• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    A substance exchange device (1) for intracorporeal use, comprising a cavity (3) for receiving blood with at least one blood inlet (8, 9) and at least one blood outlet (10, 11), a mass transfer membrane (4) adjacent to the cavity (3) A supply line (5) for supplying an exchange fluid to the mass transfer membrane (4), a blood pump (6) arranged in the cavity (3) and a drive unit (7) for the blood pump (6), the blood pump (6) for pumping blood in the direction of a blood inlet (8, 9) to a blood outlet (10, 11) of the cavity (3) is arranged, wherein the drive unit (7) comprises a turbine (19) which is connected to the supply line (5) and by means of a The turbine (19) has at least one impeller (21) coupled to the blood pump (6) and a stator (22) arranged in front of the impeller (21).
    公开号:AT519916A1
    申请号:T50318/2017
    申请日:2017-04-20
    公开日:2018-11-15
    发明作者:Ing Christoph Janeczek Dipl；Ing Dr Techn Michael Harasek Dipl；Ing Dr Techn Margit Gföhler Dipl
    申请人:Univ Wien Tech；
    IPC主号:
    专利说明:

    The invention relates to a mass transfer device for intracorporeal use, comprising a cavity for receiving blood with at least one blood inlet and at least one blood outlet, a mass transfer membrane adjacent to the cavity, a supply line for supplying an exchange fluid to the mass transfer membrane, a blood pump arranged in the cavity and a drive unit for the blood pump, the blood pump being set up for pumping blood in the direction from the blood inlet to the blood outlet of the cavity.
    In this context, a mass transfer device is to be understood as any device for exchanging substances from or into the blood. The mass transfer membrane can have a first side and a second side opposite the first side, wherein the first side can adjoin the cavity and the supply line can be set up for supplying the exchange fluid to the second side of the mass transfer membrane. An exchange substance contained in or corresponding to the exchange fluid can pass through the membrane into the blood on the other side or vice versa, an exchange substance can pass from the blood into the exchange fluid. With the blood pump, a local pressure difference can be built up between the blood inlet and the blood outlet during operation and thus enable the required blood flow through the membrane. Otherwise, due to the flow resistance through the membrane, there would hardly be any blood flow through it. The pressure loss caused by the mass transfer device is at least partially compensated for by the blood pump.
    In particular, the blood pump enables the blood flow over the membrane and improves it along the mass transfer device, and optionally supports it via a bypass arranged upstream of the membrane.
    Such mass transfer devices are known from the patent literature in different design variants. For example, WO 2004/016300 A2 discloses an intravenous oxygenator designed as a catheter for oxygenating blood with a membrane in the form of a fiber bundle, the fibers each having a first connection to a gas supply and a second connection to / 30 a gas outlet , The fiber bundle is twisted by a relative rotation of the first connection of the fibers in relation to the second connection of the fibers during operation about the longitudinal axis of the oxygenator. The fibers therefore run as continuous gas lines over the entire length of the fiber bundle. During operation of the oxygenator, oxygen is supplied, which flows through the first connection into the fibers, on the surface of which a diffuse gas exchange with blood takes place. The blood is enriched with oxygen and CO 2 is removed at the same time. At the second connection there is therefore a gas mixture of oxygen and carbon dioxide in the fibers, which flows through a withdrawal chamber in a tube and through it out of the patient's body. The blood flowing into the oxygenator flows through the twisted fiber bundle and reaches a pump. The blood is transported there in the direction of flow of the vein and leaves the oxygenator through an outlet. The pressure drop in the blood is therefore compensated for by the pump, so that the pressure at the outlet is again at the physiological pressure.
    US 2010/258116 A1 mentions only marginally the use of an impeller, but without reference to its use as a blood pump. The impeller is not shown in detail and no executable technical solution is given for how such an impeller could be arranged and driven, so that the function of the impeller remains unclear.
    The pump shown in US 2013/053623 A1 serves to support the cardiac function and thus relates to a completely different field of application than the present device. The pump shown naturally does not comprise a membrane in the sense of the device according to the invention, i.e. for the exchange of substances.
    In the device shown in GB 2505068 A, a blood pump is driven via a drive shaft by a drive unit arranged outside the body. That in this case the drive unit is not part of the mass transfer device for intracorporeal use.
    / 30
    It is an object of the invention to avoid a separate power supply for the drive unit.
    This object is achieved according to the invention by a mass transfer device of the type mentioned at the outset in that the drive unit comprises a turbine which is connected to the feed line and can be driven by means of an exchange fluid fed through the feed line, the turbine having at least one impeller coupled to the blood pump and one in front the impeller arranged stator. That the stator is arranged upstream of the impeller with respect to the direction of flow of the exchange fluid during operation. With the stator arranged in front of the impeller, a correct flow against the turbine impeller from the exchange fluids flowing through the stator (e.g. an exchange substance or a carrier medium) is achieved. Part of the internal energy of the flowing exchange fluid is converted into mechanical power by the turbine, which is delivered to the blood pump via a shaft. The exchange fluid can be liquid or gaseous. It can be supplied to the mass transfer device from outside the body through a catheter and conveyed through the mass transfer device by an extracorporeal pump. The exchange fluid can be a liquid or gaseous exchange substance or a liquid or gaseous carrier medium or conveying medium in which the exchange substance is dissolved or with which the exchange substance is mixed or from which the exchange substance is taken up from the blood.
