Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
  • A61B5/14525—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using microdialysis
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1621—Constructional aspects thereof
  • A61M1/1623—Disposition or location of membranes relative to fluids
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1654—Dialysates therefor
  • A61M1/1676—Dialysates therefor containing proteins, e.g. albumin
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1678—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes intracorporal
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
  • A61M1/3679—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits by absorption
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/0043—Catheters; Hollow probes characterised by structural features
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/10—Location thereof with respect to the patient's body
  • A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
  • A61M60/109—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems
  • A61M60/113—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems in other functional devices, e.g. dialysers or heart-lung machines
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/10—Location thereof with respect to the patient's body
  • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
  • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
  • A61M60/13—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel by means of a catheter allowing explantation, e.g. catheter pumps temporarily introduced via the vascular system
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/20—Type thereof
  • A61M60/205—Non-positive displacement blood pumps
  • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
  • A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow pumps
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
  • A61M60/36—Medical purposes thereof other than the enhancement of the cardiac output for specific blood treatment; for specific therapy
  • A61M60/37—Haemodialysis, haemofiltration or diafiltration
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
  • A61M60/36—Medical purposes thereof other than the enhancement of the cardiac output for specific blood treatment; for specific therapy
  • A61M60/38—Blood oxygenation
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/40—Details relating to driving
  • A61M60/403—Details relating to driving for non-positive displacement blood pumps
  • A61M60/405—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/40—Details relating to driving
  • A61M60/403—Details relating to driving for non-positive displacement blood pumps
  • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
  • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
  • A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/40—Details relating to driving
  • A61M60/403—Details relating to driving for non-positive displacement blood pumps
  • A61M60/419—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being permanent magnetic, e.g. from a rotating magnetic coupling between driving and driven magnets
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/80—Constructional details other than related to driving
  • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
  • A61M60/884—Constructional details other than related to driving of implantable pumps or pumping devices being associated to additional implantable blood treating devices
  • A61M60/886—Blood oxygenators
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
  • A61M60/80—Constructional details other than related to driving
  • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
  • A61M60/884—Constructional details other than related to driving of implantable pumps or pumping devices being associated to additional implantable blood treating devices
  • A61M60/888—Blood filters
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
  • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
  • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
  • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
  • A61B5/6852—Catheters
• • B—PERFORMING OPERATIONS; TRANSPORTING
  • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
  • B01D—SEPARATION
  • B01D63/00—Apparatus in general for separation processes using semi-permeable membranes
  • B01D63/08—Flat membrane modules
  • B01D63/087—Single membrane modules

Definitions

• the invention relates to a device for the exchange of
• the field of application of the invention also includes functions that support or replace the activity of organs in the body, especially the lungs, kidneys or liver. Finally, the invention can not be applied even when administered
• An extracorporeal blood purification (ECBP), for example, also falls under the above field of application. This concerns removal of endogenous or exogenous toxins or solutes from the blood and includes
• the guiding principle is the removal of blood from the patient, removal of the substance in an external
• GB 2 004 092 A shows a device for measuring the
• a measuring liquid is passed in a circuit on a membrane, which forms the outside of the catheter, passed over and out of the body, where the liquid is first enriched with oxygen. Subsequently, the Measuring liquid supplied to an enzyme reactor and the
• the surface of the membrane is limited in this construction by the dimensions of the catheter, so that only a comparatively small proportion of the blood comes into contact with the membrane and participates in the exchange with the measuring liquid.
• WO 2008/046630 A1 shows devices for continuous monitoring of the concentration of a substance in the blood by means of microdialysis.
• a tube membrane surrounded by blood and perfused with perfusate can be used.
• Pipe membrane naturally has no blood inlet or outlet.
• tube membrane is a planar membrane
• Membrane Oxygenation or ECC02R (Extra Corporeal C0 2 Removal) systems.
• Such systems typically include cannulas, a centrifugal pump, a tubing system, a membrane oxygenator, safety systems, and a heat exchanger, and are reliable and easy to handle.
• cannulas typically include cannulas, a centrifugal pump, a tubing system, a membrane oxygenator, safety systems, and a heat exchanger, and are reliable and easy to handle.
• they have several limitations for widespread use and frequent use - they are very expensive, very large and make patients immobile, that is, the patient must be sedated during treatment, as threatened by movements dislocation of the cannulas.
• Membrane oxygenators have been clinically proven in the past and approved for use in patients. These techniques primarily aimed to improve the lack of oxygen in the blood by intravascular membrane oxygenation or to ensure a sufficient supply of oxygen. Achieving this goal requires a large contact surface between blood and gas phase and a supply of gases into the catheter in the vascular system, potentially increasing the risk of gas embolism. The problem of the necessary large minimum surface was solved with the introduction of deployable networks of hollow fibers, which were rinsed extracorporeally with high gas flows. This technique has several limitations, including a low gas transfer for oxygen (0 2 ), a high thrombogenicity of the turbulent flow through the fiber system, the susceptibility of the
• Intravascular membrane oxygenators are known in different embodiments from the patent literature. So
• WO 2004/016300 A2 discloses as
• Oxygen enrichment of blood with a fiber bundle wherein the fibers are each connected with a first connection to a gas supply and with a second connection to a gas outlet.
• the fiber bundle is twisted by a relative
• catheters The structure of the catheters is not described exactly. In particular, no catheter tube with a blood inlet and blood outlet is shown. Moreover, with respect to catheters, only the supply of gases as
• Membrane oxygenator As exchange medium, only the use of - under standard conditions gaseous - oxygen is disclosed. A carrier medium is evidently not used because only one feed line for the oxygen and no return for any carrier medium is shown.
• the disclosed drive unit is obvious because of its size unsuitable for use as part of an intravascular catheter.
