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
  • A61M60/40—Details relating to driving
  • A61M60/403—Details relating to driving for non-positive displacement blood pumps
  • A61M60/422—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being electromagnetic, e.g. using canned motor 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
  • A61M60/10—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
• • 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
  • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
• • 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
  • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
  • A61M60/17—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart inside a ventricle, e.g. intraventricular balloon 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
  • A61M60/205—Non-positive displacement blood pumps
  • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
  • A61M60/221—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having both radial and axial components, e.g. mixed flow 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
  • A61M60/205—Non-positive displacement blood pumps
  • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
  • A61M60/226—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly radial components
  • A61M60/232—Centrifugal 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
  • A61M60/205—Non-positive displacement blood pumps
  • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
  • A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow 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
  • A61M60/403—Details relating to driving for non-positive displacement blood pumps
  • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
  • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
  • A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
• • 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
  • A61M60/515—Regulation using real-time patient data
• • 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
  • A61M60/515—Regulation using real-time patient data
  • A61M60/523—Regulation using real-time patient data using blood flow data, e.g. from blood flow transducers
• • 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
  • A61M60/80—Constructional details other than related to driving
  • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
  • A61M60/804—Impellers
• • 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
  • A61M60/80—Constructional details other than related to driving
  • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
  • A61M60/804—Impellers
  • A61M60/806—Vanes or blades
• • 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
  • A61M60/80—Constructional details other than related to driving
  • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
  • A61M60/81—Pump housings
  • A61M60/812—Vanes or blades, e.g. static flow guides
• • 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
  • A61M60/80—Constructional details other than related to driving
  • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
  • A61M60/827—Sealings between moving parts
• • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
  • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
  • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
  • F04D29/00—Details, component parts, or accessories
  • F04D29/18—Rotors
  • F04D29/181—Axial flow rotors
  • F04D29/183—Semi axial flow rotors
• • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
  • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
  • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
  • F04D29/00—Details, component parts, or accessories
  • F04D29/40—Casings; Connections of working fluid
  • F04D29/52—Casings; Connections of working fluid for axial pumps
  • F04D29/54—Fluid-guiding means, e.g. diffusers
  • F04D29/548—Specially adapted for liquid pumps
• • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
  • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
  • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
  • F04D3/00—Axial-flow pumps
  • F04D3/02—Axial-flow pumps of screw type
• • 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
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/33—Controlling, regulating or measuring
  • A61M2205/3365—Rotational speed
• • 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
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/82—Internal energy supply devices
  • A61M2205/8206—Internal energy supply devices battery-operated
• • 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
  • A61M2206/00—Characteristics of a physical parameter; associated device therefor
  • A61M2206/10—Flow characteristics
  • A61M2206/20—Flow characteristics having means for promoting or enhancing the flow, actively or passively

Definitions

• the present invention relates to a pump for ventricular assist.
• This is for example a battery-powered pump intended to be inserted into a human body to help the flow of blood.
• the axial pump which generates a high flow rate with a small increase in pressure
• the centrifugal pump which generates a high pressure with a low flow rate
• the specific speed is a reduced variable calculated according to different parameters: the desired flow rate, the height of elevation (pressure difference between the inlet and the outlet) and the speed of rotation. From this value, the choice of the pump can be made among the following modes: centrifugal for a speed included in [0-1,2], mixed for a specific speed included in [1-2,2] and axial to -above.
• the charts allow to choose a type of pump with a predefined profile for the blades or blades used in the rotor.
• shear forces are found in most pumps of the prior art because the rotors and casing used in the prior art create excessive swirls in the blood. Shear forces are responsible for the creation of hemolysis, that is the destruction of red blood cells. When red blood cells are destroyed, regardless of the flow rate to carry blood, oxygen does not reach the cells.
• Another disadvantage is the stagnation of blood causing clots of blood, causing thrombosis.
• the present invention relates to a pump avoiding the creation of thrombosis.