    One task of the drive unit is the conversion of energy supplied via the fluid into a torque transmitted to a shaft within the mass transfer device. The energy supply of the drive unit is thus carried out together with the supply of the exchange fluid and not separately or independently of it. That both the blood pump and the turbine are integrated in the mass transfer device. The axis of the shaft is arranged essentially parallel to a longitudinal axis of the mass transfer device. The shaft transmits the torque generated in the drive unit to a / 30 connected to the drive unit
    Pump runner of the blood pump. This finally transfers the torque to the blood. In such a conveyor device comprising a turbine as a drive unit and a blood pump as a working machine, part of the flow energy of the
    Transfer exchange fluids to the delivered blood.
    In addition to the feed line, the mass transfer device can have a return line for returning the exchange fluid from the mass transfer membrane. The present invention is not limited to one feed line and one return line. In particular, two feed lines and / or two return lines can be provided, for example different feed lines and / or different return lines can be connected to the membrane or to the turbine. This enables independent control of the mass transfer membrane and the turbine.
    In this case, in particular, the turbine and mass transfer membrane systems can also be controlled independently of one another if any actuated valves are not located in the body but are instead arranged in an external control unit.
    The mass transfer device can be dimensioned in connection with an extracorporeal conveying and exchange device for reprocessing and conveying the exchange fluid as a complete system using components already on the market in such a way that it is portable and the extracorporeal circuit with or on the console even in a pocket fits.
    In the simplest and most reliable case, the turbine element is directly coupled to the pump rotor, so that the two elements run at the same speed during operation. Also in the case of indirect coupling, e.g. by means of a magnetic coupling (see below), the blood pump and the turbine can be operated at the same speed, e.g. when using the same number of pole pairs of the magnets in the coupling. By designing the blood pump and the turbine to a desired operating point (speed, pressure ratios, volume flows), optimized operation of the mass transfer device / 30 can be achieved in both cases.
    It is advantageous if a pump rotor of the blood pump is mounted in a plain bearing. The blood itself is used as a lubricant. This advantage can be achieved regardless of the arrangement of the impeller and stator of the turbine.
    In addition, a pump runner can produce other parts of the blood pump from a technical ceramic such as aluminum oxide, from a metal such as titanium or from a plastic such as PEEK (polyether ether ketone) and preferably also be provided with a surface coating. These materials are particularly suitable for use in the bloodstream.
    It is also advantageous if at least one speed sensor is integrated in the mass transfer device, which is set up to record the speed of the turbine, the blood pump or a clutch between the blood pump and the turbine. In this context, integrated means that the speed sensor is part of the mass transfer device and is consequently arranged intracorporeally during operation of the mass transfer device. Several speed sensors can be provided, so that the speed can be recorded at several of the above-mentioned points. The recorded speed can then be converted into an electronic signal and used to monitor and control the proper operation of the mass transfer device. In particular, a Hall sensor can be provided as the speed sensor.
    In one embodiment of the present invention, the blood pump can be coupled to the turbine via a gear, the gear being set up to reduce the speed of the blood pump compared to the speed of the turbine. Such a reduction is particularly advantageous when using a gaseous exchange fluid so that the turbine can be operated at a correspondingly higher speed than that required for the blood pump. In general, the gearbox can be used to determine a suitable operating point of the turbine for the respective exchange fluid at a predetermined speed of / 30
    Blood pump can be reached.
    Furthermore, it has been found to be advantageous if the mass transfer device in question has one or more return line (s) for returning an exchange fluid from the mass transfer membrane and / or the turbine, the return line being set up to have a negative pressure (ie one compared to an ambient pressure of approx. 1 bar negative differential pressure). In this case, the overpressure of the supply line can be reduced or avoided entirely, which can reduce the risk of leakage of exchange fluid into the blood in the event of a leak. A concentration gradient can also be achieved on the mass transfer membrane by applying a vacuum instead of the exchange fluid.
    In connection with the drive unit, it is advantageous if the pump rotor is connected to the drive unit via a magnetic coupling, the magnetic coupling for torque transmission along an axis of rotation having two coupling parts which can be rotated relative to one another, each having a permanent magnet. For example, a central rotary coupling or an end rotary coupling can be used as the magnetic coupling. A magnetic coupling has a continuous mechanical connection, e.g. in the form of a continuous shaft, the advantage that the transmitted torque is limited and a hermetic separation can be made between blood-carrying and non-blood-carrying parts. If the turbine gets stuck, the pump rotor also stops; the limitation is nevertheless technically sensible, since a failure can be detected. If the turbine were to spin up due to a fault, the magnetic coupling would eventually no longer transmit the power. The blood circulation is protected against overload.