• the pump shown in US 2013/053623 AI is used to support the heart function and thus relates to a completely different
• the present invention therefore relates to a device comprising a catheter for intravascular use, the catheter having a blood inlet and a blood outlet and comprising a membrane, wherein a first side of the membrane is in contact with a carrier medium and wherein the membrane is arranged in the catheter, that at least part of the im
• the catheter can be a conveying device comprise, which is set in operation one
• the invention also relates to a device comprising a catheter for intravascular use, wherein the
• Catheter having a blood inlet and a blood outlet and comprising a membrane, wherein a first side of the membrane defines a lumen for receiving a carrier medium and wherein the membrane is disposed in the catheter such that at least a portion of the blood flowing into the catheter through the blood inlet during operation comes into contact with a first side opposite the second side of the membrane before it leaves the catheter through the blood outlet, wherein the membrane
• the invention relates to a method for removing at least one substance from venous blood for diagnostic purposes using one of said devices, wherein the substance to be sampled corresponds to the substance to be exchanged through the membrane of the catheter of the device.
• the invention relates to a method for treating a human or animal body by an exchange of at least one substance from the blood or in the blood of the
• the carrier medium is a carrier liquid in which the substance to be exchanged is soluble. That The carrier medium is in operation (under standard conditions) in the liquid state. Due to the use of a liquid as a carrier medium, the removal and transport of substances is much more controlled and
• Liquid membrane Liquid membrane
• Conveyor can be made a reduction of the cross section of the catheter due to the relatively lower pressure difference.
• Components are sized so that it is portable and the extracorporeal circuit with or on the console even fits in a pocket.
• the membrane of the device is a membrane suitable for liquids, i. to exchange substances between two
• Liquids configured and set up. Although with such a membrane to some extent an exchange of
• the conveyor comprises a drive unit for generating a torque and connected to the drive unit for transmitting a torque pump rotor.
• the torque is preferably along a shaft
• Pump rotor corresponds to the rotor of an axial pump.
• a simple control of the conveyor, in particular the speed of the rotor, can be achieved when the
• the Drive unit comprises an electric motor.
• the reliability of the conveyor is essentially by the
• the drive unit may be a turbine element
• a drive ratio can be determined by the shape, i. the area, shape and arrangement, the respective wings are determined. This type of drive has the additional advantage that no separate power supply, especially no
• the drive unit is required from outside the body. This will both the
• the pump rotor is connected via a magnetic coupling to the drive unit, wherein the magnetic coupling for
• Torque transmission along a rotational axis has two relatively rotatable coupling parts, each with a permanent magnet.
• a magnetic coupling for example, a
• Central rotary coupling or a face rotary coupling can be used.
• a magnetic coupling has opposite a continuous mechanical connection, e.g. in the form of a continuous wave, the advantage that the transmitted torque is limited.
• the rotor or rotor of the pump thus formed may also preferably be suspended.
• a storage according to the heart support system INCOR of the company "Berlin Heart” may be provided.
• one of the coupling parts comprises an at least partially ferromagnetic Umleitelement which rotatably with the permanent magnet of the coupling part
• the magnetic coupling comprises two relatively rotatable coupling parts, wherein a drive-side
• Coupling part has a drive-side permanent magnet and a driven-side coupling part a the drive-side permanent magnet along the rotation axis opposite and spaced therefrom arranged output side permanent magnet
• one of the coupling parts comprises an at least partially ferromagnetic diverting element, which with the
• Permanent magnet of the coupling part is rotatably connected, wherein a part of the bypass element is arranged radially outside of the opposite permanent magnet.
• the diverting element may be formed, for example, as a thin-walled hollow cylinder, so that at
• Front rotary coupling is largely retained and at the same time between the diverting and the distance from it
• the magnetization direction of the permanent magnets is preferably aligned perpendicular to the axis of rotation, i.
• the magnetic poles run in the circumferential direction from south to north and are - at least in a two-pole design - with respect to the axis of rotation diametrically opposite.
• Coupling dimensions larger volume of the permanent magnet advantageously a smaller axial extent and thus lower radial shear forces can be achieved on the bearings of the coupling parts.
• 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 diverting element may have at least one diamagnetic separation which divides the diverting element into at least two ferromagnetic sections and thus avoids a magnetic short circuit.
• the diverting element also to an opposite permanent magnet remote from the rear side of the rotatably connected permanent magnet extend.
• the diverting element may have a substantially H-shaped longitudinal section, with a transverse web lying perpendicular to the axis of rotation and
• the diverting element may have a hollow cylindrical jacket and preferably be formed with an intermediate bottom arranged at substantially half the height of the jacket.
• Diverter element of the magnetic coupling can be achieved if a diamagnetic shielding element is arranged on a rear side of the permanent magnet facing away from the permanent magnet, which is non-rotatably connected to the diverting element. As a result, field lines extending outside the coupling parts can be avoided and associated losses can be reduced.
• a diamagnetic shielding is arranged, which preferably circumferentially or radially on the outside the diverting element connects.
• the two coupling parts are hermetically separated.
• Such a hermetic separation may be due to a hermetic wall between the two
• Coupling parts of the magnetic coupling can be achieved, which wall should be neither magnetic nor electrically conductive.
• At least one of the coupling parts can be housed in a substantially non-magnetic and electrically non-conductive housing, so that losses due to a Remagnetization of the housing or induced eddy currents in the housing can be avoided.
• the carrier liquid may preferably have a solubility of at least 140 ml C0 2, in particular
• the solubility of C0 2 in arterial blood at 40 mmHg (about 5332.88 Pa) (physically dissolved) is about 2.6 ml / 100 ml and at 90 mmHg (11998.98 Pa) about 0.3 ml / 100 ml.
• the carrier liquid may be a perfluorocarbon or an albumin and / or an electrolyte solution, in particular enriched with specific proteins or glucose derivatives, or
• dialysate which is preferably
• activated carbon or another adsorber was prepared, be.
