Blood pump for mechanical circulatory support in Fontan patients

Abstract

The present invention relates to a radial blood pump (1) for supporting a blood flow (106) in a heart (205) of a human or animal, the radial blood pump comprising a first inlet channel (41) and a second inlet channel (42), a first outlet channel (51, 52), a first electric motor (71), a plurality of blades (20), the first electric motor comprising a first stator (77) and a first internal rotor (75), wherein the first electric motor (71) is configured to drive an impeller (2, 2a, 2b) arranged at an intersection of the first inlet channel (41) and the second inlet channel (42), wherein the impeller (2, 2a, 2b) is connected to the first internal rotor (75), and the impeller (2, 2a, 2b) comprises a merging portion (22) arranged at the intersection, at which the first blood flow (106) from the first inlet channel (41) is merged with the second blood flow (107) from the second inlet channel (42), wherein the impeller (2, The impeller (2a, 2b) is configured to pump a first blood flow (106) and a second blood flow (107) from a first inlet channel (41) and a second inlet channel (42) to a first outlet channel (51) via a merging portion (22), wherein the impeller (2, 2a, 2b) comprises a plurality of blades (20), wherein the blades (20) are formed with blade channels (21) included in the merging portion (22), wherein each blade (20) is arranged and configured to pump a first blood flow (106) and a second blood flow (107) from a first inlet channel (41) and a second inlet channel (42) to a first outlet channel (51). The first blood flow (106) and the second blood flow (107) entering the inlet channel (42) are pumped toward the outlet channel (51), wherein the blood pump (1) is arranged and constructed so that the first blood flow (106) and the second blood flow (107) meet at the merging portion (22), so that before the blood is pumped from the first blood flow (106) and the second blood flow (107) to the first outlet channel (51), the pressure difference between the first blood flow (106) and the second blood flow (107) is reduced.

Description

Technical Field

[0001] The present invention relates to a blood pump for a human or animal heart, in particular to a pump for assisting Fontan circulation in a cavopulmonary position, and to a system comprising the blood pump.

[0002] The invention also relates to a method for regulating a blood pump rate based on a measured or estimated hemodynamic signal. Background Art

[0003] In the United States and Europe, approximately 1% of all live births are born with congenital heart defects. Approximately 5% to 10% of these patients have hypoplastic left or right ventricle; therefore, the patient's circulatory system includes only one functional ventricle. Because arterial oxygen saturation is low in this configuration and the single ventricle is permanently overloaded, lack of treatment will inevitably lead to the patient's death.

[0004] The only two treatment options are heart transplantation or the creation of a so-called "Fontan circulation"[1],[2]. Although the availability of donor organs is limited, especially for children, the second option offers the prospect of conservative treatment with reported survival rates varying from less than 50% to less than 76% at thirty years[3],[4].

[0005] Mechanical circulatory support (MCS) devices therefore constitute the most promising approach for enhancing the function of the cardiovascular system in Fontan patients. Some MCS devices specifically designed for cavopulmonary support for Fontan circulation have been proposed in the literature [5] to [7].

[0006] Other clinically available approaches are left ventricular assist devices (LVAD) or right ventricular assist devices (RVAD), where the goal is to bridge the patient's time span to transplantation.

[0007] None of these methods constitutes an option for long-term treatment of Fontan patients due to their design, size, and / or invasiveness of these methods. Summary of the invention

[0008] The object of the present invention is to provide an MCS device for enhancing the cardiovascular system in Fontan patients. This object is achieved by a radial blood pump having the features of claim 1.

[0009] Advantageous embodiments are described in the dependent claims.

[0010] A radial blood pump according to claim 1 for supporting blood circulation in the heart of a patient, in particular a cardio-pulmonary assist device, comprising at least the following components:

[0011] - a first inlet channel and a second inlet channel, in particular arranged opposite to one another,

[0012] - first exit channel,

[0013] a first electric motor comprising a first internal rotor and a first stator, in particular arranged on the pump housing, wherein the first electric motor is designed to drive an impeller, wherein

[0014] - an impeller is arranged at an intersection of the first inlet channel and the second inlet channel, wherein the impeller is connected to the first inner rotor, wherein the impeller comprises a particularly open merging section arranged at the intersection, at which the first particularly venous blood flow from the first inlet channel merges with the second particularly venous blood flow from the second inlet channel, wherein the impeller is configured to pump the first blood flow and the second blood flow from the first inlet channel via the merging section, particularly towards a volute chamber or annular chamber, which is connected to the first outlet channel, wherein the outlet channel is arranged particularly in a tangential direction with respect to the rotation axis of the impeller,

[0015] - an impeller comprising a plurality of blades, wherein the blades are formed with a blade channel including at least a portion of a merging portion, wherein the blade channel is arranged between a pressure face of the blade and a suction face of the blade, wherein each blade is arranged and configured to pump a first blood flow and a second blood flow entering through a first inlet channel and a second inlet channel towards an outlet channel,

[0016] The radial blood pump is arranged and constructed so that the first blood flow and the second blood flow are combined at a merging portion, and in particular so that the pressure difference between the first blood flow and the second blood flow is reduced or equalized, in particular at the merging portion, before the blood of the first blood flow and the second blood flow is pumped into the first outlet channel.

[0017] The radial pump is specifically designed and constructed to assist the Fontan circulation in the cardiopulmonary position of the patient.

[0018] The merging section extends in particular symmetrically around a center point of the radial blood pump.

[0019] Due to the radial design of the pump, the pump can be connected to the superior vena cava (SVC) and the inferior vena cava (IVC) through the first inlet channel and the second inlet channel, while the first outlet channel can be connected to the pulmonary trunk or the left pulmonary artery and / or the right pulmonary artery. The radial design of the pump is particularly consistent with the venous and arterial anatomy of the entire cavopulmonary connection of Fontan patients.

[0020] Under healthy physiological conditions, the IVC and SVC discharge against the right atrium and therefore discharge at the same pressure. Right atrial pressure is an important determinant of venous return. Even in the case of highly unbalanced blood flow, equalizing the pump inlet pressures in the IVC and SVC may be critical to ensuring physiological perfusion of the upper and lower body. Since the blood flow at the IVC is usually slightly greater than the blood flow from the SVC, especially during physical activity, an important feature of the blood pump is to reduce or equalize the pressure difference between the SVC and the IVC in the merged portion of the impeller, especially to reduce or equalize the pressure difference between the SVC and the IVC before the blood is pumped toward the outlet channel.

