CA2352234A1 - Electric motor cooled by a fluid and having high specific power - Google Patents
Electric motor cooled by a fluid and having high specific power Download PDFInfo
- Publication number
- CA2352234A1 CA2352234A1 CA002352234A CA2352234A CA2352234A1 CA 2352234 A1 CA2352234 A1 CA 2352234A1 CA 002352234 A CA002352234 A CA 002352234A CA 2352234 A CA2352234 A CA 2352234A CA 2352234 A1 CA2352234 A1 CA 2352234A1
- Authority
- CA
- Canada
- Prior art keywords
- motor
- motor housing
- polymer material
- filler
- electric motor
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02K—DYNAMO-ELECTRIC MACHINES
- H02K9/00—Arrangements for cooling or ventilating
- H02K9/19—Arrangements for cooling or ventilating for machines with closed casing and closed-circuit cooling using a liquid cooling medium, e.g. oil
- H02K9/197—Arrangements for cooling or ventilating for machines with closed casing and closed-circuit cooling using a liquid cooling medium, e.g. oil in which the rotor or stator space is fluid-tight, e.g. to provide for different cooling media for rotor and stator
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02K—DYNAMO-ELECTRIC MACHINES
- H02K5/00—Casings; Enclosures; Supports
- H02K5/02—Casings or enclosures characterised by the material thereof
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02K—DYNAMO-ELECTRIC MACHINES
- H02K9/00—Arrangements for cooling or ventilating
- H02K9/22—Arrangements for cooling or ventilating by solid heat conducting material embedded in, or arranged in contact with, the stator or rotor, e.g. heat bridges
- H02K9/223—Heat bridges
-
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
- A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
- A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
- A61M60/554—Regulation using real-time blood pump operational parameter data, e.g. motor current of blood pressure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
- A61M60/81—Pump housings
- A61M60/816—Sensors arranged on or in the housing, e.g. ultrasound flow sensors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
- A61M60/818—Bearings
- A61M60/825—Contact bearings, e.g. ball-and-cup or pivot bearings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
- A61M60/827—Sealings between moving parts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/422—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being electromagnetic, e.g. using canned motor pumps
Abstract
Disclosed is a micromotor with a motor housing (20) formed of polymer material. Said motor housing (20) surrounds the stator (24). The motor drives a pump part (12), which pushes fluid along the motor housing (20). The polymer material of the motor housing (20) contains an electrically isolating filler having caloric conductibility, especially Al2O3. Thereby, the temperatures arising in the motor housing are reduced. Furthermore, the hollow spaces of the coils (24a) of the stator can be filled up with a polymer material which contains a filler with caloric conductibility. The internal temperature of the motor is reduced as a result of the heat carried away to the fluid flowing around the motor. The micromotor is particularly useful for an intravascular blood pump.
Description
07/19/01 15: 28 FAX 418 862 7881 ~ 02352234 2001-05-22 __ l~ OOZ/O11 Electric motor cooled by a fluid and having hiah specific power The invention refers to a fluid-cooled electric motor with high specific power comprising a motor housing injection molded from a polymer material and enclosing a stator, and in particular to a micromotor that can be introduced into the vascular system of a body to drive a blood pump situated within the body.
WO 98/44619 describes a rnicromvtor that is part of a blood pump to be introduced into the body of a patient. The micromotvr has a motor housing injection molded from polymer material and having an outer diameter no larger than 8.0 mm. The motor is part of a blood pump pumping blood in the vascular system of a patient, the blood flowing along the motor housing, thereby cooling the motor. A relatively high temperature is generated in the motor housing, l~ since polymer material has poor thermal conductivity. Due to the thermos bottle effect,-temperatures of 60' C occur. Although the motor housing is cooled by the blood flowing along the same at a temperature of 3T C, the shaft extending from the motor housing has a higher temperature. There is a risk that the temperature-critical medium blood is damaged by too high a shaft temperature. Seals seating a shaft having a high temperature are subject to greaterwear, thereby reducing the service life ofthe micromotor. Further, consideration must be given to the fact that the efficiency decreases at a high inner temperature within the motor. With micromvtors in particular, which often rely on battery power for operation, a high efficiency is important. An excessive inner temperature in the motorand the accompanying deterioration of efficiency, the mechanically available power Is also reduced.
It. is the object of the invention to provide a fluid-cooled micrvmotor with improved thermal dissipation.