• the invention can be used with a dialysis fluid as a carrier medium comprising or consisting of demineralized water containing various electrolytes as well as bicarbonate in the same concentration as the physiological extracellular fluid.
• a dialysis fluid as a carrier medium comprising or consisting of demineralized water containing various electrolytes as well as bicarbonate in the same concentration as the physiological extracellular fluid.
• the blood and dialysis fluid may be countercurrently passed along a semipermeable membrane suitable for
• Concentration gradient only for the excess Urämietoxine, but not for the electrolytes, can be achieved. If additional liquid is to be separated, a pressure gradient can be generated, which squeezes solution from the blood. In this way, the invention can be applied for example in heavy metal poisoning and alcohol intoxication.
• the carrier liquid is preferably a family of perfluorocarbons (PFC) liquid which is liquid under physiological conditions and at room temperature.
• PFC perfluorocarbons
• Solubility C0 2 in PFC is 210 ml / dl, that of 0 2 53 ml / dl).
• perfluorocarbons in particular others
• Blood substitutes such as hemoglobin-based
• Oxygen carrier (hemoglobin based oxygen carrier), in question.
• the candidate perfluorocarbons also have a low surface tension and spread very easily on surfaces due to their high propagation coefficient. These properties and their great potential for transporting C0 2 make these fluids particularly suitable for use in flowing through a hollow fiber membrane in order to remove, in particular, part of the continuously formed carbon dioxide for relief of the respiratory effort during spontaneous or mechanically assisted ventilation under low blood flows.
• Hollow fiber membrane is therefore preferably designed such that the minimum exchange surface is available for efficient C0 2 transfer, this is at
• Carrier liquid preferably include albumin.
• the invention may be for performing albumin dialysis
• a membrane is used, which only for the bound to the albumin toxins, as well as
• Carrier liquid bound Through a cycle that can Albumin with the toxins on the dialysis side too
• Dialysis machine but which filters out more of the water-soluble molecules (toxins) and checks the electrolyte content, be vrotown.
• an activated carbon filter that filters toxins that are not anionic may be provided.
• Anionic toxins can be provided.
• albumin Leave circulation via an anion filter.
• the thus purified albumin can then absorb toxins on the membrane again.
• the albumin is released on the blood circulation side and can transport new toxins.
• the blood will
• the carrier liquid with the albumin can also after a
• carrier fluids e.g., dialysates, physiological saline solutions
• Fatty metabolism disorders urea or creatinine, or are generally suitable for therapeutic apheresis.
• membranes are used.
• Particularly preferred carrier liquids are in addition to perfluorocarbon in particular albumin and / or
• Electrolyte solutions or commercially available dialysates which were additionally prepared via an ion exchanger, activated carbon or another adsorber.
• the invention may be used, for example, as an artificial pancreas, wherein the blood through the membrane absorb insulin from the carrier liquid and glucagon to the
• Carrier liquid can be discharged.
• the membrane can be any material that can be discharged.
• the membrane can be any material that can be discharged.
• the invention makes it possible to avoid hypercapnia by using a part the continuously formed carbon dioxide to relieve the work of breathing during spontaneous or mechanical ventilation by a liquid, in particular a perfluorocarbon is removed.
• Perfluorocarbons have a high solubility not for C0 2 but for all respiratory gases, therefore also for 0 2 , N 2 and NO on.
• the gas exchange surface of the membrane used therefore need not be as large as it is for conventional
• intravascular membrane oxygenators is necessary. This allows the catheter to be the size of a conventional dialysis or single port ECMO catheter.
• Oxygen used in conventional intravascular membrane oxygenators is of equal quality to achieve
• the invention can also be used with a carrier liquid
• Toxins can generally be displaced by substances that have greater affinity for the specific binding sites on the protein or lipid than the toxin. These substances are called decoupling substances.
• Entkopplersubstanzen are basically physiological
• Binding sites of the toxin thus causing a shift in chemical equilibrium, and become the toxins
• the released toxins can then be removed from the blood or blood components (enzymatic, adsorptive, membrane processes).
• Carrier liquid may preferably be an ultrafiltration process.
• the exclusion limit ie the molecular weight of the substances, which are retained at about 90%, is determined by the membrane chosen.
• the driving force is a pressure difference between the two membrane sides.
• the recovered ultrafiltrate primarily contains the low molecular weight substances, ie in general the toxin. However, small amounts of protein (about 1%) may also be present in the filtrate. In ultrafiltration and dialysis, the procedures of single passage and recirculation are to be distinguished.
• the membrane of the catheter it is favorable if the membrane is a selectively permeable membrane which is permeable at least to the substance to be exchanged.
• Materials come for example hydrophilic or
• hydrophilized copolymers and hydrophilic polymer blends in question are hydrophilized copolymers and hydrophilic polymer blends in question.
• thermoplastic polyurethane polysulfone (PSU)
• PES Polyethersulfones
• PAES polyacrylethersulfones
• Polyvinylpyrrolidone PVP
• polymethyl methacrylate PMMA
• PA Polyamide
• PAN polyacrylonitrile
• EVOH ethylene-vinyl alcohol copolymer
• CTA Cellulose triacetate
• cellulose nitrate cellulose nitrate
• Membrane material can be used.
• membranes are essentially only PSU or PES, essentially a mixture of PES, PVP and PA (PEPA) or essentially a mixture of PAES, PVP and PA.
• the pore size of the membrane may be between 0.01 ⁇ m and 0.1 ⁇ m.
• the membrane may additionally be coated, for example with heparin.
• a particularly large contact area in a small space can be achieved if the membrane is a hollow-fiber membrane.
• a hollow fiber membrane may comprise up to 20,000 individual capillaries or hollow fibers.
• the diameter of the individual hollow fibers is between 0.01 mm and 1 mm, in particular between 0.1 and 0.5 mm.
• the total surface of the membrane, which forms the contact surface for the exchange of substances, is between 0.01 and up to 10 m 2 , preferably between 0.1 and 1 m 2 .