[0021] In particular, the radial blood pump is configured to receive a first blood flow, in particular the IVC, through a first inlet channel and a second blood flow, in particular the SVC, through a second inlet channel, wherein the pressure of the first blood flow is greater than the pressure of the second blood flow, or the pressure of the first blood flow is less than the pressure of the second blood flow, such that pressure equalization between the two blood flows occurs at a merging portion of the pump. In particular, the pump is configured such that the first blood flow and the second blood flow, in particular first merge at a merging portion of the blood pump, wherein at the merging portion, any pressure difference between the first blood flow and the second blood flow is reduced or equalized, and in particular, wherein after the blood flows have merged, the blood is pumped through the outlet first channel.

[0022] Furthermore, due to the blood flow combining before or while pumping the blood towards one or more outlet channels, in particular all blade channels of the impeller carry the combined blood flow of the first inlet channel and the second inlet channel, i.e. the pump in particular does not have different blades which are specifically constructed and arranged on the impeller for pumping the blood flow of the first inlet channel or the second inlet channel.

[0023] A disadvantage of the latter configuration providing different blades for pumping blood from the first or second inlet channel is that the pressure difference is mainly maintained and may cause an overpressure in the IVC or an underpressure in the SVC depending on the pump rate.

[0024] An additional advantage of this design is that the asymmetric forces acting on the impeller due to possible blood pressure differences are greatly reduced. The design with two outlet channels, especially the design with two volute tongues, reduces radial forces, and the symmetrical inlet design with two inlet channels reduces axial thrust.

[0025] Furthermore, the pump is designed as an internally running part, as opposed to an externally running part. The rotor of an externally running pump is driven by the force generated by magnets or coils, which are arranged on the part of the pump surrounded by the rotor. An internally running pump provides the driving force by magnets or coils arranged around the rotor, usually on the housing of the rotor. The pump according to the invention is an internally running pump, which is reflected by the term "internal rotor".

[0026] Externally operated pumps generally allow for a more compact design, however, the efficiency of externally operated pumps is generally lower, and therefore, externally operated pumps generate more heat, which is dissipated to the blood pumped by the pump. As a result, the temperature of the pumped blood increases due to the heat dissipation of the pump, and the likelihood of forming a thrombus (also called a clot) increases dramatically.

[0027] For pumps located in a cardiopulmonary position, a particular challenge arises from floating thrombi that originate from the venous system that the pump must withstand. Recent clinical experience with the HeartMate III [8] suggests that large flow channels and a small amount of leading edge may prevent pump thrombosis by allowing thrombi to travel through the pump rather than becoming trapped within the device. Pumps with small clearances, such as pumps with hydrodynamic bearings, and structures like flushing ports may be disadvantageous in this regard. The proposed motor and pump design promotes the use of larger clearances.

[0028] The configuration of the pump according to the invention as an internally running pump therefore reduces the risk of clot formation and thus also reduces the risk of pump blockage due to clots.

[0029] In particular, the first stator is arranged at a pump housing which accommodates the first inner rotor. The first electric motor in particular comprises a coil and a permanent magnet.

[0030] According to an embodiment of the invention, the magnets are in particular arranged on the first rotor and the coils are arranged on the first stator around the first inner rotor.

[0031] The impeller is connected to the first inner rotor by means of a rigid connection, wherein the connection can be realized, for example, by an integrally formed component comprising the impeller and the first inner rotor. However, the impeller can also be connected to the rotor by means of a connection means, thereby essentially forming a two-piece device with a rotor and an impeller connected to the rotor.

[0032] An intersection is formed where the first inlet channel and the second inlet channel meet. Likewise, the first outlet channel is arranged at the intersection. The first outlet channel extends in particular radially relative to the rotation axis of the impeller.

[0033] To provide pressure equalization, the radial blood pump comprises a merging portion configured to combine a first particular venous blood flow from the first inlet channel and a second particular venous blood flow from the second inlet channel, particularly before or while the blood is pumped by the pump blades towards the first outlet channel.

[0034] The blades can have a variety of shapes and profiles, depending on the specific design of the impeller.

[0035] According to another embodiment of the invention, the blades are arranged in a single plane, wherein the plane is arranged symmetrically between the first channel and the second channel.

[0036] This embodiment allows pumping of blood from both the first and second inlet channels.

[0037] The blades in particular have a pressure side and a suction side which are subject to different pressure conditions during pumping.

[0038] The pressure side "pushes" the blood, while the suction side is the side of the blade that is oriented specifically opposite to the pressure side. Since the impeller accelerates the blood, a pump effect occurs.

[0039] Depending on the specific design of the impeller, in particular whether the impeller is an open impeller or a closed impeller, the merging section particularly comprises a blade channel. When the impeller is an open impeller, the merging section particularly comprises a blade channel.

[0040] In case the impeller is a closed impeller or a semi-closed impeller, the merging portion may also comprise the eye of the impeller.The blood flows are combined in the blade channels and / or in the eye of the impeller and in particular mixed before or while the blood is pumped towards the outlet channel.

[0041] According to another embodiment of the present invention, a radial blood pump is configured to support a Fontan circulation at the cavopulmonary junction of a patient.

[0042] According to another embodiment of the invention, the radial blood pump comprises a second electric motor comprising a second stator and a second inner rotor rigidly connected to the first inner rotor.

[0043] The second motor provides redundancy with respect to motor failure of the first motor. Even if the first electric motor fails to work, the second electric motor is able to maintain the pumping of blood, so that a critical situation for the patient is avoided.

[0044] Furthermore, the second electric motor can be arranged at a different mounting position of the pump and thus the dissipated heat from the blood pump is distributed elsewhere within the blood pump, thereby reducing the risk of critical temperature rise of the pumped blood relative to blood damage and clot formation.

[0045] The first and second motors are in particular arranged offset along the rotation axis of the impeller, wherein the first electric motor is in particular arranged closer to the first inlet channel than the second motor and the second electric motor is in particular arranged closer to the second inlet channel than the first motor.

[0046] Furthermore, the first motor and the second motor are particularly designed and arranged symmetrically with respect to the rotation axis of the impeller, so that the generated magnetic force can be reduced or ideally balanced.

[0047] The second inner rotor is in particular formed integrally with the first inner rotor.

[0048] The second stator is in particular formed integrally with the first stator.

[0049] It is to be noted that the two motors are particularly rigidly connected to one another, for example by means of a pump housing and a shaft, and that in particular both motors drive the same blades of the impeller.