According to the invention, the object is solved with the features mentioned in claim 1. In the present micromotor, the polymer material of the motor housing includes a thermally conductive electrically insulating filler. This filler 07/19/01 15:28 FAX 418 862 7681 CA 02352234 2001-05-22 - ~003/O11 causes the motor housing to have a high conductivity so thatthe heat occurring inside the housing can be transferred better into the surrounding blood.
Preferably, the filler is a ceramic material, in particular AIs03. Due to this material, given a corresponding filling amount, the thermal conductivity of thermoplastics or duroplastics can be increased significantly from a typical 0.05 W/mK to up to 2 W/mK without the electric conductivity increasing. It has been found that at a fluid temperature of 3T C , the internal temperature of the motor can be reduced from an initial 50' C to between 40' C and 45' C. Within the motor, no thermal build-up occurs, since the thermally conductive motor housing provides for a bettertransfer ofthe heatto the blood.
Therefiore, the components of the electric motor are subjected to a lesser thermal stress and, thus, also to a lesser wear. Moreover, the motor can be operated with improved efficiency.
The length of the motor housing is at least twice the outer diameter of this housing. Thus, it is an elongate motor housing with a small diameter. Such motor housing has a large surface relative to the volume. The thermally conductive filler contained in the housing wall, in combination with the large housing surface, allows for an effective thermal transfer to a medium flowing along the housing. Preferably, the length of the motor housing is at least 2.5 times, in particular at least three times, the outer diameter.
The filler is also advantageous in the manufacture ofthe micromotvr by injection molding or in vacuum molding, since a large amount of filler reduces the curing time of a duromer because ofthe lesserduromerthicknesses and the improved thermal conductivity. Thus, the heat curing time in an oven is significantly reduced.
The amount of filler should be at least 40 percent by weight to achieve a significant increase in the thermal conductivity of the matrix material. The 07/19/01 15:28 FAX 416 882 7881 cA 02352234 2001-05-22 _ __ _ _ X004/011 filler, initially present as a fine powder, is mixed into the liquid polymer material, whereupon the forming is done by injection molding, drenching, and the like.
An important insulator within a micromotoris formed by the wire coils.
Cavities filled with air exist between the windings, which form an ideal heat insulator.
Moreover, the individual wires are coated with insulating sheaths that also present good thermal insulators. According to a preferred embodiment of the invention, which is of independent importance, the cavities of the stator coils are filled with a polymer material including a thermally conductive filler.
Thereby, the coils become good thermal conductors, where the current-induced heat generated in the coils is dissipated to the yoke and/or the motor housing with little thermal resistance. The polymer material filling the cavities causes an improved heat transfer to the iron yoke sheet arrangement which in turn passes the heat on to the motor housing. Introducing the filler-loaded polymer material into the cavities of the coils is suitably done by drenching or by casting under a combination of vacuum and pressure, where all cavities are intentionally filled with thermally conductive polymer material.
The following is a detailed description ofan embodiment ofthe invention taken ZO in conjunction with the drawings.
In the Figures:
Fig. 1. is a longitudinal section ofthe micromotorand the pump connected thereto, and Fig. 2 is an enlarged representation of the detail II of Fig. 1.
Fig. 1 described below already forms subject matter of WO 98/4467.9.
07/19/01 15 : 28 FAX ..416 882 7881 CA 02352234 2001-05-22 -- . . __ _ , ~
WO 98/44619 describes a rnicromvtor that is part of a blood pump to be introduced into the body of a patient. The micromotvr has a motor housing injection molded from polymer material and having an outer diameter no larger than 8.0 mm. The motor is part of a blood pump pumping blood in the vascular system of a patient, the blood flowing along the motor housing, thereby cooling the motor. A relatively high temperature is generated in the motor housing, l~ since polymer material has poor thermal conductivity. Due to the thermos bottle effect,-temperatures of 60' C occur. Although the motor housing is cooled by the blood flowing along the same at a temperature of 3T C, the shaft extending from the motor housing has a higher temperature. There is a risk that the temperature-critical medium blood is damaged by too high a shaft temperature. Seals seating a shaft having a high temperature are subject to greaterwear, thereby reducing the service life ofthe micromotor. Further, consideration must be given to the fact that the efficiency decreases at a high inner temperature within the motor. With micromvtors in particular, which often rely on battery power for operation, a high efficiency is important. An excessive inner temperature in the motorand the accompanying deterioration of efficiency, the mechanically available power Is also reduced.