• the material from which the hollow fibers are formed may be composed of one or more of the above-mentioned components, preference being given to PMP (polymethylpentene).
• PMP polymethylpentene
• Contact surface caused flow resistance can be at least partially compensated by the conveyor.
• Nanocapsules can pass through
• Interfacial polymerization of polymers such as polyacrylates, preferably poly (n-butyl cyanoacrylate) (PACA), as well as poly (lactide coglycolide) (PLGA), albumin are produced.
• PPA poly (n-butyl cyanoacrylate)
• PLGA poly (lactide coglycolide)
• Nanocapsules are characterized by a very small wall thickness of 3-20 nm. They can be filled with perfluorocarbons (PFC). Alternatively or additionally, magnetic particles and fluorescent dyes (such as Nile Red) may also be added to the nanocapsules during manufacture for better specification and identification.
• PFC perfluorocarbons
• magnetic particles and fluorescent dyes such as Nile Red
• microcapsules may be made of silicone, preferably UV-curing silicone, e.g. Semicosil 949UV, by one
• microcapsules have an outer shell of silicone and a filling.
• the filling can be sodium carbonate, potassium carbonate, magnesium carbonate,
• the filling can further carbonic anhydrase or chemical equivalents thereof, such as Cyclen Zn (II) included.
• the filling may consist of PACA nanocapsules (as defined above) accommodated in a carrier medium. Furthermore, the filling of the microcapsules essentially pure
• Capsule material and / or the filling can be admixed with fluorescent dyes.
• color indicators which show a color change (for example, thymol-blue) in the case of pH changes can be added to the filling in order to be able to track the saturation of the substances.
• Such nanocapsules and / or microcapsules can be
• the membrane of the present catheter may be provided with nanocapsules and / or microcapsules.
• nanocapsules and / or microcapsules may also be incorporated into existing polymers such as silicone, e.g. be stirred. They are distributed in the starting material and form, for example, PFC-filled cavities which have the permeability of the
• Polymer layers preferably silicone (Silpuran) bring.
• This bubble films are formed. This increases the stability of the capsules.
• the materials thus produced are particularly suitable for use as a membrane of the present catheter.
• the microcapsules and / or nanocapsules for example with polymers cyanoacrylates or silicone
• films or hollow tubes are used, which films or hollow tubes can be used as a membrane of the present catheter.
• the device according to the invention is particularly suitable for minimally invasive applications, for example in the arm and leg veins.
• the device in the dimensions used in catheter technology (e.g., outer diameter of 2.3 to 12.7 mm or 7 to 40 Fr).
• the dimensions used in catheter technology e.g., outer diameter of 2.3 to 12.7 mm or 7 to 40 Fr.
• the dimensions used in catheter technology e.g., outer diameter of 2.3 to 12.7 mm or 7 to 40 Fr.
• Diameter of the device of 10 mm or smaller preferably 8.7 mm or smaller, in particular 8.0 mm or smaller has been found to be practically particularly suitable.
• the length of the device according to the invention is preferably oriented to the common venous catheter formats, ie about 100 to
• the fibers of the hollow fiber membrane are arranged to a predominant part substantially parallel to a longitudinal extent of the catheter.
• the longitudinal extension of the catheter naturally corresponds to the main flow direction of the blood in the vessel surrounding the catheter during operation.
• the membrane in particular the hollow fiber membrane
• the membrane is folded.
• both ends of the hollow fibers are at the same end of the catheter.
• the catheter has an inlet and an outlet for the carrier liquid, which are connected to an extracorporeal exchange device to form a circulation system with the exchange device, wherein the circulatory system is a pump for
• the replacement device is a membrane oxygenator. It may be in the exchange device but also to absorber (for the deposition of ß 2 -microglobulin, rheumatoid factors, lipids, immunoglobulins or endotoxins), such as activated carbon or resin absorber to membrane devices for diffusion, ultrafiltration and / or convection of substances from the
• Carrier medium or to act other filter devices.
• such a device may be provided with a catheter and an extracorporeal replacement device in a kit, the kit additionally having at least one with the catheter and with the replacement device
• the tube preferably has at least two channels or lines, wherein an inwardly leading channel for supplying the carrier liquid to the catheter and an outgoing channel for discharging the carrier liquid from the catheter are set up.
• the exchange means a portable exchange device, preferably with a
• Carrying device is.
• a carrying device can For example, fasteners for a strap or attachment to a belt or other
• the substance to be taken for diagnosis is a
• Disease indicator of which also endogenous substances, their presence (e.g., antibodies) or quantity (e.g.
• Inflammatory proteins, cytokines, complement factors, etc. are correlated with a disease or its course, in particular e.g. at least one pathogen or at least one antibody, a body toxic substance (e.g.
• Area such as potassium, calcium, etc.
• substance that is otherwise not excreted by the body see storage disorders relating to glucose, copper, etc.
• storage disorders relating to glucose, copper, etc.
• endogenous substance whose quality or quantity correlates with a course of disease, in particular at least one
• disease-specific protein or disease-causing substance e.g., complement, cytokines, interleukins, or antibodies.
• the method may be part of a diagnostic method for measuring blood glucose.
• a device comprising a catheter for intravascular use, wherein the catheter has a blood inlet and a
• Blood outlet and comprising a membrane, wherein a first side of the membrane is in contact with a carrier medium and wherein the membrane is arranged in the catheter such that at least a part of the blood flowing into the catheter through the blood inlet during operation opposes to one of the first side the second side of the membrane comes into contact before it leaves the catheter through the blood outlet, wherein the membrane allows an exchange of at least one substance to be exchanged between the carrier medium and the blood, and wherein the catheter comprises a conveyor, which established is, during operation to compensate at least partially for a pressure difference between the blood inlet and the blood outlet, characterized in that the carrier medium is a carrier liquid, in which the substance to be exchanged is soluble.