[0050] However, each motor includes its own set of coils and magnets for providing the driving force.

[0051] The second electric motor may be designed identically to the first electric motor, in particular wherein the second rotor may be formed integrally with the impeller, or may be essentially a two-piece arrangement, wherein the rotor and the impeller are connected to each other by means of a connecting means.

[0052] According to another embodiment of the invention, a first electric motor is arranged in a first half-space, which extends from a plane extending orthogonally to the rotation axis of the impeller and includes a first inlet channel, and wherein a second electric motor is arranged in a particularly complementary second half-space, which extends from said plane and includes a second inlet channel.

[0053] This embodiment allows for better heat distribution and promotes a symmetrical pump design allowing for symmetrical forces.

[0054] This embodiment reduces wear and tear and allows reduced energy consumption due to symmetrical load distribution.

[0055] Furthermore, this embodiment reduces the design constraints on the stator topology of the pump, since in particular the coils can be arranged along the inlet channel, which results in a space-efficient design.

[0056] According to this embodiment, the rotors and stators of the first motor and the second motor are arranged in corresponding half-spaces, in particular on both sides of the impeller, for example above and below the impeller.

[0057] According to a further embodiment of the invention, the impeller is a double-suction impeller, in particular without a separating mid-plane, wherein the impeller is in particular a symmetrical double-suction impeller.

[0058] A double suction impeller allows two opposite inlet channels to be provided.A double suction impeller allows a symmetrical distribution of the forces on the impeller, thereby in particular reducing the forces on the magnetic bearing or in particular reducing wear and tear on the mechanical bearing.

[0059] The double suction impeller is configured to receive blood flow from both sides of the impeller mid-plane, in particular from two inlet channels.

[0060] According to another embodiment of the invention, the impeller is a closed double-suction impeller, wherein the impeller comprises a first shroud and a second shroud at least partially covering the blades and in particular covering the blade channels, and wherein the merging portion comprises two opposite eye-shaped portions, in particular wherein the diameter of each of the two eye-shaped portions is greater than 2.5 mm, and more particularly greater than 7 mm.

[0061] According to this embodiment, the merging portion comprises the eye and / or blade channel of the impeller, so that a particularly effective merging and particularly mixing of the blood flows from the first and second inlet channels is achieved before or while the blood flows are pumped from the first and second inlet channels towards the outlet channel.

[0062] An impeller eye with a diameter greater than 2.5 mm and more particularly greater than 7 mm avoids pressure losses before the two inlet flows meet and avoids clogging of the pump due to clots.

[0063] According to a further embodiment of the invention, the first inner rotor of the first electric motor is arranged on the first shroud, and in particular wherein the second inner rotor of the second electric motor is arranged on the second shroud.

[0064] This embodiment allows for better heat dissipation even if the two inlet flows are severely unbalanced, while the symmetrical layout reduces wear and tear on the pump.

[0065] The temperatures generated in the motor and the support affect the blood compatibility of the blood pump. Compared to conventional blood pumps, cooling of the motor area is challenging due to the smaller pressure head in the main operating state. In order to promote sufficient auxiliary flow, a large fluid gap is inevitable. In the mentioned pump, the dual motor configuration allows a fluid gap greater than 0.5 mm at an acceptable temperature increase and even at higher flow rates.

[0066] According to a variant of the invention, the impeller is an open impeller without shroud, in particular a double suction impeller, wherein the blades project from a shaft extending along the rotation axis of the impeller, wherein the shaft comprises a first internal rotor of the first electric motor and / or a second internal rotor of the second electric motor.

[0067] Although open impellers are generally less efficient than closed impellers, they are better suited for pumping blood that includes clots because they provide fewer adhesion points for blood to attach to, potentially leading to clot buildup and the risk of pump clogging. Open impellers are less complex in structure and flow than closed impellers.

[0068] The merging part of the open impeller comprises in particular the blade channels.

[0069] According to another embodiment of the invention, the first internal rotor of the first electric motor is arranged on a first portion of the shaft in a first half-space extending from a plane extending orthogonally to the axis of rotation of the impeller, the first half-space comprising a first inlet channel, and wherein the second internal rotor of the second electric motor is arranged on a second portion of the shaft in a second particularly complementary half-space extending from said plane such that the second half-space comprises a second inlet channel.

[0070] According to this embodiment, when a large amount of dissipated heat is distributed approximately equally to the first inlet channel and the second inlet channel, the inflowing venous blood can be used to cool the first electric motor and the second electric motor, which ensures that the blood temperature does not exceed a critical temperature compared to a single motor design.

[0071] According to another embodiment, the gap between the shaft and the first stator and / or the second stator is greater than one millimeter, wherein the blood flows through the gap when being pumped by the pump.

[0072] This relatively large gap reduces the motor efficiency, but reduces the pressure loss before the two inlets merge and allows clots included in the blood to be pumped without the risk of pump clogging. Furthermore, according to another embodiment of the present invention, the gap between the first rotor and / or the second rotor and in particular all rotating pump parts, and the gap between the first stator and / or the second stator and in particular the inner wall of the pump housing is greater than 1 mm.

[0073] According to another embodiment of the present invention, the first inlet channel and the second inlet channel are arranged opposite to each other, in particular, arranged opposite to each other along the rotation axis of the impeller, and wherein the blades are configured so that a blade channel through the impeller and / or a straight fluid channel through the eye of the impeller is provided and maintained between the first inlet channel and the second inlet channel, so that the pressure difference between the first blood flow and the second blood flow is reduced or ideally equalized before the first blood flow and the second blood flow are pumped to the first outlet channel.

[0074] The pump comprises a straight fluid channel, in particular in a cross-sectional view along the axis of rotation a straight line can be drawn between the first inlet channel and the second inlet channel, wherein this line is not blocked by components of the pump, in particular the impeller.

[0075] The straight channel may, for example, extend through a blade channel of an impeller or through the eye of a closed impeller.

[0076] Such straight channels allow the flows to merge before or while the blood is pumped from the first and second inlet channels toward the outlet channel.

[0077] Additionally, the pump is less susceptible to blockages due to clots in the blood.

[0078] If the impeller is an open impeller, the straight channel is located, for example, along a gap between the first rotor and / or the second rotor and the inner wall of the pump housing.

[0079] If the impeller is a double suction closed impeller, a straight channel extends through the eye of the impeller, ie if the pump is not functioning properly, blood may flow in a straight line from the first inlet channel to the second inlet channel, even though this is not ideal.