    In order to be able to transmit a desired torque even in the case of a particularly compact magnetic coupling, it has proven to be advantageous if one of the coupling parts comprises an at least partially ferromagnetic diverting element which is connected to the permanent magnet of the coupling part in a rotationally fixed manner, part of the diverting element being radial is arranged outside the permanent magnet of the other coupling part. Such a magnetic coupling is shown for example in WO 2015/172173 A2, the content of which is hereby incorporated into this application. That the magnetic coupling comprises two coupling parts which can be rotated relative to one another, a drive-side coupling part having a drive-side permanent magnet and a drive-side coupling part having a drive-side permanent magnet opposite the drive-side permanent magnet along the axis of rotation and arranged at a distance therefrom, one of the coupling parts comprising an at least partially ferromagnetic diverting element which is connected in a rotationally fixed manner to the permanent magnet of the coupling part, part of the diverter element being arranged radially outside the opposite permanent magnet. This design has the advantage over conventional central rotary couplings that it is easier and cheaper to manufacture and requires an overall smaller coupling area, since part of the torque is transmitted via the end face of the coupling parts.
    Compared to conventional face rotary couplings, it has the advantage that smaller radial dimensions are required to transmit a certain torque. The diverting element can - like the outer coupling part of a central rotary coupling - be pot-shaped or hollow-cylindrical and surround the other coupling part on the circumference, i.e. it preferably extends radially outside of both permanent magnets. The bypass element can be designed, for example, as a thin-walled hollow cylinder, so that the magnetized volume of the front rotary coupling is largely retained while the dimensions remain the same, and at the same time a transmissible torque comparable to a central rotary coupling can be achieved between the bypass element and the permanent magnet located at a distance from it. The magnetization direction of the permanent magnets is preferably oriented perpendicular to the axis of rotation, i.e. the magnetic poles run in the circumferential direction from south to north and are at least in a two-pole version diametrically opposite with respect to the axis of rotation. The diverting element bundles magnetic field lines / 30 radially extending from the permanent magnets and additionally increases the magnetic force between the coupling parts because of the ferromagnetic material of the diverting element. The magnetic force for transmitting the torque is increased by the compression of the magnetic field lines in the ferromagnetic material. Due to the larger volume of the permanent magnets compared to central rotary couplings with the same coupling dimensions, a smaller axial extension and thus lower radial transverse forces on the bearings of the coupling parts can advantageously be achieved.
    The permanent magnets of the magnetic coupling can each be 2-, 4-, or 6-pole permanent magnets. They are preferably bipolar, each with two semi-cylindrical magnetic poles. The at least partially ferromagnetic diverting element can have at least one diamagnetic or paramagnetic separation. This separation divides the diverting element into at least two ferromagnetic sections and thus avoids a magnetic short circuit. A diamagnetic separation or a paramagnetic separation (e.g. made of aluminum or brass) can be used. Materials with a magnetic permeability of only slightly greater than 1 are referred to as paramagnetic, in particular with a magnetic permeability less than 1.2, preferably with a magnetic permeability less than 1.05.
    In addition to the radially outer arrangement, the diverting element can also extend to a rear side of the non-rotatably connected permanent magnet facing away from the opposite permanent magnet. Alternatively or additionally, the diverter element can have an essentially H-shaped longitudinal section, with a transverse web lying perpendicular to the axis of rotation and cup-shaped recesses on both sides, a permanent magnet being received in one of these recesses and connected in a rotationally fixed manner. That the diverting element can have a hollow cylindrical jacket and can preferably be formed with an intermediate floor arranged at substantially half the height of the jacket.
    A particularly high concentration of magnetic field lines in / 30
    Diverter element of the magnetic coupling can be achieved if a diamagnetic or paramagnetic shielding element is arranged on a rear side of the permanent magnet that is non-rotatably connected to the diverter element and faces away from the opposite permanent magnet. As a result, field lines running outside the coupling parts, in particular outside the diverter element, can be avoided and associated losses can be reduced. That the “shielding achieved by the shielding element is preferably that the magnetic field lines preferably pass through the bypass element than through the shielding element.
    Furthermore, it has proven to be advantageous if, in the magnetic coupling, a diamagnetic or paramagnetic shielding element is arranged on a front side of the permanent magnet, which is connected to the bypass element in a rotationally fixed manner, in particular in a region centered around the axis of rotation, which is preferably circumferential or radial connects to the outside of the diversion element. With such a shield, a deflection of the magnetic field can be achieved in areas located radially at a greater distance from the axis of rotation, so that the torque transmitted at a given magnetic force is increased.
    In order to reliably prevent the carrier medium from entering the blood, it is also advantageous if the two coupling parts are hermetically separated. Such a hermetic separation can be achieved, for example, by a hermetic partition arranged between the two coupling parts, which hermetically separates the drive unit and the blood pump. The hermetic partition should not be magnetic or electrically conductive. In particular, at least one of the coupling parts can be accommodated in a substantially non-magnetic and electrically non-conductive housing, so that losses due to magnetic reversal of the housing or induced eddy currents in the housing can be avoided.