• the conveyor means comprises a drive unit for generating a torque and one with the drive unit for
• Transmission of torque associated pump rotor includes.
• Device characterized in that the drive unit comprises an electric motor.
• Device characterized in that the drive unit comprises a turbine element, which is flowed around in operation by the carrier medium.
• Magnetic coupling is connected to the drive unit, wherein the magnetic coupling for torque transmission along a rotational axis has two relatively rotatable coupling parts, each having a permanent magnet.
• ferromagnetic Umleitelement comprises, which with the
• Permanent magnet of the coupling part is rotatably connected, wherein a part of the bypass element is arranged radially outside of the permanent magnet of the other coupling part.
• Device characterized in that the diverting element has at least one diamagnetic separation, which the diverting element in at least two
• Device characterized in that the substance to be exchanged C0 2 , wherein the carrier liquid has a solubility of at least 140 ml C0 2 , in particular at least 180 ml C0 2 , in 100 ml of the carrier liquid at 37 ° C. having.
• Electrolyte solution in particular enriched with specific proteins or glucose derivatives, or a commercial
• dialysate which was preferably additionally treated via an ion exchanger, activated carbon or another adsorber, is.
• Entkopplersubstanz includes.
• Device according to one of embodiments 1 to 11, characterized in that the membrane is a selectively permeable membrane, which is permeable at least for the substance to be exchanged.
• Device characterized in that the membrane is a hollow fiber membrane.
• Device according to one of embodiments 1 to 14, characterized in that the membrane is folded.
• Nanocapsules or microcapsules are connected. 17. Device according to one of embodiments 1 to 16, characterized in that the membrane nanocapsules or
• Microcapsules comprises, wherein the nanocapsules or microcapsules embedded in an otherwise homogeneous carrier material or the membrane of interconnected nanocapsules or
• Microcapsules exists.
• the catheter has an inlet and an outlet for the carrier liquid, which are connected to an extracorporeal exchange means for forming a circulation system with the exchange means, wherein the circulation system comprises a pump for conveying the
• Carrier liquid has.
• Catheter and connected to the exchange tube for transporting a carrier fluid between the catheter and the exchange device.
• the exchange device is a portable exchange device, preferably with a carrying device.
• An apparatus comprising a catheter for intravascular use, wherein the catheter has a blood inlet and a
• Blood outlet and comprising a membrane, wherein a first side of the membrane defines a lumen for receiving a carrier medium and wherein the membrane is arranged in the catheter such that at least a portion of the in operation by the
• Blood inlet into the catheter of flowing blood comes into contact with a first side opposite the second side of the membrane before it leaves the catheter through the blood outlet, the membrane exchanging at least one substance to be exchanged between a carrier medium received in operation in the lumen and the blood allows, by characterized in that the lumen for receiving a
• Carrier liquid in which the substance to be exchanged is soluble is set up as a carrier medium and the membrane allows an exchange between the carrier liquid and the blood during operation.
• Electrolyte solution in particular enriched with specific proteins or glucose derivatives, or a commercial
• dialysate which was preferably additionally treated via an ion exchanger, activated carbon or another adsorber, is set up as a carrier liquid.
• Device according to one of embodiments 22 to 24, characterized in that the catheter comprises a conveyor which is adapted to compensate at least partially during operation, a pressure difference between the blood inlet and the blood outlet.
• Apparatus comprising a catheter for intravascular use, wherein the catheter has a blood inlet and a
• Blood outlet and comprising a membrane, wherein a first side of the membrane is in contact with a carrier medium and wherein the membrane is arranged in the catheter such that at least a part of the blood flowing into the catheter through the blood inlet in operation with one of the first side opposite lying second side of the membrane comes into contact before it leaves the catheter through the blood outlet, wherein the membrane allows an exchange of at least one substance to be exchanged between the carrier medium and the blood, characterized
• the carrier medium is a carrier liquid in which the substance to be exchanged is soluble.
• Method according to embodiment 27, wherein the substance to be extracted is a disease indicator, in particular at least one pathogen, at least one antibody, a toxic substance for the body, one not otherwise through the body
• excretable substance or an endogenous substance whose quality or quantity correlates with a course of disease, in particular at least one disease-specific protein or a substance produced by disease processes.
• Embodiments 22 to 25 with a liquid carrier medium Embodiments 22 to 25 with a liquid carrier medium.
• liquid carrier medium is a perfluorocarbon or an albumin and / or an electrolyte solution, in particular
• Entkopplersubstanz includes.
• Fig. 1 shows schematically a longitudinal section through a device with an intravascular catheter with a lateral Blood inlet and a centrally disposed hollow fiber membrane;
• Fig. 2 shows schematically a longitudinal section through a device with an intravascular catheter with a central
• Blood passage laterally disposed hollow fiber membranes and a proximal return lumen
• Fig. 3 shows schematically a cross section through the catheter along the line III-III in Fig. 2;
• Fig. 4 shows schematically a longitudinal section through a device with an intravascular catheter with a central
• FIG 5 schematically shows a longitudinal section through a device according to FIG 4 with a motor-driven conveyor at the distal end of the blood passage.
• FIG. 6 schematically shows a longitudinal section through a device with an intravascular catheter with laterally arranged hollow-fiber membranes, with lateral blood inlets and with a turbine-driven conveyor at the distal end of the
• Fig. 7 shows a further embodiment of a
• Fig. 1 is a device 1 with an intravascular
• Catheter 2 shown schematically in longitudinal section.
• the catheter 2 is intended to be inserted through a vein and positioned in the inferior or superior vena cava.
• the catheter 2 may in principle be of conventional design and has those properties which are suitable for its use or
• the catheter 2 comprises a
• the catheter tube 3 has a substantially round cross section in the relaxed state.
• the diameter of the catheter tube 3 is adapted to a vein, in particular smaller than the diameter of a vein in which the catheter is to be used.