• a pump intended to be immersed in a fluid, this pump comprising: an inductor with guide vanes to make the flow of the fluid linear;
• a rotor comprising a central body of flared shape, this rotor being intended to create kinetic energy and being disposed downstream of the inductor with respect to the direction of circulation of the fluid;
• this helical blade having a flared outer profile and comprises turns with increasing winding pitch and tending towards infinity, and the inner volume of the casing being complementary to the flared shape of said at least one helical blade,
• this diffuser being disposed downstream of the rotor so as to discharge the fluid from the rotor to the outside by transforming the kinetic energy created by the rotor into potential energy;
• a rectifier equipped with blades and an orifice at the outlet of diameter smaller than the input diameter of the rectifier, the blades directing the fluid, coming from the diffuser, towards the orifice so as to increase the speed and give the fluid a predetermined profile at the outlet of the orifice.
• the helical blade is wound around the rotor such that the angle of attack of the helical blade decreases as one moves from the upstream end of the rotor towards the rotor. downstream end; the angle of attack being defined as the angle between the axis of rotation of the rotor and a vector tangent to the outer surface of the helical blade.
• the blade can be wound around the rotor as described mainly in the present application, but it can also be positioned on the inner wall of the housing.
• linear fluid flow as defined herein is as opposed to a swirling flow. This linear flow can be laminar.
• the straightener (“straightener” in English) according to the invention makes it possible to create a flow by concentrating the fluid so as to obtain high speed values at the output of the pump.
• the vascular system of a heart has fairly high vascular resistance.
• An effective pump is a pump that can propel the blood into the valves with enough pressure to overcome these resistances Vascular.
• the pressure at the outlet of the pump is essential compared to the output speed which with the pump according to the invention can reach the maximum speed of 3 m / s.
• the rectifier makes it possible to channel the fluid, to create a profile making it possible to have a maximum speed at a point, i.e. aligned with the aortic valve, so as to expel the flow in a laminar manner.
• the diameter of the outlet orifice is smaller than the internal diameter of the housing. Its small exit diameter, for example a half or a third of the internal diameter of the housing, makes it possible to adjust the pressure parameters, between 80 and 200 mmHg, and speed, between 1 and 3 m / s, while avoiding the creation a current at negative speed (in backflow due to lack of pressure and homogeneity of the output flow).
• the diffuser and rectifier assembly according to the invention therefore makes the pump effective.
• the rectifier diffuses the fluid directly to the outlet in the environment by creating a flow.
• This ambient medium may advantageously be said fluid, which is preferably blood.
• the inductor according to the invention avoids the phenomenon of cavitation, that is to say the creation of bubble in the fluid.
• this pump is perfectly adapted for operation in a vertical arrangement, or slightly bent, that is to say inclined between 0 and 5 degrees with respect to the vertical axis.
• the pump according to the invention can also operate lying down like most pumps of the prior art.
• the pump according to the invention may further comprise an inlet chamber provided with lateral openings so that the fluid can penetrate radially and then engage in the axis towards the inductor.
• This inlet chamber may be cylindrical having on its upper part downstream of said openings, a receptacle for accommodating the inductor.
• the intake chamber and the inductor may be two pieces intended to be firmly attached to one another or be designed as a single piece.
• the guide blades of the inductor are advantageously designed so as to pass a rod for connecting the rotor to a motor, the inductor located between the housing and the engine.
• the central body (with the helical blade) rotates inside the housing without coming into contact with the other components of the pump.
• the pump comprises altogether four identical helical blades distributed homogeneously around the central body.
• the central body of the rotor is of oblong shape, that is to say that the flanks of the central body may have curvatures.
• the head of this central body may be rounded and devoid of blades, for example in the form of a warhead.
• the diffuser may be a hollow cylinder provided with straight guide vanes distributed in its inner wall and extending from the periphery to the center. Its role is to transform a portion of the kinetic energy of the fluid into pressure, this pressure being in particular transferred to the rectifier.
• the guide vanes of the diffuser may have a twisted shape in a direction opposite to the winding direction of the helical blade around the central body.