    The bypass element can preferably be connected in a rotationally fixed manner to the drive-side coupling part, at least one flushing channel being provided within a hermetic partition between the two coupling parts, which has a gap / 30 between the end face of the pump-side coupling part and the hermetic partition wall in operation with at least one blood flow outside the Hermetic partition connects, which blood flow can be either a blood flow through the blood inlet or a blood flow before the blood inlet. The flushing channel thus connects a part of the coupling on the blood and pump side and a blood flow outside the coupling. The inlet to the blood and pump-side part of the coupling takes place via a coupling bearing close to the coupling in front of the blood-side magnet or via a bore in the shaft of the pump. A connection to a blood flow outside the coupling is thus established between the end face of the pump-side coupling part and through the hermetic partition wall, the function of the hermetic separation between blood-carrying and non-blood-carrying parts remaining. Such flushing channels can be used to reduce or completely avoid dead spaces on an output side (“blood side”) within the magnetic coupling.
    In particular, it has been shown that an integrated bearing, preferably a roller bearing, is provided between a coupling part on the drive side and the hermetic partition and a sliding bearing between the hermetic partition and the coupling part on the output side. That the coupling part on the drive side is rotatably supported in a roller bearing relative to the hermetic partition and the coupling part on the output side is rotatably supported in a plain bearing relative to the hermetic partition. Such storage ensures more stable operation and increased smoothness in the area of the coupling compared to coupling parts that are not mounted on the end face, since here there is, among other things, the risk that the magnetic pot will start to vibrate and the torque transmission will break off.
    The mass transfer across the membrane is determined by three transport resistances, the blood-side mass transfer resistance - also known as concentration polarization, the mass transfer resistance through the membrane and the mass transfer resistance into the transducer phase (carrier substance) on the permeate side of the membrane. Because of the essentially / 30 laminar flow conditions, the boundary layer thickness and thus the mass transfer resistance increases with the overflow length of the membrane. Due to the substance properties of the blood - the rheology, the low diffusion coefficients and the buffering effect - the primary aim is to reduce the mass transfer resistance on the blood side. This is achieved by: a) increasing the overflow speed and thus reducing the boundary layer thickness, b) improving the flow distribution and making the dwell time more uniform, c) geometric measures through controlled flow control, through the installation of static turbulence promoters, through the geometrically induced induction of secondary flow phenomena and through targeted Interruption of the boundary layer structure, d) controlled distribution, merging, mixing and redistribution of the blood on the membrane. The present invention solves this problem by combining measures a) to d).
    It is therefore particularly advantageous if a deflection device is arranged between the blood pump and the at least one blood outlet in the cavity, wherein the deflection device is designed to partially deflect a blood flow flowing axially through the cavity in the radial direction and / or to induce turbulence in this blood flow is set up. For example, the diverter can serve as a static turbulence promoter. By partially redirecting the blood in the direction of a radial flow component and / or inducing turbulence in the flow, the exchange with the exchange fluid on the mass exchange membrane can be improved.
    For example, the deflection device may have spiral, conical (or truncated cone), arrow-shaped and / or disk-shaped guide surfaces concentric to a longitudinal axis between the blood pump and the blood outlet.
    The deflection device can be rotatably mounted in the cavity. It can be freely rotatable or preferably coupled to the pump rotor of the blood pump for forced rotation of the deflection device.
    / 30
    The cavity can preferably have at least two blood outlets at different distances from the at least one blood inlet. In particular, a first blood outlet can be provided immediately downstream of the blood pump and a second blood outlet can be provided downstream of the mass transfer membrane. The first blood outlet forms a bypass for the mass transfer membrane. In operation, blood can flow out of the cavity and out of the mass transfer device to the outside of the mass transfer device, e.g. pour into a surrounding vessel. Due to the drive by the blood pump, this blood has a higher internal energy than the blood flowing past the mass transfer device, so that the delivery leads to a comparatively higher local pressure in the vessel. Such an arrangement of a plurality of blood outlets can also be provided independently of the use of a turbine as the drive unit and consequently also independently of the arrangement of the impeller and stator of a turbine. Instead of a turbine, the mass transfer device could, for example, comprise an electric motor as a drive unit for the blood pump.
    The invention also relates generally to a mass transfer device for intracorporeal use, comprising a cavity for receiving blood with at least one blood inlet and at least one blood outlet, a mass transfer membrane adjacent to the cavity, a supply line for supplying an exchange fluid to the mass transfer membrane, a blood pump arranged in the cavity and a drive unit for the blood pump, the blood pump being set up for pumping blood in the direction from a blood inlet to a blood outlet of the cavity, the drive unit comprising a turbine which is connected to the feed line and can be driven by means of an exchange fluid fed through the feed line.
    The invention is explained in more detail below on the basis of particularly preferred exemplary embodiments, to which, however, it should not be restricted, and with reference to the drawings. The following show in detail:
    Figure 1 shows schematically a longitudinal section through a / 30 mass transfer device according to the invention in an intracorporeal and intravascular use.