• the catheter tube 3 consists of a customary for catheters, elastic material,
• Catheter tube 3 is one along the catheter tube 3 extending diaphragm 4 ', in particular a hollow fiber membrane 4, arranged.
• the hollow fiber membrane 4 is shown for simplicity with only a single hollow fiber 5 and in practice comprises a plurality of semipermeable hollow fibers of one of the initially mentioned preferred membrane materials. If the function of the hollow fiber 5 is described below, the corresponding statements apply equally to a second and any further hollow fiber of the hollow-fiber membrane 4
• Hollow fiber membrane 4 is designed such that at the distal end 6 of the catheter 2 via an inlet 7 for a
• Carrier liquid the carrier liquid can be introduced into the hollow fiber membrane 4, which carrier liquid the
• Hollow fiber 5 of the hollow fiber membrane 4 flows through, and that the carrier liquid can be discharged via an outlet 8 for the carrier liquid.
• the carrier liquid therefore flows through the hollow-fiber membrane 4 or its hollow fiber 5 between the
• Hollow fiber 5 are in a connection region 10 by a
• the hollow fiber 5 has a diffraction 13, so that the hollow fiber 5 has a continuous loop-shaped course between the inlet 7 and the outlet 8.
• the intravascular catheter 2 is further designed such that it can be surrounded by blood and flowed through.
• the catheter tube 3 just outside the catheter
• Catheter tube 3 is opened so that the opening one
• Blood outlet 15 forms.
• the blood flow in the catheter 2, in the catheter 2 and out of the catheter 2 is indicated by directional arrows 16.
• the blood flows around the hollow fiber 5 of the hollow-fiber membrane 4, so that at least part of the blood flowing into the catheter 2 during operation through the blood inlet 14 with an outside of the
• Hollow fiber 5 comes into contact, which outside of the first side opposite the second side of the hollow fiber membrane. 4 forms. Due to the material of the hollow fiber 5, this and thus the hollow fiber membrane 4 as a whole allows an exchange of at least one substance to be exchanged between the carrier liquid in the interior of the hollow fiber 5 and the surrounding blood.
• the inlet 7 and the outlet 8 are connected in a connection region 17 with a supply hose 18.
• the feed tube 18 has a coaxial inner tube 19. In the embodiment shown in FIG. 1, the inside of the
• Inner tube 19 formed channel as inlet channel 20 and between the inner tube 19 and the outer jacket of the
• Feed tube 18 formed channel as a drain channel 21 for the carrier liquid.
• the delivery tube is in the connection area 17 by means of an elastic connection compound 22, e.g.
• FIGs. 2 and 3 is another embodiment of a
• Catheter tube 25 corresponds to the catheter 2 described in connection with FIG. 1 and the catheter tube 3, unless otherwise described below.
• the central blood passage 24 extends as an open channel along a longitudinal axis in the center of the catheter 23.
• the blood passage 24 thus connects a central blood inlet 26 at the distal end 27 of the catheter 23 and a central blood outlet 28 at the proximal end 29 of the catheter 23 parallel to
• catheter 23 is a substantially cylindrical
• Hollow fibers 31, 32 are arranged around the central blood passage 24 around and substantially parallel to the longitudinal extent of the catheter 23.
• the hollow fiber membrane 30 is shown for simplicity with only two individual hollow fibers 31, 32 and in practice comprises a plurality of semipermeable
• the first hollow fiber 31 is at the distal end 27 of the catheter 23 with an inlet channel 33 of a
• the second hollow fiber 32 is connected at the distal end 27 of the catheter 23 to a drainage channel 35 of the delivery tube 34. If the function of the first or second hollow fibers 31, 32 is described below, the corresponding explanations apply equally to a respective first part of all further hollow fibers of the hollow-fiber membrane 30
• the second ends of all the hollow fibers 31, 32 in a second annular joining region 38 are also defined by an embedding compound 39 and are bonded to the embedding compound 39, e.g. an epoxy resin.
• the hollow fibers 31, 32 are connected at their second ends to a return lumen 40, which is formed at the distal end 29 of the catheter 23 as an annular channel within the catheter tube 25.
• Hollow-fiber membrane 30 is thus designed such that a carrier liquid introduced into hollow-fiber membrane 30 at the distal end 27 of catheter 23 passes through first hollow fiber 31 of hollow-fiber membrane 30 and at the proximal end 29 of the catheter into reflux lumen 40, to the second hollow fiber 32, the second hollow fiber 32 of the hollow fiber membrane 30 flows through and is discharged via an outlet 42.
• the inside of the hollow fibers 31, 32 thus form a first side of the hollow fiber membrane 30, which is in contact with the carrier liquid.
• Catheter 23 and out of the catheter 23 is indicated by directional arrows 43.
• the blood flows around the hollow fibers 31, 32 of the hollow-fiber membrane 30, so that at least part of the blood flowing into the catheter 23 during operation through the blood inlet 26 with an outside of the Hollow fibers 31, 32 comes into contact, which outside of the first side opposite the second side of the
• Hollow fiber membrane 30 forms. Due to the material of the
• Hollow fibers 31, 32 leave them and thus the hollow fiber membrane 30 in total an exchange at least one exchanged
• FIG. 4 shows a further alternative embodiment variant of the device according to the invention with a catheter 44.
• Catheter tube 45 again corresponds to the catheter 2 or 23 described in connection with FIGS. 1 to 3, unless otherwise described below.
• the hollow-fiber membrane 46 of the catheter 44 forming the membrane 4 'of the catheter, as shown in FIG. 2 is cylindrically arranged around a central blood passage 24 as shown in FIG. 4, but the individual hollow fibers are 47, 48 as in Fig. 1 loop-shaped with a diffraction 13 in the region of a proximal end 49 of the catheter 45 is formed.
• Hollow fiber membrane 46 thus corresponds to a half-height turned outward cylinder.