• the diffuser when the central body comprises a rounded head devoid of blades, the diffuser caps this rounded head, and each guide blade of the diffuser has a shape complementary to a portion of the rounded head facing.
• the internal diameter of the cylinder forming the diffuser is identical to the internal diameter of the housing at the downstream end of the helical blade.
• the rectifier is disposed downstream of the diffuser in the direction of circulation of the fluid.
• the inner wall of the rectifier may be conically shaped with straight guide vanes arranged thereon.
• this diffuser may comprise a central part in the shape of a pointed ogive towards the downstream, a cylinder around the base of the ogive, guide blades connecting this cylinder to the base of the warhead; this diffuser being intended to engage with the downstream end of the rotor via a bearing to keep the diffuser fixed relative to the rotor.
• a diffuser makes it possible to improve the directivity, the pressure and the homogeneity of the flow at the outlet of the pump.
• the guide blades of the diffuser can also be twisted in a direction opposite to the winding direction of the helical blade around the central body.
• the diffuser opposes the swirling nature of the fluid arriving from the rotor. After the passage of the fluid in the diffuser, it is completely corrected so as to constitute a laminar flow by the action of the rectifier.
• the rectifier is disposed downstream of the diffuser in the direction of circulation of the fluid; guide vanes are straight and are designed so as to let the head of the warhead enter the central part of the rectifier.
• the rotor and helical blade assembly may advantageously have a centrifugal type profile on the upstream side, of mixed type in the central part, and of axial type on the downstream side.
• the rotor and housing assembly has the characteristics of both:
• a pump of the centrifugal type that is to say a radial acceleration of the fluid arriving axially, to do this the lower part of the helical blades has a pronounced angle, of the order of the order of 45 degrees, for example between 40 and 50 degrees, relative to the axis of rotation of the rotor,
• a mixed type pump that is to say a slope or a less pronounced curvature of the turns of the helical blades
• the pump according to the invention avoids the vortices by a call of blood using a centrifugal type structure and an axial discharge.
• the portion of the upstream side of the assembly central body and helical blade is dimensioned for a specific speed between 0 and 1.2. Furthermore, the central portion of the central body and helical blade assembly can be sized for a specific speed of between 1 and 2.2. Finally, the central portion of the central body and helical blade assembly can be sized for a specific speed greater than 2.2. This is a specific velocity value for classifying the centrifugal, mixed or axial structures respectively.
• the pump according to the invention should have a specific speed of the order of 1.
• the abacuses In the technical field of the invention and the commonly accepted prejudices would have naturally pushed the skilled person to a choice of centrifugal or axial pump or turbine.
• the pump according to the invention has a very particular and innovative design where the three types of pump are present, including the mixed type.
• the structure of the pump according to the invention does not follow the traditional method ("handbook") of drawing a pump or turbine of homogeneous type.
• the pump comprises a shaft for driving and holding the rotor, this shaft being fixed on the upstream end of the rotor and passing through the inlet chamber in its axial zone.
• This shaft is in particular connected to a motor adapted to set the rotor in motion.
• the inlet chamber, the inductor, the housing and the diffuser are designed in one piece or are firmly fixed to each other without relative movements, the rotor being kept rotatable in the housing.
• the inductor in the inlet chamber, the diffuser and the rectifier are also fixed elements relative to the rotor.
• the helical blade has a radial height (its thickness in the radial direction) the same throughout its length (from bottom to top of the central body).
• a radial height its thickness in the radial direction
• a height of 1 to 4 mm at the bottom and 1 to 3 mm at the top of the central body can be provided, with continuous progression or increments, depending on the pressure and speed characteristics required.
• the overall outer shape of the pump is a cylinder of circular section, but other types of sections may be envisaged such as a square section, triangular; the intake chamber may have a different overall shape of the overall shape of the housing.
• a method of controlling the pump as defined above In this process, the rotor is actuated by a motor, connected to the pump, according to the heart rate.
• the blood is drawn out of the pump according to the rhythm of the heartbeat, including sinusoidal type with accelerations and slowdowns.