[0080] It is to be noted that when the first rotor and / or the second rotor rotates, the linear channel also rotates, in particular around the rotation axis of the impeller.

[0081] The rectilinear fluid channel is in particular cylindrical in shape.

[0082] The straight fluid channel extends in particular parallel to the axis of rotation of the impeller.

[0083] According to another embodiment of the present invention, the radial blood pump has a housing including a first stator and / or a second stator, the housing enclosing at least the following components:

[0084] a) Impeller;

[0085] b) a first inner rotor and / or a second inner rotor;

[0086] In which, in the entire blood pump, the distance between the inner wall portion of the shell and the said component is at least 0.25 mm, preferably at least 0.5 mm, so as to promote proper flushing to prevent thrombosis, venous clots will not block the blood pump, and the heat loss generated by the motor will be fully eliminated.

[0087] According to another embodiment of the invention, the blood pump comprises an active magnetic support, in particular a first motor and / or a second motor of a bearingless type, or wherein the blood pump comprises a mechanical support particularly arranged at the inlet of the first inlet channel and / or the second inlet channel, so that venous blood can be used to cool the support.

[0088] The magnetic bearing comprises in particular magnets and control coils and sensors for estimating / measuring the position of the rotor in at least one direction. The bearing position is adjusted according to the sensor data.

[0089] The advantage of a magnetic bearing is that it is contactless and no frictional heat is generated at the bearing. This comes at the expense of increased space requirements for the pump.

[0090] Alternatively, the blood pump may include a mechanical support. Although the rotating mechanical support generates frictional heat and although the mechanical support is subject to wear and tear, the space requirement is small and the components of the mechanical support do not require additional power. The mechanical support in the blood pump dictates an acceptable wear without disturbing the flow field [9] and a well-flushed design, which will minimize the risk of heat and thrombosis even under off-design conditions: the support structure is located at a large distance from the impeller inlet area, making the flow field around the support much smoother than, for example, the flow field in the mechanically supported HeartMate II (Abbott, Chicago, IL, USA).

[0091] According to another embodiment of the present invention, the blood pump comprises a second outlet channel, and the blood flow can be pumped from the first inlet channel and / or the second inlet channel to the second outlet channel through the impeller, in particular wherein the second outlet channel is arranged along a tangential direction relative to the impeller, in particular along a radial impeller plane, in particular wherein the second outlet channel points in a direction opposite to the first outlet channel.

[0092] All embodiments concerning the first outlet channel and all advantages associated with the pump concerning the first outlet channel apply in an analogous manner to the second outlet channel.

[0093] The second outlet channel has in particular the same dimensions and the same shape as the first outlet channel.

[0094] This embodiment allows the blood flow to be distributed in both vessels and reduces the radial forces on the impeller and, therefore, on the support.

[0095] The first outlet channel and the second outlet channel are in particular connected to the left pulmonary artery and the right pulmonary artery.

[0096] Furthermore, the problem according to the invention is solved by a system having a blood pump according to the invention and a device for power transmission, such as wire-constrained or inductive transcutaneous power transmission, wherein the system further comprises a sensor for measuring and / or estimating a hemodynamic signal and a controller configured to adjust the pumping rate of the blood pump depending on the hemodynamic signal, wherein the sensor is in particular a pressure sensor arranged at the blood pump, or wherein the sensor can be arranged in a cardiovascular system, which sensor is suitable for measuring and / or estimating the blood pressure in a blood vessel or the pressure difference between two chambers or the pressure difference between at least one inlet and one outlet within the entire pump.

[0097] The system allows the blood pump rate to be adjusted based on the determined pressure, in particular the pressure differential. Such a system allows a response to the changing needs of cardiac output and therefore the patient's oxygen consumption. For example, a lower heart rate output is required when the patient is sleeping than when the patient is physically active and the body requires a higher heart rate output. Thus, the system regulates the blood flow rate by keeping the pressure in the IVC / SVC or the pressure differential across the pump or the pressure differential between the IVC and the atria of the system constant or within a predetermined range.

[0098] To regulate the pump rate, the sensor specifically measures the blood pressure in the blood vessels, which can be used as an indicator of the actual heart rate output requirements of the body.

[0099] However, other hemodynamic signals may also be sensed by the pressure sensor and used to adjust the pump rate, such as, for example, the heart rate or the pump flow rate.

[0100] Typically, the blood pump requires an external power source near the patient's body. If the system is a wire-constrained system, power is transmitted from the power source to the blood pump via a percutaneous access via a cable through a device for power transmission, making the system inconvenient and not prone to inflammatory diseases at the percutaneous access.

[0101] The power source is for example a wearable battery pack. The system particularly also includes a wearable power source.

[0102] Due to the low power requirements for the radial blood pump in the cavopulmonary position, the system can be fully implantable, particularly in the case of transcutaneous energy transfer including an implantable battery.

[0103] Furthermore, the problem according to the invention is solved by a system having a blood pump according to the invention and a device for power transmission, such as wire-constrained or inductive transcutaneous power transmission.

[0104] According to another embodiment of the present invention, a device for power transmission is configured to wirelessly transmit power to a blood pump, wherein the power transmission device includes a power receiver and a power transceiver, wherein the power receiver is electrically connected to the blood pump in the patient's body and is configured to provide the blood pump with electrical energy transmitted from the power transceiver to the power receiver, wherein the power transceiver is specifically located outside the patient's body.

[0105] Wireless power transmission eliminates the need for percutaneous access, thereby reducing the risk of inflammation and allowing for greater flexibility in terms of ease of maneuverability of the system.

[0106] Additionally, the system's controller for regulating the pump rate may also be disposed external to the patient's body, thereby reducing the need to deliver additional power into the patient's body.

[0107] Furthermore, the problem of the invention is solved by a method for regulating the rate of a blood pump according to a hemodynamic signal using a system according to the invention, the method comprising the following steps:

[0108] - evaluating, in particular measuring, a hemodynamic signal of a patient in which a radial blood pump has been implanted, in particular wherein the hemodynamic signal is an inlet channel pressure at least at a first inlet channel and / or a second inlet channel and / or at least one outlet channel pressure at a first outlet channel and / or a second outlet channel, or wherein the hemodynamic signal is a pressure difference between an atrium and the inferior vena cava of the heart, or wherein the hemodynamic signal is a pressure difference between at least one of the inlet channels, namely the first inlet channel and / or the second inlet channel, and one of the outlet channels, namely one of the outlet channels being the first outlet channel and / or the second outlet channel;

[0109] - determining a required pump output rate for the blood flow of the first output channel and / or the second output channel based on the hemodynamic signal, in particular determining a required pump output rate for the venous blood flow entering through the first inlet channel and the second inlet channel based on the hemodynamic signal;

[0110] - regulating the blood pump, in particular regulating the pump speed of the blood pump, such that a determined pump output rate is achieved, in particular such that the hemodynamic signal remains within a predetermined range.