• the ends 50, 51 of the hollow fibers 47, 48 are secured in an annular joining region 52 by an embedding compound 53 and are bonded to the embedding compound 53, e.g. an epoxy resin.
• the radially inwardly with respect to a central longitudinal axis of the catheter 45 ends 50 of the hollow fibers 47, 48 open into an annular inlet 54 of the hollow fiber membrane 46 for a carrier liquid.
• the radially outer ends 51 of the hollow fibers 47, 48 with respect to a central longitudinal axis of the catheter 45 accordingly open into an annular outlet 55 of the hollow-fiber membrane 46 for a
• Carrier liquid which is arranged concentrically to the inlet 54 and radially outside thereof.
• Hollow fiber membrane 46 is connected to an inlet channel 56 of a
• Hollow fiber membrane 46 is connected to a drainage channel 58 of the
• the feed tube 57 connected.
• the feed tube 57 is
• Hose branches 60 is forked.
• the carrier liquid introduced into the hollow-fiber membrane 46 via the inlet 54 flows through the hollow fibers 47, 48 of the hollow-fiber membrane 46 parallel to the
• the catheter 45 at the distal end 61 has a central blood inlet 62 into the blood passage 24.
• the catheter tube 44 is opened, so that, as in FIG. 1, the opening forms a blood outlet 15. The blood flow in the catheter 45, in the catheter 45 and from the catheter 45 is through
• the blood flows around from the blood inlet 62, the hollow fibers 47, 48 of the hollow fiber membrane 46, so that at least a part of the in operation by the
• FIGS. 5 and 6 each show a conveying device 64, 65 which, in particular in the catheters 23 and 44 shown in FIGS. 2 and 4, preferably each in the blood inlet 26 and 62 can be used. Accordingly, the catheter 44 in Fig. 5 and 6 are shown only schematically and it will be
• the conveyor shown in Fig. 5 comprises a
• Electric motor 68 The electric motor 68 transmits in operation over a shaft 69, a torque on the pump rotor 66.
• the shaft 69 is mounted with an opposite end of the electric motor 68 end 70 in a stator 71.
• the stator 71 is in one
• the pump rotor 66 in turn also has wings 74, which are like a propeller for the axial transport of the upon rotation of the pump rotor 66 between the wings 74th
• the pump rotor 66 is driven by the electric motor 68, which forms a drive unit 85 ', such that an acceleration of the blood flow in the region of the blood inlets and thus an overpressure at the distal end 61 of the catheter 44 is generated.
• the speed of the electric motor 68 is controlled via a controller (not shown) so that achieved
• Catheter tube 45 would be moved, the catheter would have no membrane.
• the electric motor 68 is embedded in an embedding compound 76, which connects the electric motor to the catheter tube 44.
• Fig. 6 shows a further, preferred embodiment for a conveyor 65.
• the conveyor 65 forms the distal end 77 of the catheter 44.
• the conveyor 65 has a pump rotor 78 which rotatably disposed between a magnetic coupling 79 and a pump stator 80 and with a shaft 81 is rotatably mounted in the pump stator 80.
• the Pump stator 80 is attached via side wings 82 in a first connecting ring 83.
• the first connection ring 83 comprises an embedding mass 84 in which the hollow fibers 47, 48 of the hollow-fiber membrane 46 are embedded and connected thereto, the hollow fibers 47, 48 passing through the first connecting ring 83 axially, ie parallel to a longitudinal axis of the catheter 44.
• the first connecting ring 83 is connected to the catheter tube 45 of the catheter 44 on a radial outer side.
• the conveyor 65 further comprises a turbine element 85 as a drive unit 85 ', which is rotatably mounted in a turbine stator 86 about a shaft 87.
• the shaft 87 forms a rotationally fixed connection of the turbine element 85 with the
• Magnetic coupling 79 in particular with a drive-side
• Coupling member 88 The turbine stator 86 is between the
• the turbine stator 86 has side wings 89, with which it is in a in the
• Inner tube 92 of a feed tube 93 is attached.
• the turbine element 85 is accordingly also in the
• the annular inlet 54 and outlet 55 of the hollow fiber membrane 46 is formed on a second connecting ring 98, which - comparable to the connecting portion 52 in Fig. 4 - a
• An embedding mass 99 includes, in which the ends 50, 51 of the hollow fibers 47, 48 are embedded so that they open into the inlet 54 and in the outlet 55. Between the second connection ring 98 and the first connection ring 83, which is arranged proximally of the second connection ring 98, the catheter 44 has lateral blood inlets 100.
• the magnetic coupling 79 includes in addition to the drive side Coupling member 88 has a corresponding output side
• Coupling member 101 which is rotatably connected to the pump rotor 78. Due to the rotatable mounting over the
• Coupling part 101 comprises a driven-side two-pole permanent magnet 102, which rotatably connected to the shaft 81 of the
• Clutch part 88 comprises a drive-side two-pole permanent magnet 103, which rotatably connected to the shaft 87 of the
• Turbine element 85 is connected. The output side
• Permanent magnet 102 is circumferentially surrounded by a substantially cup-shaped Umleitelement 104 with a hollow cylindrical shell. It is between the output side
• Permanent magnet 102 and the bypass element 104 is provided a gap or gap, so that the output-side coupling part 101 contactlessly with the drive-side coupling part 88th
• the diverter 104 is mostly made of ferromagnetic material.
• the jacket of the diverting element 104 is only in a narrow angular range by a
• diamagnetic separation (not shown) interrupted.
• the separation essentially divides the diverting element 104 into two ferromagnetic halves or half shells.
• Separation extending cutting plane is thus perpendicular to a direction of magnetization of the diverter 104th
• Clutch part 101 provided a hermetic separation (not shown).
• the hermetic separation is formed by a sealingly connected to the radial inside of the second connecting ring 98 film.
• Carrier liquid on the wings 97 a torque on the Turbine element 85 applied.