• the heart rate can be detected by means of a probe connecting the heart to a control unit that controls the motor.
• the pump adapts in rotation: if the heart beats at 60 pulses or at 120 pulsations per minute, the pump according to the invention follows the rhythm whereas most of the pumps of the prior art operate at fixed speed.
• FIG. 1 is an external general view of the pump according to the invention
• FIG. 2 is an internal view by transparency of the pump according to the invention
• FIG. 3 is an exploded view of the pump according to the invention.
• FIG. 4 is a diagrammatic view in longitudinal section of the pump according to the invention.
• FIG. 5 is a perspective view of the intake chamber according to the invention.
• FIG. 6 is a perspective view of the inductor to be inserted in the intake chamber according to the invention.
• FIG. 7 is a diagram illustrating different views of the casing according to the invention.
• FIG. 8 is a perspective view of the rotor according to the invention
• FIG. 9 is a perspective view of the diffuser according to the invention
• FIG. 10 is a perspective view of the rectifier according to the invention
• FIG. 11b and 11c are schematic views of a variant of the pump according to the invention
• Figures 12 and 13 are schematic perspective views of the front and rear of the diffuser according to the variant of Figures l la-c,
• FIG. 14 is a schematic view of a rotor according to a variant in which the head of the rotor is in the form of a warhead
• FIG. 15 is a schematic view of a rotor according to the variant of FIGS. 1a-c,
• FIGS. 16 and 17 are schematic views of an inductor according to the invention.
• FIGS 18 and 19 are schematic views of a rectifier according to the invention.
• FIG 20 is a schematic sectional view of a blade with an illustration of different parameters.
• the pump 1 according to the invention in the overall form of a circular section cylinder for sucking a fluid such as blood and pump back to promote blood circulation.
• a fluid such as blood and pump back to promote blood circulation.
• Such a pump is intended to be installed in a body, in particular for ventricular assistance.
• Its length is about 61.8mm
• the diameter of the housing 2 is about 17-20 mm
• the lower portion 3a has a diameter of about 15-20 mm.
• the pump according to the invention can advantageously, but not only, be used in a vertical position, that is to say the housing 2 in the vertical and above the lower part 3a.
• Most pumps of the prior art are used in a horizontal mode.
• the function of the admission chamber 3 is to introduce the fluid, in particular blood, through the openings or apertures 3d under the action of a suction coming from inside the casing 2. The fluid is then discharged through an opening at the end of the housing.
• FIG. 5 shows in more detail the inlet chamber 3 consisting of a lower part 3a, an upper part 3b, the two parts being connected by radial guides 3c delimiting openings 3d towards the inside of the admission room.
• the lower part 3a is a cylinder of circular section, thick wall so that the central portion is a third tunnel.
• the diameter of the latter is smaller than the outside diameter of the cylinder section, which is about 15mm.
• the diameter of the tunnel 3e is 6 mm.
• the radial guides 3c are three plates inscribed in planes which intersect on the axis of the intake chamber.
• the outer face of each plate 3c is flush with the outer lateral surface of the upper part 3b.
• the central zone containing the axis of the inlet chamber is empty for the passage of fluid. This central zone constitutes a tunnel of diameter greater than the diameter of the tunnel 3e.
• the upper part 3b is in the form of a cylinder having two different thicknesses, a first thickness on the upstream side, that is to say on the side in contact with the radial guides 3c, and a second thickness, lower than the first, on the downstream side. Between the two layers is a step 3f.
• an inductor 4 as described in Figure 6 can be inserted and fixed inside the inlet chamber 3 in the part 3b of great thickness. During insertion, this inductor 4 can come to rest on the ends of the guides 3c.
• the dimensions of the inductor 4 are such that once inserted, its upper part is flush with the step 3f.
• Other embodiments may be envisaged, such as, for example, a single part consisting of elements 3b and 4, or else 3 and 4.