    Fig. 2 shows schematically a mass transfer device with a
    Deflection device with spiral guide surfaces;
    3 schematically shows a mass transfer device with a deflection device with frustoconical guide surfaces;
    4 schematically shows a partial longitudinal section through a mass transfer device with a deflection device according to FIG. 3;
    5 schematically shows a longitudinal section of a deflection device with arrow-shaped guide surfaces for use in a mass transfer device according to the invention;
    6 schematically shows a longitudinal section of a deflection device with disk-shaped guide surfaces for use in a mass transfer device according to the invention;
    FIG. 7 schematically shows a detailed view of the magnetic coupling of the mass transfer device according to FIG. 1; and
    8 schematically shows an intracorporeal and extravascular use of a mass transfer device according to the invention.
    1 shows a mass transfer device 1 in operation in an intracorporeal arrangement. In this arrangement, the mass transfer device 1 is used as an intravascular catheter in a blood vessel 2. The mass transfer device 1 comprises a cavity 3, a mass transfer membrane 4, a feed line 5, a blood pump 6 and a drive unit 7. Blood is received in the cavity 3 during operation. The cavity 3 has two blood inlets 8, 9 and two blood outlets 10, 11. The two blood outlets 10, 11 are different
    Distances from the two blood inlets 8, 9 arranged. The first blood outlet 10 is arranged immediately after the blood pump 6 and forms a bypass for the mass transfer membrane 4. The second blood outlet 11 is arranged after the mass transfer membrane 4 and forms the proximal end of the mass transfer device 1. The mass transfer membrane 4 adjoins the cavity 3. It can be a hollow fiber membrane with fibers arranged in a cylindrical shape around the cavity 3. The mass transfer membrane 4 essentially maintains a constant position in the surrounding vessel 2 and is not rotated relative to it.
    / 30
    The supply line 5 is set up for supplying an exchange fluid to the mass transfer membrane 4. The exchange fluid can be a low-CO2 gas mixture, for example. The feed line 5 connects, for example, the inlet 12 of a hollow fiber membrane to a feed hose 13, which connects the mass transfer device 1 to an extracorporeal exchange device for reprocessing the exchange fluid. The mass transfer device 1 also includes a return line 14 for returning an exchange fluid from the mass exchange membrane 4. The return line 14 and a return hose 15 connected to it are set up to withstand a negative pressure. The supply hose 13 and the return hose 15 can be designed as a single multi-lumen, e.g. be double-walled, hose.
    The blood pump 6 is arranged in the cavity 3. It is for pumping blood towards blood inlets 8, 9
    Blood outlets 10, 11 of the cavity 3 are set up. The blood pump 6 is preferably a centrifugal pump in a radial, diagonal or axial design. A pump rotor 16 of the blood pump 6 is mounted in at least one slide bearing 17. A stator 18 can be arranged after the pump rotor 16 to reduce or completely remove the rotary portion of the conveyed medium and convert it into a pressure increase. However, if this stator 18 is not used, the flow can also be directed with a rotation to the mass transfer membrane 4 so that the flow is not (only) flowed in the longitudinal direction. The blood pump 6 has the task of promoting the blood flow in such a way that the mass transfer membrane 4 is sufficiently flowed through with blood. In the case of an intravascular application, the mass transfer device 1 represents an additional resistance in the vessel 2, which is at least partially compensated for by the kinetic energy supplied to the blood by the blood pump 6. At the same time, depending on the operating mode, the pressure loss through the mass transfer device 1 in the vessel 2 can be completely or partially compensated for or an increase in pressure in the vessel 2 can also be achieved. In particular, this can take place through the first blood outlet 10, which makes it possible that not every blood volume that flows through the blood pump 6 also flows through the mass transfer membrane 4.
    / 30
    The drive unit 7 serves to drive the blood pump 6. With its help, the blood pump can be set in rotation and thus the entry of the blood into the mass transfer membrane 4 can be defined in relation to the flow direction and volume flow. The drive unit 7 comprises a turbine 19. The turbine 19 is connected to the feed line 5, in particular arranged in the feed line 5, and can be driven by means of an exchange fluid fed through the feed line 5. The turbine 19 has an impeller 21 coupled to the blood pump 6 via a rotatably mounted shaft 20 and a stator 22 arranged in front of the impeller 21. The blood pump 6 is coupled to the turbine 19 via a gear 23. The gear 23 is set up to reduce the speed of the blood pump 6 compared to the speed of the turbine 19. It can be a planetary gear, for example. The drive unit 7 and the blood pump 6 together form a delivery device for delivering blood through the cavity 3 of the mass transfer device 1. In operation, the pump rotor 16 of the blood pump 6 is driven by the turbine 19 in such a way that an acceleration of the blood flow in the area of the blood inlets 8, 9 and thus an overpressure is generated at the distal end of the cavity 3. The speed of the turbine 19 can be controlled via the mass flow or the volume flow of the exchange fluid such that the differential pressure achieved at the pump just compensates for all pressure losses occurring from the blood inlets (8,9) to the proximal blood outlet (11). This effectively compensates for the flow resistance inside the mass transfer device 1 caused by the mass transfer membrane 4.