• the turbine element 85 transmits the torque via the shaft 87 on the drive side
• the pump rotor 78 carries with lateral propeller-like wings 105, the blood located between the wings 105 from the blood inlets 100 in
• the conveyor 65 generates in this way a pressure difference between the blood inlets 100 and the proximal end of the
• Blood passage 24 which preferably a pressure difference between the proximal and distal ends (not shown) of the catheter 44 due to the flow resistance of
• Hollow fiber membrane 46 substantially completely compensated.
• the turbine element 85 and the pump rotor 78 are included
• the two conveyors 64, 65 are in the above
• Embodiments each arranged in the region of the distal end 27, 77 of the catheter 44.
• arrangements at any point in the catheter 44 are also conceivable, whereby, as expected, similar advantages can be achieved.
• Turbine element with respect to the respective stators or with multiple stators or a total of only one stator possible without leaving the inventive operation and thus the scope of the invention.
• a hollow-fiber membrane instead of a hollow-fiber membrane, another type of membrane can also be used in the catheter, with the person skilled in the art using the delivery device 64, 65 as expected
• Fig. 7 shows a further embodiment of a
• intravascular catheter 106 which is intended to be inserted through a vein and positioned in the inferior or superior vena cava.
• the catheter 106 may
• the catheter 106 therefore has a
• Catheter tube 107 whose diameter is adapted to the diameter of the vein, in particular slightly smaller than the diameter of the vein.
• the catheter tube 107 consists of a customary for catheters, elastic material,
• biocompatible polyurethane in the catheter tube 107 is a hollow fiber membrane module 108 running along the tube 107 with a hollow-fiber membrane having a multiplicity of gas-permeable but
• liquid-impermeable hollow fibers of any of the aforementioned materials, for example polyethylene or thermoplastic polyurethane.
• the hollow fiber membrane module 108 is configured such that at the distal end of the catheter 106 via a first catheter port 109 in the
• Hollow fiber membrane module 108 a medium which flows through the hollow fibers, can be supplied and via a second
• the medium can be derived.
• the medium which will be discussed in more detail, therefore flows through the hollow fiber membrane module 108 between the first
• FIG. 7 shows a possible embodiment of the
• Hollow-fiber membrane module 108 as a hollow fiber bundle, which between the first catheter port 109 and the second
• Catheter connection 110 in a loop shape along the
• the one ends of the hollow fibers are thus connected to the first catheter port 109 and the second ends to the second catheter port 110.
• the hollow fibers can be encapsulated or bonded together by an epoxy resin or the like.
• the loop-shaped hollow fiber bundle can additionally be twisted or twisted.
• the intravascular catheter 106 is also designed so that it can be surrounded by blood and flow through it.
• the tube 107 for example, just outside the two catheter ports 109, 110 with a number of inlet ports 111 and in
• Outlet openings 112 may be provided.
• the hollow fiber membrane module 108 may be configured so that in one part of the hollow fibers the medium is co-current with the blood and in another part of the hollow fibers the medium in the
• the two catheter ports 109, 110 are shown coaxially positioned in the embodiment shown, but may also, depending on the design of the
• Hollow fiber membrane module 108 be arranged side by side (cf. Fig. 1 or Fig. 2).
• the catheter connections 109, 110 are also flexible, over a section in particular coaxial
• the catheters 2, 23, 44, 106 described so far and shown in FIGS. 1 to 7 can form part of a larger one
• FIG. 8 shows schematically a
• the pump 116 is connected to the
• Feed tube 118 connected.
• Another component is an oxygenator 119 into which the carrier fluid coming from the outlet channel 120 is introduced.
• the oxygenator 119 may be a conventional, commercially available membrane oxygenator 119 'having a gas feed 121 and a gas discharge 122. in the
• Extracorporeal part of the circulation are also a Heat exchanger 123, which contains the carrier liquid
• Components such as pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring pressure measuring devices, facilities for measuring devices.
• Hollow fiber membrane module 108 is pumped, wherein the carrier liquid, the hollow fiber membrane module 108 partly in the flow direction of the blood and partly against the flow direction of the blood
• Embodiment of the invention supplied with ambient air. From the ambient air, the liquid takes through the
• the liquid can be enriched with oxygen in the context of its oxygen capacity by supplying oxygen in the oxygenator 119.
• the heated to body temperature carrier liquid is fed back into the hollow fiber membrane module 108 in the circuit.
• the efficiency of the gas transfer in the hollow fiber membrane module 108 is characterized in that the carrier liquid in the flow direction of the blood as well as against the flow direction of the blood through the
• Hollow fiber membrane module 108 is pumped, especially high.
• the device can also be used to remove other substances, for example endotoxins, from the blood.
• a suitably suitable liquid eg commercially available
• the dialysate can be removed from a tank, pumped through the catheter and then collected in a separate tank for disposal.
• a filter unit e.g. with an adsorption filter, be provided so that a substance to be exchanged in the filter unit is separated from the carrier medium.
• the device according to the invention is portable, small
• Device according to the invention can also be used in any conventional extracorporeal method as an additional device, especially in conventional dialysis circuits.

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• 2016
  • 2016-10-14 EP EP16781481.3A patent/EP3362119B1/de active Active
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  • 2016-10-14 CN CN201680071107.2A patent/CN108472424B/zh not_active Expired - Fee Related
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  • 2016-10-14 CA CA3000908A patent/CA3000908A1/en not_active Abandoned
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  • 2016-10-14 WO PCT/EP2016/074776 patent/WO2017064285A1/de not_active Ceased
  • 2016-10-14 KR KR1020187013572A patent/KR20180075550A/ko not_active Abandoned
  • 2016-10-14 BR BR112018007521-3A patent/BR112018007521A2/pt not_active IP Right Cessation
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• 2018
  • 2018-04-04 ZA ZA2018/02187A patent/ZA201802187B/en unknown
• 2021
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