proposed artificial hearts has been able to give complete satisfaction because none meets the very severe conditions which must absolutely be fulfilled by an artificial heart under penalty of failure.
- the circulatory support system comprises a systemic circulation portion and a pulmonary circulation portion each having a pulsatile aspirated flow rate and a pulsatile flow rate, i.e. go through a maximum and then cancel.
- suction pressure drop must be low in order to prevent hemolysis of the blood when it is depressed, even very low.
- the respiratory assistance system must therefore preserve laminar flows and avoid iso-volumic barometric stresses.
- a heart pump comprising a rotary piston whose cross section is a trochoid, which is rotatable in a body.
- This particular form of the rotor makes it possible to obtain a pump having a uniform rotational speed, whose sucked and discharged flow rates have a pulsatile regime and whose bulk allows its implantation in the thoracic cavity of a patient.
- this device has dead spaces in which blood may stagnate and form thrombi as well as areas of friction conducive to the hemolysis of red blood cells.
- An object of the invention is therefore to provide an implantable circulatory assistance system in a living being limiting the risk of hemolysis of blood and thrombosis, which is also pulsatile, simple to perform and easy to adapt in order to adjust in the body of a patient regardless of his morphology or age.
- the invention proposes a circulatory assistance system comprising:
- a rotor comprising an outer surface defining a curve having the shape of a Reuleaux triangle and a housing delimited by internal walls, and
- a cam shaft comprising a central shaft on which a cam is integrally fixed, the cam shaft being housed in the housing of the rotor and configured to rotate the rotor about an axis of rotation, the axis of rotation; the cam shaft being offset from a center of symmetry of the rotor.
- An outer surface of the cam defines an envelope substantially complementary to the inner walls of the housing so that said inner walls are in contact at all points with the outer surface of the cam and that the assembly formed by the cam and the rotor is devoid of dead space.
- the outer surface of the cam has a circular shape
- the system also includes: a stator in which is formed a cavity accommodating the rotor, a side wall of said cavity having a trochoidal shape defined by the curve traversed by vertices of the rotor corresponding to the vertices of the Reuleaux triangle, the cavity being divided into a first chamber and a second chamber symmetrical with respect to a plane passing through the axis of rotation of the camshaft,
- first intake orifice and a first discharge orifice each opening into the first chamber
- second intake orifice and a second discharge orifice each opening into the second chamber
- first intake orifice and the second second inlet port on the one hand and the first discharge port and the second inlet port on the other hand being symmetrical with respect to the plane
- each vertex of the rotor has a predefined height in a direction parallel to the axis of rotation
- the first and second intake ports and the first and second discharge ports each have a height in the direction parallel to the axis of rotation
- each orifice being less than the predefined height of each vertex of the rotor
- the stator further has a bottom wall and an upper wall substantially perpendicular to the axis of rotation and each orifice extends away from the bottom wall and / or the upper wall of the stator so that the side wall of the cavity is substantially continuous at the lower wall and / or the upper wall of the stator;
- each orifice has a substantially rectangular section
- the distance between an area of the side wall immediately downstream of the inlet and a zone of side wall immediately upstream of the discharge port is greater than the sum of a distance between two peaks of the rotor and a maximum dimension of an activated wafer, so as to form the clearance between the rotor and the stator;
- the stator further has an upper wall and a lower wall connecting the side wall of the cavity, a minimum distance between the upper wall and the rotor and between the bottom wall and the rotor being greater than a maximum height of the rotor;
- the bottom wall and the top wall have surface irregularities configured to locally create a turbulent flow in the system
- the rotor extends at a distance of at least 7 micrometers from the stator walls.
- FIG. 1 is a top view of an exemplary embodiment of a circulatory assistance system according to the invention which illustrates an admission phase in a first ventricular chamber and a drain phase of a second ventricular chamber.
- FIG. 2 is a view from above of the circulatory assistance system of FIG. 1 which illustrates a neutral time of the first ventricular chamber
- FIG. 3 is a view from above of the circulatory assistance system of FIG. 1 which illustrates a phase of emptying the first ventricular chamber and an admission phase in the second ventricle
- FIG. 4 is a view from above of the circulatory assistance system of FIG. 1 which illustrates a neutral time of the second ventricular chamber
- FIG. 5 is a partial perspective view of an exemplary embodiment of a circulatory assistance system according to the invention, on which are visible in transparency an intake orifice and a discharge orifice,
- FIG. 6 is a partial view of the top of an embodiment of a circulatory assistance system according to the invention, on which is illustrated a shunt zone at an intake orifice and a discharge port of the system,
- FIG. 7 is a view from above of an exemplary embodiment of a front face of a circulatory assistance system according to the invention.