[0111] In particular, the blood pump is adjusted so that at least one inlet channel pressure (for example, at the first inlet channel and / or the second inlet channel) or the pressure difference between the atrium of the heart and the inferior vena cava or the pressure difference between at least one of the inlet channels and one of the outlet channels is maintained within a predetermined range, that is, at least one of the inlet channels is the first inlet channel and / or the second inlet channel, and one of the outlet channels is the first outlet channel and / or the second outlet channel.

[0112] The pump output rate is in particular the blood flow, in particular the blood flow in terms of the volume of blood pumped per time unit.

[0113] According to another embodiment of the method, the pressure difference of the cardiovascular system is estimated from a hemodynamic signal sensed by a pressure difference sensor of the system.

[0114] According to another embodiment of the invention, the system further comprises a processing unit for processing sensor data of the system.

[0115] According to a further embodiment of the method, the processing unit provides a mean pressure difference signal.

[0116] According to a further embodiment of the invention, a controller of the system receives a controller signal, wherein the controller signal comprises information about a deviation from a target pressure, in particular a target pressure difference, and an estimated pressure, in particular an estimated pressure difference.

[0117] According to another embodiment of the invention, the radial blood pump is a pump for supporting a Fontan circulation at the cavopulmonary junction, in particular a Fontan pump.

[0118] According to another embodiment of the invention, a radial blood pump provides particularly beneficial fluid dynamics over a wide range of operating conditions, which are achieved by well-directed flow and avoidance of any stagnant and recirculation areas within the pump.

[0119] According to another embodiment of the invention, the radial blood pump comprises an annular chamber, in particular instead of an actual volute casing.

[0120] This allows a wide operating range of the pump. In particular, the shear stress is lower than in conventional rotary blood pumps, thus ensuring low blood damage characteristics. The hydraulic characteristics of the pump indicate a pressure-sensitive characteristic (typical slope is 2 mm / Hg to 5 mm / Hg (L / min). This flat pressure-flow relationship (HQ curve) ensures an inherent adaptability of the pump output to changes in venous return

[10] , especially in cases where automatic speed adaptation achieved by a physiological control algorithm is not anticipated. BRIEF DESCRIPTION OF THE DRAWINGS

[0121] In the following, the present invention is described in detail with reference to the exemplary embodiments shown in the accompanying drawings. It should be noted that the drawings are not necessarily to scale. In the accompanying drawings:

[0122] Figure 1 is a cross-sectional view of a radial blood pump having an open impeller and a mechanical support according to the present invention;

[0123] Figure 2 is a perspective view of a radial blood pump having an open impeller and a mechanical support according to the present invention;

[0124] Figure 3 is a cross-sectional view of a radial blood pump having an open impeller and an incorporated magnetic support according to the present invention;

[0125] Figure 4 is a cross-sectional view of a radial blood pump having an open impeller and a free-standing magnetic support according to the present invention;

[0126] Figure 5 is a cross-sectional view of a radial blood pump having a closed impeller and a mechanical support according to the present invention;

[0127] Figure 6 is a cross-sectional view of a radial blood pump having a closed impeller and a separate magnetic support according to the present invention;

[0128] Figure 7 is a cross-sectional view of a radial blood pump having a closed impeller and an incorporated magnetic support according to the present invention;

[0129] Figure 8 is a cross-sectional view of a radial blood pump having a closed impeller and a separate magnetic support according to the present invention;

[0130] Fig. 9 is a flow profile through a radial blood pump with a closed impeller according to the invention;

[0131] Fig.10 is a system according to the present invention having a blood pump and a pressure sensor; and

[0132] Fig.11 is a schematic flow chart of a method for controlling with a system according to the invention. DETAILED DESCRIPTION

[0133] Figures 1 to 9 Various views and embodiments of a radial blood pump 1 are shown. In all described embodiments, the blood pump 1 is designed symmetrically with respect to a center point 100 where a vertical axis 101 and a horizontal axis 102 intersect, or the blood pump 1 is designed symmetrically with respect to a radial plane 103 extending orthogonally to the vertical line 101 and including the horizontal line 102. The vertical line 101 corresponds to the rotation axis 104 of a single impeller 2 arranged in the housing 3 of the blood pump 1.

[0134] The symmetrical pump design, in particular the oppositely arranged inlet channels 41 , 42 and the oppositely arranged outlet channels 51 , 52 , reduces the hydraulic force acting on the impeller 2 and thus on the bearing 60 .

[0135] The radial plane 103 divides the space into a first half space S1 including the first inlet channel 41 of the pump 1 and a second half space S2 including the second inlet channel 42 of the pump 1 .

[0136] The first inlet passage 41 and the second inlet passage 42 are arranged opposite to each other and form straight pipes.

[0137] When radial blood pump 1 is implanted in a patient, first inlet channel 41 is connected to superior vena cava 200 , while second inlet channel is connected to inferior vena cava 201 .

[0138] The blood flow 200 entering the radial blood pump 1 is depicted by arrows.

[0139] The impeller 2 of the radial blood pump 1 rotates about an axis of rotation 104 and is centered on a center point 100. In the embodiment shown, the pump 1 always comprises two outlet channels 51 , 52 which are arranged on opposite sides pointing in a radial direction of the radial blood pump 1 .

[0140] The first outlet channel 51 and the second outlet channel 52 extend tangentially with respect to the impeller 2 .

[0141] The impeller 2 is driven by a first electric motor 71 and a second electric motor 72 , wherein in the embodiment shown, the first electric motor 71 is arranged in the first half space S1 and the second electric motor 72 is arranged in the second half space S2 .

[0142] The impeller 2 is designed as a double-suction impeller 2 which comprises a plurality of blades 20 which form blade channels 21 through which the blood is pumped towards at least one outlet channel 51 , 52 .

[0143] The first electric motor 71 and the second electric motor 72 include a motor coil 73 and a motor magnet 74 , and are brushless DC motors, thereby facilitating contactless actuation and requiring less maintenance.