• Inductor 4 is a hollow cylinder comprising radial guides 4a, for example four in number. 'to six, all the way up the cylinder and inscribed in concurrent radial planes in the center of the cylinder.
• the inductor 4 serves as a fluid inlet guide. It limits cavitation in the upper floors that will be described later.
• the guides 4a produce a laminar flow so that the turbulent nature of the fluid is greatly reduced. This makes it possible to slow down and reduce the generally rapid deterioration of the rotor, which will be described below, by limiting the attacks of the fluid on the blades of this rotor.
• the different parts of the pump can be designed by molding, 3D printing, machining or others,
• Figures 2 and 3 are distinguished in transparent interior view and exploded view of the different parts of the pump.
• the view of FIG. 2 makes it possible to distinguish a hollow space 3g of larger diameter than that of the tunnel 3e.
• the upper stages of the intake chamber comprise a rotor 5 intended to move inside a housing 6, and output elements such as a diffuser 7 and a rectifier 8.
• the rotor 5 visible in FIGS. 3 and 4 has an oblong or oval shape with a single axis of symmetry: that is to say, as an elongated or stretched ogive on one end.
• the rotor 5 is a body whose diameter of the circular section (radial section) increases from its lower part to the upper part, then decreases rapidly to the upper end.
• a useful part can be defined as that for which the diameter increases. This growth is preferably continuous but not linear so that the outer shape of the useful part is of conical type convex wall.
• each helical blade is a serpentine of constant or variable thickness over the entire length so that the outer shape of the rotor with the helical blades with evolutionary pitch that remains conical with convex wall.
• This innovative form of rotor 5 has an upper half-sphere part 5h and the useful part, the latter can be pre-cut in three parts: a (first) lower part 5 whose characteristics (shape, angle of attack, inclination of the blades , ...) are those of a centrifugal pump. In a centrifugal pump the pumped fluid is drawn axially and then accelerated radially, and finally discharged tangentially.
• the fluid arrives axially via the inlet chamber and is then accelerated radially thanks to the pronounced curvature of the bottom of the rotor.
• This pronounced curve is obtained using abacuses known to those skilled in the art such as the charts published by Sabersky, Acosta and Hauptmann in 1989 ("Fluid Flow: A First Course in Fluid Mechanics", by Rolf H. Sabersky, AJ Acosta and Edward G. Hauptmann, 3 Sub Edition, March 6, 1989, Prentice Hall College Div) or Stepanoff A. (Stepanoff A., "Centrifugal and Axial Flow Pumps", 2nd ed 1957, New York: Krieger Publishing Company) .
• the centrifugal effect is optimally rendered by the fact that the housing 6 has an inner concave shape also conical, complementary to the shape of the rotor 5 over the entire useful part.
• the second part 5f is of mixed form according to the charts. It is an intermediate part following the centrifugal part and having a curvature less pronounced than that of the centrifugal part or a plane inclined relative to the axis of rotation.
• the third portion 5g is of axial shape, the outer shape of the rotor and the inner shape of the housing are substantially linear and parallel to the axis of rotation of the rotor.
• Figure 8 we see in detail such a rotor.
• a not shown shaft is provided in the form of a rod fixed in the axis of the rotor.
• the shaft connects the rotor 5 to a motor not shown, the shaft passing via the inlet chamber.
• the shaft rotates without coming into contact with the walls of the intake chamber.
• the shaft and the rotor can be designed in a single piece or the shaft can be inserted into the rotor 5 by the bore 5i visible in Figure 4.
• the housing 6 consists of a main body 6a and a secondary body 6b.
• the main body 6a is an elongated cylinder, the secondary body being a cylinder whose outer diameter is smaller than the outer diameter of the main body.
• the secondary body 6b is shaped to fit and be held fixed in the upper part 3b of the intake chamber. Preferably the lower end of the secondary body 6b abuts on the step 3f, visible in Figure 5.
• the inner shape of the housing 6 is complementary to the outer shape of the useful part of the rotor along the entire length of the helical blades.