- FIG. 8 is a sectional view of the front face of FIG. 7, and
- Figure 9 is a partial sectional view according to the height of the rotor of an exemplary embodiment of a circulatory assistance system according to the invention.
- a circulatory assistance system 1 comprises a rotor 10, a camshaft 20 and a stator 30.
- the rotor 10 comprises an outer surface defining a curve having the shape of a Reuleaux triangle, and a housing delimited by internal walls.
- the triangle of Reuleaux is a curve of constant width, that is to say a curve of which all the diameters have the same length. More precisely, the triangle of Reuleaux is a closed plane curve whose width, measured by the distance between two opposite parallel lines which are tangent to it, is the same whatever the orientation of these straight lines.
- the rotor 10 thus has three vertices 12 corresponding to the vertices of the Reuleaux triangle separated by three curved surfaces. We hear by elsewhere by radius R of the rotor 10 the distance between the center of symmetry of the rotor 10 and an apex 12 of the rotor 10.
- the camshaft 20 comprises a central shaft 22 on which is integrally fixed a cam 24.
- the camshaft 20 is housed in the housing of the rotor 10 and is configured to rotate the rotor 10 about an axis of rotation. rotation X corresponding to the axis of extension of the central shaft 22.
- the rotor 10 is fixed on the cam 24 and the cam 24 is configured so that the center of symmetry C of the rotor 10 is offset relative to the axis of rotation X of the central shaft 22 of a distance e corresponding to the eccentricity of the cam 24.
- the central shaft 22 of the camshaft 20 is configured to be connected to a motor capable of driving the central shaft 22 in rotation at a determined speed.
- the rotational speed of the central shaft 22 may in particular be adjusted according to the desired flow rate in the circulatory assistance system 1, which depends inter alia on the body surface of the patient.
- An outer surface 25 of the cam 24 defines an envelope substantially complementary to the inner walls of the housing so that the inner walls 15 of the rotor 10 are in contact at all points with the outer surface 25 of the cam 24 and that the assembly formed by the cam 24 and the rotor 10 is devoid of dead space.
- the shape of the outer surface 25 of the cam 24 is complementary to the shape of the inner walls of the housing of the rotor 10 and the height of the cam 24 is substantially equal to the height of the housing.
- height will be understood to include a dimension (in particular of the camshaft 20, of the rotor 10 or of the stator 30) in a direction substantially parallel to the axis of rotation X.
- the outer surface 25 of the cam 24 and the inner walls 15 of the housing may for example be smooth, that is to say without protrusion or meshing means.
- the Applicant has indeed noticed that the transmission of forces to the rotor 10 by simple friction between the outer surface 25 of the cam 24 and the inner walls 15 of the housing was sufficient in the case of a circulatory assistance system 1 of the heart pump type.
- the outer surface 25 of the cam 24 may have a circular section.
- the cam 24 of the camshaft 20 and the rotor 10 may be monoblock, that is to say formed integrally and in one piece or fixed together by gluing.
- the rotor 10 is housed in a cavity 31 formed in the stator 30.
- the side wall 32 of the cavity 31 has a trochoidal shape defined by the curve traveled by the vertices 12 of the rotor 10.
- the vertices 12 of the rotor 10 substantially continuously sweep the side wall 32 of the cavity 31 during the rotation of the rotor 10 in the stator 30.
- the ratio between the radius R of the rotor 10 and the eccentricity e thus defines the shape of the side wall 32 of the cavity 31.
- the stator 30 further has an upper wall 33 and a lower wall 34 substantially parallel to each other and normal to the axis of rotation X of the camshaft 20, which extend facing an upper face 14 and a a lower face 16 of the rotor 10, respectively.
- the cavity 31 of the stator 30 is divided into a first ventricular chamber 35 and a second ventricular chamber 38 which extend symmetrically with respect to a first plane P1 passing through the axis of rotation X of the central shaft 22 of the camshaft 20.
- intake orifices 36, 39 and delivery ports 37, 40 opening into the first chamber 35 and into the second chamber 38 are formed in the wall Lateral 32 of the stator 30.
- the first chamber 35 comprises a first inlet 36 and a first discharge port 37 while the second chamber 38 comprises a second inlet 39 and a second discharge port 40.