[0144] The motor coil 73 is arranged in the housing 3 of the pump 1 and can be connected to a power supply and a controller (not shown) that controls the motor speed. Therefore, the housing 3 includes or can be considered as a first stator of the first electric motor 71 and a second stator of the second electric motor 72, respectively.

[0145] The motor magnets 74 of the first motor 71 and the second motor 72 are arranged on the first rotor 75 and the second rotor 76 of the first motor 71 and the second motor 72 , respectively.

[0146] The first rotor 75 and the second rotor 76 are rigidly connected or coupled to each other so that the first motor 71 and the second motor 72 always rotate at the same speed.

[0147] The presence of two independently driven but synchronized electric motors 71, 72 with rigidly connected rotors 75, 76 provides a fail-safe option for the radial blood pump 1 in the event that one motor is damaged or otherwise impaired such that the motor cannot maintain the desired pump rate. In the event that one motor fails, the other motor is able to maintain the desired pump rate or at least an emergency pump rate for patient safety.

[0148] In general, all embodiments of the pump 1 have relatively large fluid channels 8 and gaps 9 for blood flow and thus provide relatively low resistance against floating thrombi.

[0149] Furthermore, the blood pump 1 is designed such that recirculation and stagnation of blood in the pump 1 is avoided. This can be achieved, for example, by opposite inlet channels 41, 42 and opposite outlet channels 51, 52, a properly designed flow path and a larger gap 9.

[0150] Since the pump 1 is designed to discharge well-mixed blood entering through the first and second inlet channels 41, 42 to the opposing outlet channels 51, 52, an ideal liver flow distribution is achieved, thereby preventing the collapse of the pulmonary vasculature.

[0151] exist Figure 1 and Figure 2 , an embodiment of a radial pump 1 comprising an open impeller 2a is shown. The radial blood pump 1 comprises a shaft 10 extending along the rotation axis 104 of the impeller 2a. The impeller 2a is integrally formed to the shaft 10 together with the blades 20. The shaft 10 comprises the motor magnets 74 of the first motor 71 and the second motor 72. Thus, the shaft 10 comprises the impeller 2a and the first rotor 75 and the second rotor 76.

[0152] A gap of at least 1 mm is maintained between all rotating parts, i.e. between the shaft 10 of all parts with the shaft 10 and the inner housing wall 30 of the radial blood pump 1, so that even clots can be pumped by the pump 1. The size of the gap 9 also prevents clots from sticking and forming in the pump 1.

[0153] The first motor 71 and the second motor 72 are cooled by the blood flowing through the respective inlet channels 41, 42. The heat dissipated by the motors 71, 72 causes the blood temperature to rise. Since clot formation depends inter alia on the blood temperature, it is advantageous if the first motor 71 and the second motor 72 are arranged along different inlet channels 51, 52 to avoid a temperature rise exceeding the critical clot formation temperature.

[0154] The shaft 10 of the radial blood pump 1 comprises a mechanical support 61 at an axial end of the shaft. The mechanical support 61 may be a ball-cup support comprising a ceramic, such as ruby.

[0155] The mechanical support 61 resists axial forces and also allows a small pump size. However, the mechanical support 61 generates additional heat and a disturbed flow field, both of which can lead to blood damage and clot formation. Materials with excellent tribological properties and high thermal conductivity limit wear to an acceptable level, thereby minimizing this risk, which is also reduced by a well-cleaned design. In addition, the mechanical support 61 is located at a relatively large distance from the impeller merging part 22 (here the blade channel 21), so that the flow field around the mechanical support 61 is smoother than, for example, in a mechanically supported HeartMate II (Abbott Company, Chicago, Illinois, USA).

[0156] exist Figure 3 In the figure, a similar Figure 1 and Figure 2 However, unlike Figure 1 and Figure 2 Compared to the radial blood pump 1 in FIG. 1 , the radial blood pump 1 does not include a mechanical support 61, but includes a magnetic support 62, so that the shaft 10 is kept on the central axis 101. Each stator 77, 78 includes a support coil 63 and a support sensor (not shown) placed around the axial flow path. The radial position control of the shaft 10 (and therefore the first rotor 75 and the second rotor 76) is performed by using the support coil 63 and the support sensor. The axial positioning of the shaft 10 is achieved by magnetic resistance.

[0157] In this example, the motor coil 73 and the support coil 63 are combined into one functional unit of a motor of the substantially levitating type. The magnetic support 62 operates in a contactless manner and shows no mechanical wear.

[0158] Figure 4 It shows that Figure 3 , however, where the magnetic bearing coils 63 and bearing magnets 64 are separate and distinct from the motor coils 73. In this embodiment, radial suspension is achieved in a passive magnetic (repelling magnets 64) manner. One or more control coils 63 control the rotor position in such a way that the axial magnetic force of the repelling bearing magnets acting on the impeller is always equal to the axial thrust and the rotor is suspended with minimal power requirements. (Zero force control). The reference numerals in all figures refer to functionally similar or identical devices and are therefore not repeated for each figure.

[0159] Figures 5 to 9 A radial blood pump 1 with a closed impeller 2b design is shown. Reference numerals from the previous figures apply, unless otherwise explicitly mentioned. The function and specific arrangement of the pump components have been explained above and apply analogously to the closed impeller design 2a, unless otherwise indicated.

[0160] exist Figure 5 In FIG. 6 , a radial blood pump 1 with a mechanical support 61 is shown.

[0161] Figure 5 A cross-sectional view of a pump 1 is shown.

[0162] The impeller 2 is a double suction closed impeller 2b, wherein the merging part 22 of the impeller 2b is located in the eye 23 of the impeller 2b and in the blade channel 21. The straight flow connection 105 between the first inlet channel 41 and the second inlet channel 42 is centrally located about the axis of rotation 104.

[0163] In an embodiment, a first motor 71 is arranged in the first half space S1, and a second motor 72 is arranged in the second half space S2. The motor coils 73 are arranged on respective first and second stators 77, 78 formed by the housing 3 of the pump 1. The closed impeller 2b has two shields 24 covering the blades 20. The blood from the first and second inlet channels 41, 42 flows through the eye 23 of the impeller 2b and is mixed at the central area of ​​the impeller 2b, the merging portion 22.

[0164] The impeller 2 b , in particular the shroud 24 of the impeller 2 b , accommodates the motor magnets 74 , 75 .