    Two speed sensors 24, 25 are integrated in the mass transfer device 1. The first speed sensor 24 is set up to record the speed of the turbine 19, the second speed sensor 25 is set up to record the speed of the blood pump 6. Both speed sensors 24, 25 are Hall sensors. The speed sensors 24, 25 are integrated in a housing 71 of the mass transfer device 1, which surrounds the drive unit 7 and the blood pump 6. A magnet 72, preferably centrally, is arranged as a signal generator for the speed sensors 24, 25 in the impeller 21 of the turbine 19 and in the pump rotor 16 of the blood pump 6 (the eccentric representation is only schematic and serves to make it easier to identify; in practice there is one Avoid unbalance).
    A pump rotor 16 of the blood pump 6 is connected to the turbine 19 via a magnetic coupling 26 (cf. FIG. 7). For torque transmission along an axis of rotation 27, the magnetic coupling 26 has two coupling parts 28, 29 that can be rotated relative to one another, each with a two-pole permanent magnet. One of the coupling parts 28 comprises an at least partially ferromagnetic, pot-shaped diverter element 30. The diverter element 30 is connected to the permanent magnet of the drive-side coupling part 28 in a rotationally fixed manner. Part of the diverter element 30 is arranged radially outside the permanent magnet of the other coupling part 29. The jacket of the diverter element 30 is interrupted only in a narrow angular range by a diamagnetic or paramagnetic separation (not shown). The diamagnetic separation essentially divides the diverter element 30 into two ferromagnetic halves or half-shells. A section plane running through the diamagnetic or parmagnetic separation is thus perpendicular to a direction of magnetization of the two-pole permanent magnet on the drive side connected to the bypass element 30. The ferromagnetic sections of the diverter element 30 defined by the diamagnetic or paramagnetic separation are therefore magnetized in accordance with the permanent magnet on the drive side.
    Due to the contactless coupling, a hermetic partition 31 is provided between the drive-side coupling part 28 and the output-side coupling part 29. At least one flushing channel 32 is provided within the hermetic partition 31. The flushing channels 32 connect a gap 33 between the end face 34 of the pump-side coupling part 29 and the hermetic partition 31 with an area adjacent to the blood inlets 8, 9. An additional flushing channel 73 is provided within the pump-side shaft section 38 for lubricating a fixed slide bearing socket 74, in which the shaft section 38 is mounted. As can be seen in detail in FIG. 7, the rotatable components of the mass transfer device are on the driven side (also / 30
    Pump side or "blood side) stored in slide bearings 17 and the rotatable components of the mass transfer device on the
    Drive side (also turbine side) are mounted in roller bearings 35 (see also FIG. 1).
    In operation, a torque is applied to the impeller 21 by the flow of the exchange fluid supplied via the blades of the turbine 19. The turbine 19 transmits the torque via the shaft 36, which is rotatably mounted in roller bearings 35, to the drive side of the gear 23. On the output side of the gear 23, a correspondingly higher torque is transmitted at a lower speed via a further shaft section 37 to the drive-side coupling part 28 of the magnetic clutch 26 , If the drive fluid is a liquid medium, the transmission 23 can be dispensed with, provided that the turbine and the pump have the same speed at the respective operating point and the output torque of the turbine corresponds to the required input torque of the pump. The torque is transmitted from the drive-side clutch part 28 to the output-side clutch part 29 by the magnetic forces between the clutch parts 28, 29, the strength of the magnetic forces defining a certain maximum transmissible torque beyond which there is a “spinning of the clutch parts 28, 29 comes relative to each other. The output-side coupling part 29 transmits a torque exerted by the input-side coupling part 28 to the pump rotor 16 of the blood pump 6 via a third shaft section 38, which is mounted in slide bearings 17 , 9 through the cavity 3 in
    Direction of the mass transfer membrane 4 of the mass transfer device 1. In this way, the conveying device generates a pressure difference between the blood inlets 8, 9 and the proximal end of the cavity 3, which preferably causes a pressure loss between the proximal and the distal end of the mass transfer device 1 due to the
    Flow resistance of the mass transfer membrane 4 essentially completely compensated, so that after the
    Mass exchange device 1 blood 41 flowing in the vessel 2 has at least the same internal energy as the blood 40/30 before it. The concentration of a substance can either be reduced at the point in the blood 40 to the point in the blood 41 (for example CO 2
    Reduction) or increased (eg O 2 enrichment).
    Instead of a hollow fiber membrane, another membrane type can also be used in the mass transfer device 1 as the mass transfer membrane 4, the person skilled in the art adapting the conveying device with the drive unit 7 and the blood pump 6 to the expected pressure difference due to the different flow resistance of other membrane types.