- first inlet port 36 and the second discharge port 40 on the one hand and the first discharge port 37 and the second inlet port 39 on the other hand are symmetrical with respect to the first plane P1 in order to to make the flows sucked up and pushed back by the two pulsatile chambers. They are also symmetrical with respect to a second plane P2 which extends perpendicularly to the first plane P1 and passes through the center of rotation of the shaft.
- FIGS. 1 to 4 show the four phases of an operating cycle of the circulatory assistance system 1.
- the rotor 10 rotates in the counterclockwise direction. This is however not limiting, the rotor 10 being rotatable in the clockwise direction.
- the rotor 10 is positioned so as to release the first inlet orifice 36 and close the first discharge orifice 37 of the first chamber 35 and to close the second inlet orifice 39 and release the second discharge port 40 of the second chamber 38.
- the rotational movement of the rotor 10 in the trigonometric direction has the effect of aspirating a fluid through the first inlet 36 and purge a fluid by the second discharge port 40 by closing the discharge path of the first chamber 35 and the admission path of the second chamber 38.
- a second phase (FIG. 2), the rotor 10 is positioned so as to block the first inlet orifice 36 and the first discharge orifice 37 and to release the second inlet orifice 39 and the second inlet orifice 37. repression 40 of the second chamber 38.
- This second phase corresponds to a neutral time for the first chamber 35 (zero flow).
- the rotational movement of the rotor 10 in the trigonometrical direction has the effect of sucking a fluid through the second inlet orifice 39 and completing the purging of the fluid by the second discharge orifice 40.
- the rotor 10 is positioned so as to keep open the second inlet orifice 39 and close the second discharge orifice 40 of the second chamber 38 and to release the first discharge port 37 and closing the first inlet 36 of the first chamber 35.
- the rotational movement of the rotor 10 in the trigonometric direction therefore has the effect of continuing the suction of the fluid through the second inlet 39 and start to purge the fluid sucked during the first phase by the first discharge orifice 37 by closing the discharge way of the second chamber 38 and the admission way of the first chamber 35.
- a fourth phase (FIG. 4), the rotor 10 is positioned so as to block the second inlet orifice 39 and the second discharge orifice 40 of the second chamber 38 and to release the first inlet orifice 36 and keep open the first discharge port 37 of the first chamber 35.
- This fourth phase corresponds to a neutral time for the second chamber 38 (zero flow).
- the rotational movement of the rotor 10 in the trigonometrical direction has the effect of sucking a fluid through the first inlet orifice 36 and completing the purging of the fluid by the first discharge orifice 37.
- the first, second, third and fourth phases of the cycle take place continuously and are consecutive.
- a new cycle begins by repeating the phases from the first to the fourth.
- each orifice 36, 37, 39, 40 has a rectangular section, the length of the rectangle extending along the height of the stator 30 (see Figure 5).
- Such a section makes it possible to preserve a laminar flow in the system 1 even around the orifices and thus to limit the friction forces likely to be applied to the blood by maintaining constant shear stresses, thus reducing the risk of hemolysis .
- the size of the section (and more particularly its width) is moreover determined by the flow rate that the system 1 must provide.
- the height of the orifices 36, 37, 39, 40 (corresponding to the length of their rectangular section) is smaller than the height of the vertices 12 of the rotor 10 and therefore less than the height of the lateral wall 32 of the stator 30.
- the side wall 32 forms a continuous envelope on the periphery of the cavity 31, even at the openings 36, 37, 39, 40, thus providing areas above and / or below the orifices.
- 36, 37, 39, 40 forming slides 42 for the vertices 12 of the rotor 10 preventing them from penetrating the orifices 36, 37, 39, 40 and to lock the rotor 10 in rotation.
- each slideway 42 may be of the order of a few millimeters.
- the side wall 32 of the cavity 31 is dimensioned so as to maintain a minimum clearance (preferably over the entire height of the side wall 32) between the side wall 32 and the vertices 12 of the rotor 10 regardless of the operating phase of the system 1 ( Figure 6). It should be noted, however, that during the revolution of the rotor 10, said rotor 10 remains in contact at all times with the side wall 32 in at least one point in order to constrain its tilting.
- This minimum clearance thus generates a washing flow making it possible to continuously stir the first chamber 35 and the second chamber 38 during rotation of the rotor 10 in the stator 30, even during the neutral times, thus greatly reducing the risk of thrombus formation. .