[0165] The closed impeller 2b is more efficient than an open impeller and allows nearly equal flow around the upper and lower motor areas in the auxiliary flow path even in the case of an inflow / outflow imbalance. In addition, the shroud 24 is beneficial in terms of blood damage compared to an open impeller.

[0166] Figure 6 A schematic cross section of a radial blood pump 1 with a closed impeller 2 b and a magnetic support 62 is shown.

[0167] The magnetic support 62 includes a support magnet 64, a support coil 63 and a support sensor (not shown). In this embodiment, radial suspension is achieved in a passive magnetic (attractive magnet) manner. One or more control coils control the rotor position in the following way: the axial magnetic force acting on the impeller to attract the support magnet is always equal to the axial thrust, and the rotor is suspended with minimal power demand. (Zero force control). The motor magnets 74 of the first motor 71 and the second motor 72 and the support magnet 64 are all placed in the shield 24 of the impeller 2b. Axial position control is achieved by using the support coil 63 and the support sensor (not shown). Radial positioning is achieved passively.

[0168] Figure 7 An embodiment is shown with a magnetic support 62 merged with an electric motor 71, 72 (axially suspended motor), wherein the support 62 (and therefore the motor 71, 72) is arranged so that the axial position of the impeller 2b can be actively controlled, while the radial position of the impeller 2b is achieved passively (reluctance force). The motor magnet 74 and the support magnet 64 are merged and each formed as a single magnet.

[0169] Figure 8An embodiment is shown with a magnetic support 62 merged with an electric motor 71, 72 (axially suspended motor), wherein the support 62 (and therefore the motor 71, 72) is arranged so that the radial position of the impeller 2b can be actively controlled, while the axial position of the impeller 2b is achieved passively (reluctance force). The motor magnet 74 and the support magnet 64 are merged and each formed as a single magnet.

[0170] exist Fig. 9 , a flow profile of blood flowing through an operating radial blood pump 1 is shown. The radial blood pump 1 shown is a blood pump with a closed impeller 2b. In this embodiment, no supports are shown.

[0171] The arrows indicate the flow velocity in the pump 1 at the position of the arrows.

[0172] As can be seen, the merging portion 22 in the closed impeller 2b embodiment is located at the eye 23 of the closed impeller 2b and at the blade channel 20 in the central region of the impeller 2b.

[0173] Thus, the merging of the blood flows from the first inlet channel 41 and the second inlet channel 42 takes place before and simultaneously with the blood being conveyed towards the outlet channels 51, 52. This allows pressure equalization between the two inlet channels 41, 42 so that symmetrical forces are maintained within the pump 1. There are a number of straight connections 105 between the first inlet channel 41 and the second inlet channel 42 and are exemplarily indicated by dashed lines. The straight connections 105 allow instantaneous pressure equalization between the inlet channels 41, 42.

[0174] Fig.10 A part of a system according to the invention is shown. A radial blood pump 1 is connected to the respective blood vessels 200, 201, 202, 203 of a heart 205 and supports the Fontan circulation of the heart 205. The pump 1 is connected to the SVC 200 via a first inlet channel 41, the pump is connected to the IVC 201 via a graft 206 via a second inlet channel, the pump 1 is connected to the left pulmonary artery 202 via a first outlet channel 51, and the pump is connected to the right pulmonary artery 203 via a second outlet channel 52.

[0175] Furthermore, a differential pressure sensor 11 is arranged between the atrium of the heart 205 and one of the inlet channels 41 , 42 , here the second inlet channel 42 of the radial blood pump 1 .

[0176] The data from the pressure sensor 11 are then used to regulate the pump rate of the pump 1 .

[0177] This is Fig.11300. The estimated pressure differential 300 is compared 400 to the desired pressure differential 301. A signal compiling the deviation 402 between the estimated pressure differential 300 and the desired pressure differential 301 is provided to a controller 302 of the system. The controller 302 adjusts the pump rate 401 accordingly so that the deviation 402 between the desired pressure 301 and the estimated pressure 300 is minimized. The pressure sensor data 403 is processed before comparison with the processor 303 to provide an appropriate response. In this way, blood flow 200 in the cardiovascular system 500 can be controlled in a robust and fail-safe manner.

[0178] The present invention provides a blood pump 1, in particular a Fontan pump, having a reduced space requirement and having a robust and fail-safe operation.

[0179] References

[0180] [1] M. Gewillig, “The fontan circulation”, Heart, vol. 91, pp. 839–846, 2005.

[0181] [2] DJ Goldberg, R. E. Shaddy, C. Rivashankar, and J. Rychik, “The failing Fontan: etiology, diagnosis and management,” Cardiovascular Specialists Revised, volume 9, number 6, pages 785–793, 2011.

[0182] [3] K. N. Dundi, J. N. Johnson, J. A. Dearani, K. N. Dundi, Z. Li, C. A. Hinck, S. H. Dahl, B. C. Cannon, P. W. O'Leary, D. J. Driscoll, and F. Cetta, “40-Year Follow-Up after the Fontan Operation Long-Term Outcomes of 1,052 Patients,” J. Am. Coll. Cardiol., vol. 66, no. 15, pp. 1700–1710, 2015.

[0183] [4] Y. d'Udekem, AJ Iyengar, JC Galati, V. Forsdick, RG Weintraub, GR Wheaton, A. Bullock, RN Justo, LE Grigg, GF Sholler, S. Hope, DJ Radford, TL Gentles, DS Celermajer, and DS Winlaw, “Redefining Expectations of Long-Term Survival After the Fontan Procedure: Twenty-Five Years of Follow-Up From the Entire Population of Australia and New Zealand,” Circulation, vol. 130, 11_suppl_1, pp. S32–S38, 2014.

[0184] [5] M. D. Rodefeld, B. Coats, T. Fisher, G. A. Giridharan, J. Chen, J. W. Brown, and S. H. Frankel, “Cavopulmonary assist for the univentricular Fontan circulation: Von Kármán viscous impeller pump,” J. Thorac. Cardiovascular Surgery, vol. 140, no. 3, pp. 529–535, 2010.

[0185] [6] C. M. Haggerty, F. Fynn-Thompson, D. B. McElhinney, A. M. Valente, N. Saikrishnan, P. J. Del Nido, and A. P. Yoganathan, “Experimental and numerical investigation of Impella pumps as cavopulmonary assistance for a failing Fontan,” J. Thorac. Cardiovascular Surgery, vol. 144, no. 3, pp. 563–569, 2012.