    In the section of an exemplary embodiment shown in FIG. 2, a deflection device 44 is arranged between the blood pump (on the right side, not shown here) and a blood outlet 42 in the cavity 3 within a mass transfer membrane 43. The deflection device 44 is designed for the partial deflection of a blood flow flowing axially through the cavity 3 in the radial direction. The deflection device 44 shown schematically in FIG. 2 has spiral guide surfaces 46 concentric to a longitudinal axis 45 between the blood pump and the blood outlet 42. The deflection device 44 can be fixed rigidly in the cavity 3 of the mass transfer device 1 or can be rotatably mounted in the cavity 3. By means of the spiral-shaped guide surfaces 46, the blood 47 flowing in during operation from the pump in the center along the longitudinal axis 45 is constantly pushed radially through the length along the longitudinal axis and thus transversely to the mass transfer membrane 43 by the spiral shape. A mass transfer with an exchange fluid takes place in the mass transfer membrane 43, which is supplied to the mass transfer membrane 43 through feed and return lines 48 or is returned from the mass transfer membrane 43.
    A further variant of a deflection device 49 is shown schematically in FIGS. 3 and 4. The mass transfer membrane 43 and the feed and return lines 48 correspond to those from FIG. 2. The deflection device 49 according to FIGS. 3 and 4 points concentrically to a longitudinal axis 45 between the blood pump (not shown; right side in FIG. 4) and the blood outlet 42 frustoconical guide surfaces 50. That in / 30
    Operation of blood 47 flowing in from the pump flows along the outside of the guide surfaces 50 through the spaces or openings 51 of the deflection device 49 left free therebetween and through the mass transfer membrane 43. The deflection device 49 is freely rotatably mounted between two slide bearings 52, 53. The slide bearing 53 arranged downstream has flushing channels in order to ensure lubrication in the bearing area. The deflection device 49 also has its own turbine element 54, which is driven by the blood 47 flowing in from the blood pump and thus sets the deflection device 49 in rotation. By means of the centrifugal force generated by the rotation, an additional acceleration of the blood flow in the radial direction is achieved through the mass exchange membrane 43 arranged radially outside. Part of the blood flows in the center of the internally hollow deflection device 49 along the longitudinal axis 45.
    5 shows, in a highly simplified manner, a similarly functioning deflection device 55 with arrow-shaped guide surfaces and FIG. 6, likewise in a highly simplified manner, a deflection device 56 with disk-shaped guide surfaces. The deflection devices 44, 49, 55, 57 can each be freely rotatable or optionally coupled to the pump rotor 16 of the blood pump 6 in a rotationally fixed manner and rotate with its speed in order to accelerate the blood flow in the radial direction by a radial direction by means of a centrifugal force generated by the rotation to achieve mass transfer membrane 43 arranged outside. As an alternative to coupling to the pump rotor 16, a turbine element 54 (see FIG. 4) can be integrated into the deflection device.
    In the use shown in FIG. 8, a mass transfer device 59 according to the invention (only indicated schematically) with a mass transfer membrane 60 and a conveying device 61 is arranged in a tube 62 which is foreign to the body and which connects two blood vessels 63, 64 to one another. By a first
    Tube section 65, a part of the blood flow or the entire blood flow is withdrawn from the first blood vessel 63 and fed through a blood inlet 66 of the mass transfer device 59 to the conveyor 61 with a turbine, a magnetic coupling and / 30 a blood pump and the mass transfer membrane 60 to the mass transfer device 59. From the blood outlet 67 of the mass transfer device 59, the blood is supplied to the second blood vessel 64 through a second tube section 68. The second blood vessel 64 can be identical to the first blood vessel 63. The direction of flow of the blood is indicated by arrows 69. An exchange fluid is supplied to the mass transfer device 59 through a multi-lumen tube 70 and is returned from the mass transfer device 59. In this application, there is no need for a gearbox between the turbine and the blood pump, since when a gas is used as the drive fluid for the turbine, the space available can make it correspondingly larger. Provided that the turbine and the pump have the same speed at the respective operating point and the delivered torque of the turbine corresponds to the required input torque of the pump.
    权利要求:
    Claims (15)
    [1]
    Expectations:
    1. A mass transfer device (1) for intracorporeal use comprising a cavity (3) for receiving blood with at least one blood inlet (8, 9) and at least one blood outlet (10, 11), a mass transfer membrane (4) adjacent to the cavity (3) , a supply line (5) for supplying an exchange fluid to the mass exchange membrane (4), a blood pump (6) arranged in the cavity (3) and a drive unit (7) for the blood pump (6), the blood pump (6) for pumping of blood in the direction from a blood inlet (8, 9) to a blood outlet (10, 11) of the cavity (3), characterized in that the drive unit (7) comprises a turbine (19) which is connected to the supply line (5 ) and can be driven by means of an exchange fluid supplied through the feed line (5), the turbine (19) having at least one impeller (21) coupled to the blood pump (6) and one stator (22) arranged in front of the impeller (21).
    [2]
    2. mass transfer device (1) according to claim 1, characterized in that a pump rotor (16) of the blood pump (6) is mounted in a slide bearing (17).
    [3]
    3. mass transfer device (1) according to claim 1 or 2, characterized in that in the mass transfer device (1) at least one speed sensor (24, 25) is integrated, which for receiving the speed of the turbine (19), the blood pump (6) or a coupling between the blood pump (6) and the turbine (19) is set up.
    [4]
    4. mass transfer device (1) according to any one of claims 1 to
    3, characterized in that the blood pump (6) is coupled to the turbine (19) via a gear (23), the gear (23) being set up to reduce the speed of the blood pump (6) compared to the speed of the turbine (19) is.