• An upper portion of the casing on the other hand, has a uniform internal diameter so that it constitutes a conventional hollow cylinder of circular section. At the level of this upper part, inside the housing, we find the head 5h of the rotor as well as the diffuser 7 and the rectifier 8.
• the complex internal shape of the casing makes it possible to perform the centrifugal, mixed and axial functions so that the fluid is sucked into the pump without creating a vortex, it is then propelled towards the top of the pump without shear so as not to destroy red blood cells.
• the rotor according to the invention makes it possible to communicate the kinetic energy to the fluid by its particular shape. It therefore modifies the speed of the fluid without shear and also increases its pressure. To do this, the output elements of the pump help to increase the pressure by having a reduced outlet orifice as well as specific shapes.
• the diffuser 7 which is a cylinder for coming to cap the head 5h of the rotor.
• the diffuser comprises guide blades oriented 7a in the direction of the discharge of the fluid supplied by the rotor.
• the orientation of the guide blades makes it possible to transform part of the kinetic energy of the fluid into pressure, which is a potential energy.
• the thickness of the guide blades can be fixed along the diffuser or variable to match the shape of the rotor head.
• the height of the diffuser 7 is preferably substantially identical to that of the rotor head.
• the table below shows the properties of the broadcaster:
• a rectifier 8 having the role of guiding the discharge of the fluid by creating a laminar flow so as to eliminate turbulence. It is an open cylinder 8a on its base for receiving the fluid from the rotor 5 via the diffuser 7. It has an orifice 8b of smaller diameter than the diameter of the opening 8a on its base.
• Each blade 8c is a blade of width that is thicker on the side of the wall than on the side of the center of the cylinder. The width is thus refined away from the wall of the cylinder.
• the profile of the side facing the axis of rotation of the cylinder is curved, in particular in a circular arc, so that the guide blades are brought closer to each other. level of the orifice and are further away from the side of the opening 8a.
• a variant of the rectifier can be concavely designed with blades that follow the concave inner part of the rectifier and whose thickness widens towards the end 8b linearly. This variant allows the rectifier to marry the shape of the portion 5h in Figure 4 or an ogive 24 'directly attached to the rotor of Figure 14 or the ogive 24 of the diffuser of Figure 12 according to another embodiment.
• the rectifier adapts to the shape of the head of the rotor and / or the diffuser used.
• the dimensions that can be adopted are shown in the table below:
• FIG. 1 a variant of the pump according to the invention.
• This variant is particularly suitable for effectively diffusing blood out of the pump.
• the peculiarity of this pump is its diffuser 22 disposed at the end of the active zone of the rotor 16 by means of a bearing 21.
• This feature is illustrated in FIG. 1 together with other components of the pump, these components being different from those described in the other figures but it is naturally possible to consider using the components already described to the extent that they are compatible with the present feature.
• turbine box 12 which is a cylindrical piece with side openings 13 for the admission of blood.
• This turbine box 12 can be designed either in a single room that includes the inductor or this box can be created in two separate parts to which the inductor can be added. In other words, there may be only one room or three separate rooms such that the lower portion 14 which comprises the portion 13, the inductor and the portion 15 as shown in Figures 5, 6 and 7.
• the side openings 13 can distinguish an upper part 15 of the box higher than a lower part 14.
• the upper part 15 is hollow to receive the rotor 16 and its drive shaft 17.
• the latter is intended to pass through the lower portion 14 at its center to a motor 10a.
• the motor 10a holds the drive shaft 17 which passes through the entire lower portion 14 to the rotor 16 and to which it is firmly fixed to drive it in rotation.
• the motor 10a may be partially or totally integrated at the end of the lower portion 14, but it may also be disposed outside.
• a seal 11 is provided inside the lower portion 14 for sealing between a bearing 10b, the motor 10a and the blood. In all cases, this seal 11 is located before the part 13 and after a bearing 10b which is not shown here and which serves to guide the drive shaft 17.
• This bearing 10b can be located in the lower part 14 or in the engine 10a.