[0186] [7] R. Prêtre, A. D. Bettex and M. Genoni, "Right-Sided Univentricular Cardiac Assistance in a Failing Fontan Circulation," Ann. Thoracic Surgery, Vol. 86, No. 3, pp. 1018-1020, 2008.

[0187] [8] M. R. Mehra, Y. Naka, N. Uriel, DJ Goldstein, J. C. Leveland, P. C. Colombo, M. N. Walsh, C. A. Milano, C. B. Patel, U. P. Jorde, F. D. Pagani, K. D. Aronson, D. A. Dean, K. McCants, A. Itoh, G. A. E. Wald, D. Horstmanshof, J. W. Long, and C. Salerno, “A Fully Magnetically Levitated Circulatory Pump for Advanced Heart Failure,” N. Engl. J. Med, vol. 376, no. 5, pp. 440–450, 2017.

[0188] [9] KS Sundareswaran, SH Reichenbach, KB Masterson, KC Butler, and DJ Farrar, “Low Bearing Wear in Explanted HeartMate II Left Ventricular Assist Devices After Chronic Clinical Support,” ASAIO J., vol. 59, No. 1, pp. 41–45, 2013.

[0189]

[10] M. Granegger, M. Schweiger, M. Schmid Daners, M. Meboldt, and M. Hübler, “Cavopulmonary mechanical circulatory support in Fontan patients and the need for physiologic control: A computational study with a closed-loop exercise model,” Int. J. Artif. Organs, March 2018.

Claims

1. A radial blood pump (1), for supporting blood flow in a human or animal heart (205), the radial blood pump comprising at least: - a first inlet channel (41) and a second inlet channel (42), - a first outlet channel (51) and a second outlet channel (52), a first electric motor (71) comprising a first stator (77) and a first internal rotor (75), wherein the first electric motor (71) is configured to drive an impeller (2, 2b): - the impeller (2, 2b), the impeller (2, 2b) being arranged at an intersection of the first inlet channel (41) and the second inlet channel (42), wherein the impeller (2, 2b) is connected to the first inner rotor (75), and the impeller (2, 2b) comprises a merging portion (22) arranged at the intersection, at which the first blood flow (106) from the first inlet channel (41) and the second blood flow (107) from the second inlet channel (42) are merged, wherein the impeller (2, 2b) is configured to pump the first blood flow (106) and the second blood flow (107) from the first inlet channel (41) and the second inlet channel (42) to the first outlet channel (51) via the merging portion (22), - the impeller (2, 2b) comprises a plurality of blades (20), wherein the blades (20) are formed with blade channels (21), the merging portion (22) comprises the blade channels (21), wherein each blade (20) is arranged and configured to pump the first blood flow (106) and the second blood flow (107) entering through the first inlet channel (41) and the second inlet channel (42) towards the first outlet channel (51), in, The radial blood pump (1) is arranged and configured so that the first blood flow (106) and the second blood flow (107) meet at the merging portion (22) so that the pressure difference between the first blood flow (106) and the second blood flow (107) is reduced before blood from the first blood flow (106) and the second blood flow (107) is pumped to the first outlet channel (51), wherein the impeller is a closed double suction impeller, wherein the impeller (2, 2b) comprises a first shroud and a second shroud at least partially covering the blades (20), and wherein the merging portion (22) comprises two eye-shaped portions (23), wherein the radial blood pump (1) comprises a straight fluid channel between the first inlet channel (41) and the second inlet channel (42), wherein the straight fluid channel extends through the eye-shaped portion (23) of the closed double suction impeller (2, 2b).

2. The radial blood pump according to claim 1, wherein: The radial blood pump (1) comprises a second electric motor (72) comprising a second stator (78) and a second inner rotor (76), wherein the second inner rotor (76) is rigidly connected to the first inner rotor (75).

3. The radial blood pump according to claim 2, wherein: The first electric motor (71) is arranged in a first half space (S1), which extends from a plane (103) extending orthogonally to the rotation axis (104) of the impeller (2, 2b) and includes the first inlet channel (41), and the second electric motor (72) is arranged in a second half space (S2), which extends from the plane (103) and includes the second inlet channel (42).

4. A radial blood pump according to one of claims 1 to 3, wherein: The impellers (2, 2b) are symmetrical double-suction impellers.

5. The radial blood pump according to one of claims 1 to 3, wherein The diameter of each of the two eye-shaped portions (23) is greater than 2.5 mm.

6. The radial blood pump according to one of claims 1 to 3, wherein The first inner rotor (75) of the first electric motor (71) is arranged on the first shroud.

7. A radial blood pump according to one of claims 1 to 3, wherein The first inlet channel (41) and the second inlet channel (42) are arranged opposite to each other, and the blade (20) is configured so that the straight fluid channel (105) passing through the eye-shaped portion (23) of the impeller (2, 2b) is provided between the first inlet channel (41) and the second inlet channel (42), so that before the blood of the first blood flow (106) and the second blood flow (107) is pumped to the first outlet channel (51) or the second outlet channel (52), the pressure difference between the first blood flow (106) and the second blood flow (107) is reduced.

8. A radial blood pump according to claim 2 or 3, wherein: The radial blood pump (1) has a housing (3), wherein the housing (3) includes the first stator (77) and / or the second stator (78), and the housing (3) at least encloses the following components: a) impeller (2, 2b); b) the first inner rotor (75) and / or the second inner rotor (76); In the entire radial blood pump (1), the distance (8, 9) between the inner wall portion (30) of the housing (3) and the component is at least 0.25 mm.

9. The radial blood pump according to one of claims 1 to 3, wherein The radial blood pump (1) comprises an active magnetic support (62), or wherein the radial blood pump (1) comprises a mechanical support (61).

10. The radial blood pump according to one of claims 1 to 3, wherein Blood from the first inlet channel (41) and / or the second inlet channel (42) can be pumped to the second outlet channel (52) by the impeller (2, 2b).

11. A system having a radial blood pump (1) according to one of claims 1 to 10 and a device for power transmission, wherein: The system also includes a sensor (11) for estimating a hemodynamic signal (300) and a controller configured to adjust a pump rate according to the determined hemodynamic signal (300).

12. The system according to claim 11, wherein: The device for power transmission is configured to wirelessly transmit the power to the radial blood pump (1), wherein the device for power transmission comprises a power receiver and a power transceiver, wherein the power receiver is electrically connected to the radial blood pump (1) and is configured to provide the radial blood pump (1) with electrical energy transmitted from the power transceiver to the power receiver.

Images