- the minimum clearance is greater than the size of an activated wafer (about seven micrometers) to ensure that the wafers are not crushed or at least stressed between the rotor 10 and the sidewall 32 of the wafer.
- the clearance between the side wall 32 and the vertices 12 of the rotor 10 may be of the order of a few millimeters. The zones of the system 1 in which the vertices 12 of the rotor 10 are at a short distance from the lateral wall 32 of the cavity 31 are then less likely to be stressed, which significantly reduces the risk of haemolysis of the blood.
- the dimensions and the shape of the side wall 32 of the cavity 31 of the stator 30 are chosen so that the distance D1 between the zone Za of the side wall 32 immediately downstream of the inlet orifice 36 (respectively 39) and the zone Zb immediately upstream of the discharge orifice 37 (respectively 40) (upstream and downstream being defined relative to the direction of rotation of the rotor 10 in the stator 30) is greater than the sum of the distance D2 between two vertices 12 of the rotor 10 and the size of an activated wafer (of the order of seven micrometers) so as to obtain the desired minimum clearance.
- a rotor 10 will be chosen such that the distance D1 remains smaller than the sum of the distance D2 and a few millimeters.
- the distance D2 is globally equal to 2.R.cos (30), where R corresponds to the radius R of the rotor 10.
- R corresponds to the radius R of the rotor 10.
- the minimum clearance between the upper 33 and lower 34 walls of the stator 30 and the faces 14, 16 facing the rotor 10 is greater than the size of a wafer (about seven micrometers) to limit the risks of hemolysis of the blood, for example of the order of one millimeter (within two micrometers).
- the surface of the upper 33 and lower 34 walls of the stator 30 which faces the rotor 10 may furthermore have surface irregularities 44 configured to locally create a turbulent flow in the system 1 and thus force the evacuation of the red blood cells inevitably. accumulated against said walls 33, 34.
- the surface irregularities 44 are chosen to transform the laminar flow of blood at the approach of the lower face 16 and the upper face 14 into a turbulent flow, thus limiting the risks of thrombus formation.
- the surface irregularities 44 may in particular have the form of fins (or propellers) extending radially flaring from the axis of rotation X to the side wall 32.
- the fins 44 thus have a substantially triangular section.
- each fin 44 has a variable height from upstream to downstream (relative to in the direction of rotation of the rotor 10 in the stator 30) to promote the generation of a turbulent flow.
- the profile may thus have an upstream section whose thickness is increasing from the upstream edge 45 of the fin 44 to an intermediate vertex 46 and then a downstream section whose thickness decreases from the vertex 12 to the downstream edge 47 of the fin 44.
- the slope of the upstream section is softer than the slope of the downstream section.
- the angle between the upstream edge 45 and the top 46 of a fin 44 given is at least twice as large as the angle between this vertex 12 and the downstream edge 47 of said fin 44.
- the fins 44 are preferably adjacent to each other so as to form a symmetrical relief around the axis of rotation X.
- the upstream edge 45 of a fin 44 given therefore corresponds to the downstream edge 47 of the fin 44 extending immediately upstream.
- the height of the surface irregularities is less than the size of an activated wafer, less than seven micrometers, to prevent stagnation of said wafers between irregularities.
- the height between the top 46 of a given fin 44 and the downstream edge 47 of this fin 44 is preferably less than seven micrometers.
- the size of the circulatory assistance system 1 depends on the anatomy of the patient to receive the system 1, including its cardiac output.
- the cardiac output of a patient can be determined for example according to his body surface area. Such a determination being known to those skilled in the art, it will not be detailed here.
- the knowledge of the cardiac output thus makes it possible, on the one hand, to determine the dimensions of the cavity 31 and the rotor 10, and on the other hand the rotational speed of the camshaft 20.
- the dimensions of the cavity 31 are determined in practice from the eccentricity e of the cam 24, the radius R of the rotor 10 and the height of the stator 30.
- the R / e ratio makes it possible to define the trochoidal curve. of the cavity 31 and thus the shape of each chamber 35, 38 of the stator 30 while the height of the stator 30 defines the volume of the chambers.
- the ratio R / e may especially be between 5.0 and 6.5.
- the geometry of the trochoidal shape of the cavity 31 is defined by the following trigonometric formulas, which depend on the eccentricity e of the cam 24 and the radius R of the rotor 10:
- the ratio between the radius R of the rotor 10 and the eccentricity e may be equal to 5.678.
- the system 1 is simple and has few moving parts
- a rotor 10 and a camshaft 20 which makes it reliable and can greatly reduce friction and therefore energy requirements and the risk of thrombosis and hemolysis.