• the upper part 15 is long enough to accommodate in addition to the rotor 16, the bearing 21, the diffuser 22 and the rectifier 26, these elements being connected in series.
• the rotor 16 consists of a flared central body 19 around which are wound four helical blades 18 over the entire length of the central body.
• the rotor head is cut flat, only an axis 20 protrudes.
• the axis 20 is a male rod sized to receive the bearing 21 as a female element.
• the outer ring of the bearing 21 is mounted tightly in the housing 29 of Figure 13 of the diffuser 22 itself fixed inside the part 15 of the box 12.
• the axis 20 of the rotor 16 is slidably mounted in the inner ring of the bearing 21 thus allowing the rotation of the rotor in the same way as the bearing 10b of the motor 10a.
• the rectifier 26 is fixed in the upper part 15 of the box 12, in the same way as the diffuser 22. It is a hollow cylinder with straight blades arranged radially. When the pump is fully assembled, the rectifier 26 is flush or recessed (inside) from the end of the top 15. The assembly with the motor is less than 100mm in length.
• the motor 10a of "brushless” type rotates the assembly 16 which is composed of parts 17 to 20.
• the blood enters through the openings 13, then passes through an inductor (not shown) disposed inside the box 12.
• This inductor may be in the form of several blades of straight guides radially fixed to the inner wall of the box 12, "at the foot” of the upper part 15.
• the blood is sucked by the rotor 16 and passes all around the drive shaft 17 as a linear flow.
• the blood is then driven by the rotor while rotating into the diffuser which carries blades twisted in the opposite direction to the direction of the helical blades.
• the flow of blood stops rotating and is then straightened through the rectifier 26 which through its outlet creates a laminar flow of high pressure.
• the pump is designed to operate in immersion at a frequency ranging from 500 to 10,000 rpm.
• FIGs 11b and 11c there is the interior of the turbine box 12 shaped to accommodate the different components.
• the upper portion 15 has an inside flared shape that marries, without touching, the outer shape of the rotor 16.
• the blades 27 are directly formed on the inner wall of the box, thus forming an inductor at the upstream end of the upper part 15
• the openings 13 are directly made in the box so that only blades 28 are left inscribed in planes that compete with the axis of revolution of the box.
• the drive shaft 17 is provided along the axis of revolution of the box as can be seen in Figure 11b.
• the fluid is intended to penetrate radially through the openings 13 and to be driven all around the drive shaft 17 towards the rotor, between the helical blades, through the diffuser 22.
• the blades of the rectifier can also be directly made on the inner wall at the downstream end of the upper part 15.
• FIGS. 11b and 11c are variants for which the inductor and the rectifier are directly made in the box.
• the dimensions of the rotor can be as shown in the table below.
• the angles of attack and exit of the blood in the rotor are such that the blood is propelled at the inlet by a centrifugal force, and is released at the output by an axial force, the central zone of the rotor being similar to a mixed force.
• the height of the helical blade (its thickness in the radial direction) can vary, for example decrease between the bottom and top of the rotor.
• the lateral thickness of the helical blade can also vary, for example grow between the bottom and the top of the rotor.
• the height "a" and the lateral thickness "b" are schematically represented in FIG. 14. The same dimensions can be applied for the different embodiments.
• FIG. 12 is shown in more detail a diffuser 22 according to the invention. It is composed of a cylinder 23 connected to a warhead 24 by twisted blades 25. In FIG. 13 one can see the rear of the diffuser 22. It is noted that the nose 24 has on its rear face the housing 29 designed to receive the bearing 21 and the axis 20.
• the diffuser consists of a cylinder like the cylinder 23 but with twisted blades only fixed to these cylinders and allowing the passage of the warhead with a margin thickness to avoid any friction.
• FIG. 16 and 17 there is a schematic representation of an inductor 34 in Figure 16 and a schematic representation only of the blades 35 of this inductor in Figure 17.
• This inductor can be individually designed. It will then be firmly fixed in an intake chamber. It can also be directly carried out in an intake chamber or in a turbine box; in this case it is the blades that are made on the inner wall of the inlet chamber or the turbine box.