    [5]
    5. mass transfer device (1) according to any one of claims 1 to
    4, characterized by a return line (15) for returning an exchange fluid from the mass transfer membrane (4) and / or the turbine (19), the return line (15)
    22/30 is set up to withstand oppression.
    [6]
    6. mass transfer device (1) according to any one of claims 1 to
    5, characterized in that a pump rotor (16) of the blood pump (6) is connected to the turbine (19) via a magnetic coupling (26), the magnetic coupling (26) for torque transmission along an axis of rotation having two coupling parts (28, 29) each with a permanent magnet.
    [7]
    7. mass transfer device (1) according to claim 6, characterized in that one of the coupling parts (28) comprises an at least partially ferromagnetic diverting element (30) which is non-rotatably connected to the permanent magnet of the coupling part (28), part of the diverting element (30 ) is arranged radially outside the permanent magnet of the other coupling part (29).
    [8]
    8. mass transfer device (1) according to claim 7, characterized in that the at least partially ferromagnetic diverting element (30) has at least one diamagnetic or paramagnetic separation.
    [9]
    9. mass transfer device (1) according to any one of claims 6 to
    8, characterized in that a hermetic partition (31) is arranged between the two coupling parts (28, 29), which hermetically separates the drive unit (7) and the blood pump (6).
    [10]
    10. mass transfer device (1) according to claim 9, characterized in that an integrated bearing, preferably a roller bearing (35), between a drive-side coupling part (28) and the hermetic partition (31) and a sliding bearing (74) between the hermetic partition ( 31) and the output-side coupling part (29) are provided.
    [11]
    11. mass transfer device (1) according to any one of claims 7 to
    10, characterized in that the diverter element (30) is connected in a rotationally fixed manner to the drive-side coupling part (28), at least one flushing channel (32) being located within a hermetic partition (31) between the two coupling parts (28, 29).
    23/30 is provided which connects a gap (33) between the end face (34) of the pump-side coupling part (29) and the hermetic partition (31) in operation with at least one blood flow outside the hermetic partition (31), this blood flow either a blood flow through the blood inlet (8, 9) or a blood flow (40) before the blood inlet (8, 9).
    [12]
    12. mass transfer device (1) according to any one of claims 1 to
    11, characterized in that a deflection device (44, 49, 55, 57) is arranged between the blood pump (6) and the at least one blood outlet (11) in the cavity (3), the deflection device (44, 49, 55, 57 ) is set up for the partial deflection of a blood stream flowing axially through the cavity (3) in the radial direction and / or for inducing turbulence in this blood stream.
    [13]
    13. mass transfer device (1) according to claim 12, characterized in that the deflection device (44, 49, 55, 57) concentric to a longitudinal axis (45) between the blood pump (6) and the blood outlet (11) spiral, cone-shaped, arrow-shaped and / or disc-shaped guide surfaces (46, 50, 56, 58).
    [14]
    14. mass transfer device (1) according to claim 12 or 13, characterized in that the deflection device (44, 49, 55, 57) is rotatably mounted in the cavity (3).
    [15]
    15. mass transfer device (1) according to one of claims 1 to
    14, characterized in that the cavity (3) has at least two blood outlets (10, 11) at different distances from the at least one blood inlet (8, 9).
    类似技术:
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    AT393456B|1991-10-25|Centrifugal pump for the conveyance of blood
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    同族专利:
    公开号 | 公开日
    AT519916B1|2019-02-15|
    EP3612245A1|2020-02-26|
    WO2018193079A1|2018-10-25|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    WO2003061727A2|2002-01-16|2003-07-31|Alung Technologies, Inc.|Intravenous oxygenator having an impeller|
    WO2004016300A2|2002-07-22|2004-02-26|Helmut Reul|Intravenous oxygenator|
    WO2006031858A1|2004-09-13|2006-03-23|University Of Maryland, Baltimore|Blood pump-oxygenator system|
    US8641659B2|2011-02-17|2014-02-04|Medtronic, Inc.|Method and device to treat kidney disease|
    DE102006036948A1|2006-08-06|2008-02-07|Akdis, Mustafa, Dipl.-Ing.|blood pump|
    US9162017B2|2011-08-29|2015-10-20|Minnetronix, Inc.|Expandable vascular pump|US20200288988A1|2019-03-14|2020-09-17|Abiomed, Inc.|Blood Flow Rate Measurement System|
    AT523469A1|2020-01-27|2021-08-15|Univ Wien Tech|Mass transfer device|
    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    ATA50318/2017A|AT519916B1|2017-04-20|2017-04-20|Mass transfer device|ATA50318/2017A| AT519916B1|2017-04-20|2017-04-20|Mass transfer device|
    US15/950,218| US10709827B2|2015-10-14|2018-04-11|Membrane catheter|
    PCT/EP2018/060160| WO2018193079A1|2017-04-20|2018-04-20|Mass transfer device|
    EP18719831.2A| EP3612245A1|2017-04-20|2018-04-20|Mass transfer device|
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