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Mechanical Engineering (AREA)
- Cardiology (AREA)
- Hematology (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Vascular Medicine (AREA)
- General Engineering & Computer Science (AREA)
- External Artificial Organs (AREA)
- Rotary Pumps (AREA)
- Valve Device For Special Equipments (AREA)
Abstract
Description
Claims
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
FR1660511A FR3058067B1 (en) | 2016-10-28 | 2016-10-28 | CIRCULATORY ASSISTANCE SYSTEM |
PCT/EP2017/077681 WO2018078135A1 (en) | 2016-10-28 | 2017-10-27 | Circulatory assistance system |
Publications (1)
Publication Number | Publication Date |
---|---|
EP3532121A1 true EP3532121A1 (en) | 2019-09-04 |
Family
ID=57750235
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP17800722.5A Withdrawn EP3532121A1 (en) | 2016-10-28 | 2017-10-27 | Circulatory assistance system |
Country Status (10)
Country | Link |
---|---|
US (1) | US20190358377A1 (en) |
EP (1) | EP3532121A1 (en) |
JP (1) | JP2020511203A (en) |
KR (1) | KR20190092406A (en) |
CN (1) | CN110325227A (en) |
BR (1) | BR112019008469A2 (en) |
CA (1) | CA3041776A1 (en) |
FR (1) | FR3058067B1 (en) |
WO (1) | WO2018078135A1 (en) |
ZA (1) | ZA201903305B (en) |
Families Citing this family (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN112972886B (en) * | 2021-02-02 | 2022-09-30 | 北京工业大学 | Single-slider volumetric blood pump |
CN113893454A (en) * | 2021-09-28 | 2022-01-07 | 中国科学院江西稀土研究院 | Pulsating artificial heart pump, stator structure and application |
CN115111863B (en) * | 2022-02-28 | 2024-04-19 | 海信冰箱有限公司 | Refrigerator with a refrigerator body |
Family Cites Families (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2389382B1 (en) * | 1977-05-06 | 1982-07-09 | Anvar | |
CN1117115A (en) * | 1994-08-13 | 1996-02-21 | 梅展鹏 | Engine |
US5980448A (en) * | 1998-01-28 | 1999-11-09 | Vascor, Inc. | Single chamber blood pump |
US8177536B2 (en) * | 2007-09-26 | 2012-05-15 | Kemp Gregory T | Rotary compressor having gate axially movable with respect to rotor |
CN203756529U (en) * | 2014-03-06 | 2014-08-06 | 艾默生环境优化技术(苏州)有限公司 | Rolling rotor type compression mechanism and compressor comprising same |
DE102014010745A1 (en) * | 2014-07-23 | 2016-02-11 | Rheinisch-Westfälische Technische Hochschule Aachen | Rotary piston pump |
-
2016
- 2016-10-28 FR FR1660511A patent/FR3058067B1/en not_active Expired - Fee Related
-
2017
- 2017-10-27 CA CA3041776A patent/CA3041776A1/en not_active Abandoned
- 2017-10-27 JP JP2019545849A patent/JP2020511203A/en active Pending
- 2017-10-27 US US16/345,355 patent/US20190358377A1/en not_active Abandoned
- 2017-10-27 KR KR1020197015355A patent/KR20190092406A/en unknown
- 2017-10-27 CN CN201780081290.9A patent/CN110325227A/en active Pending
- 2017-10-27 EP EP17800722.5A patent/EP3532121A1/en not_active Withdrawn
- 2017-10-27 WO PCT/EP2017/077681 patent/WO2018078135A1/en unknown
- 2017-10-27 BR BR112019008469A patent/BR112019008469A2/en not_active Application Discontinuation
-
2019
- 2019-05-24 ZA ZA2019/03305A patent/ZA201903305B/en unknown
Also Published As
Publication number | Publication date |
---|---|
US20190358377A1 (en) | 2019-11-28 |
CA3041776A1 (en) | 2018-05-03 |
BR112019008469A2 (en) | 2019-07-09 |
KR20190092406A (en) | 2019-08-07 |
FR3058067B1 (en) | 2018-11-30 |
CN110325227A (en) | 2019-10-11 |
WO2018078135A1 (en) | 2018-05-03 |
FR3058067A1 (en) | 2018-05-04 |
ZA201903305B (en) | 2020-09-30 |
JP2020511203A (en) | 2020-04-16 |
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