• the central zone of the inductor is left free for the passage of the fluid. In FIG. 17, the central zone of the inductor represents the fluid flow.
• the blades of the inductor according to the invention are thicker upstream than downstream in the direction of movement of the fluid.
• the progression of the thickness may be linear, but preferably discontinuous: a linear progression until reaching a certain thickness, then the thickness remains constant over the rest of the length of the blade.
• the blades can also be thicker at the point of connection with the cylinder 36 which carries them than at the central end. An angle is also provided between the radial section of each blade and the radius of the cylinder 36 carrying the blades.
• FIG. 20 is a sectional view of a blade on which various design parameters are illustrated. The definitions of the various parameters are illustrated by the figure below: There is a blade 37 on which a leading edge is defined
• leading edge (inlet) and a trailing edge (outlet).
• entry zone For the entry zone:
• Vi velocity of the fluid after contact with the blade (exit velocity / final velocity)
• Wi velocity of the fluid before contact with the blade (speed of entry / initial velocity)
• Vui projection of the velocity vector VI on the Ui axis
• Vai Projection of Vi and Wi on the axis defined by the axis of the turbine
• ⁇ angle between the vector Wi and the axis of the turbine
• ⁇ angle between the vector Vi and the axis of the turbine
• V 2 velocity of the fluid after contact with the blade (exit velocity / final velocity)
• W 2 velocity of the fluid before contact with the blade (entry speed / initial velocity)
• V U2 projection of the velocity vector V 2 on the U axis 2
• V a2 Projection of V 2 and W 2 on the axis defined by the axis of the turbine
• ⁇ 2 angle between the vector W 2 and the axis of the turbine
• ⁇ 2 angle between the vector V 2 and the axis of the turbine
• V m velocity of the fluid after contact with the blade (speed of exit / final speed)
• W m velocity of the fluid before contact with the blade (entry speed / initial velocity)
• Sets U, V and W constitute flux velocity triangles and serve as a reference for the definition of velocity vectors and angles 3 m and Q m , where m is equal to 1 for the reference whose origin has been moved to leading edge, and 2 for the marker whose origin has been moved to the trailing edge.
• the dotted line represents the axial direction.
• FIGs 18 and 19 illustrate a front view and a rear view of a rectifier according to the invention.
• This rectifier can be made individually and then fixed in the housing of the pump or directly on the inner wall of the housing, that is to say a wall identically shaped to the inner wall of the cylinder 30 of the rectifier and blades designed directly on this wall.
• the blades 31 are thicker upstream than downstream in the fluid flow direction. The progression of the thickness can be linear.
• Figure 18 is illustrated the downstream side of the rectifier, that is to say the place where the fluid comes out.
• Figure 19 is illustrated the upstream side of the rectifier, the fluid inlet. On the latter side, the blades 31 leave a central space larger than the downstream side, the blades and the inner wall 32 of the cylinder 30 carrying the blades being designed to guide the fluid to the outlet port 33 which is more narrow as the entrance of the straightener.
• the pump according to the invention can easily be implanted in a heart by its small size because of its particular design allowing high pressure while maintaining the quality of the blood.
• the pump according to the invention consumes little because it operates according to the physiological heart rate: an oscillating flow.
• the pump according to the invention operates by propelling: the rhythm is pulsed.
• the pump according to the invention is advantageously designed to operate vertically, the rotor being arranged vertically, the fluid enters via the inductor, passes through the rotor and then emerges from above via the diffuser and the rectifier.
• Most pumps of the prior art operate horizontally. It is the intake and discharge capacity that allows the vertical operation of the pump according to the invention.
• Such a pump, placed in a left ventricle for example has the advantage of having an inlet and an outlet directly in this ventricle. This makes it possible to avoid the presence of an inlet and / or outlet tube as it exists on the other devices of the prior art.

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• 2015
  • 2015-08-25 FR FR1557893A patent/FR3040304B1/fr not_active Expired - Fee Related
• 2016
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