It. is the object of the invention to provide a fluid-cooled micrvmotor with improved thermal dissipation.
According to the invention, the object is solved with the features mentioned in claim 1. In the present micromotor, the polymer material of the motor housing includes a thermally conductive electrically insulating filler. This filler 07/19/01 15:28 FAX 418 862 7681 CA 02352234 2001-05-22 - ~003/O11 causes the motor housing to have a high conductivity so thatthe heat occurring inside the housing can be transferred better into the surrounding blood.
Preferably, the filler is a ceramic material, in particular AIs03. Due to this material, given a corresponding filling amount, the thermal conductivity of thermoplastics or duroplastics can be increased significantly from a typical 0.05 W/mK to up to 2 W/mK without the electric conductivity increasing. It has been found that at a fluid temperature of 3T C , the internal temperature of the motor can be reduced from an initial 50' C to between 40' C and 45' C. Within the motor, no thermal build-up occurs, since the thermally conductive motor housing provides for a bettertransfer ofthe heatto the blood.
Therefiore, the components of the electric motor are subjected to a lesser thermal stress and, thus, also to a lesser wear. Moreover, the motor can be operated with improved efficiency.
The length of the motor housing is at least twice the outer diameter of this housing. Thus, it is an elongate motor housing with a small diameter. Such motor housing has a large surface relative to the volume. The thermally conductive filler contained in the housing wall, in combination with the large housing surface, allows for an effective thermal transfer to a medium flowing along the housing. Preferably, the length of the motor housing is at least 2.5 times, in particular at least three times, the outer diameter.
The filler is also advantageous in the manufacture ofthe micromotvr by injection molding or in vacuum molding, since a large amount of filler reduces the curing time of a duromer because ofthe lesserduromerthicknesses and the improved thermal conductivity. Thus, the heat curing time in an oven is significantly reduced.
The amount of filler should be at least 40 percent by weight to achieve a significant increase in the thermal conductivity of the matrix material. The 07/19/01 15:28 FAX 416 882 7881 cA 02352234 2001-05-22 _ __ _ _ X004/011 filler, initially present as a fine powder, is mixed into the liquid polymer material, whereupon the forming is done by injection molding, drenching, and the like.
An important insulator within a micromotoris formed by the wire coils.
Cavities filled with air exist between the windings, which form an ideal heat insulator.
Moreover, the individual wires are coated with insulating sheaths that also present good thermal insulators. According to a preferred embodiment of the invention, which is of independent importance, the cavities of the stator coils are filled with a polymer material including a thermally conductive filler.
Thereby, the coils become good thermal conductors, where the current-induced heat generated in the coils is dissipated to the yoke and/or the motor housing with little thermal resistance. The polymer material filling the cavities causes an improved heat transfer to the iron yoke sheet arrangement which in turn passes the heat on to the motor housing. Introducing the filler-loaded polymer material into the cavities of the coils is suitably done by drenching or by casting under a combination of vacuum and pressure, where all cavities are intentionally filled with thermally conductive polymer material.
The following is a detailed description ofan embodiment ofthe invention taken ZO in conjunction with the drawings.
In the Figures:
Fig. 1. is a longitudinal section ofthe micromotorand the pump connected thereto, and Fig. 2 is an enlarged representation of the detail II of Fig. 1.
Fig. 1 described below already forms subject matter of WO 98/4467.9.
07/19/01 15 : 28 FAX ..416 882 7881 CA 02352234 2001-05-22 -- . . __ _ , ~
Fig. 1 illustrates an intravascular blood pump 10, i.e. a blood pump that can be pushed through the blood vessels of a patient so as to arrive in the heart.
In general, the outer diameter of such a blood pump is nowhere larger than 8 mm.
The pump 10 has a drive portion 11 and a pump portion 12 rigidly connected thereto. The drive portion 11 includes an electric micromotor 21 with an elongate cylindrical housing 20. At the rear end, the housing 20 is closed by an end wall adjoined in a seating manner by a flexible catheter 14. Electric wires 23 for power supply to and control vfthe electric motor 21 extend through the catheter 14, together with further wires 23a connected to sensors of the blood pump 10.
In a conventional manner, the stator 24 of the motor has a plurality of circumferentially distributed coils 24a, as welt as a magnetic yoke z4b made of metal sheets and extending longitudinally. It is extrusion-coated with the motor housing 20. The stator 24 encloses the rotor 26 connected to the motor shaft 25 and consisting of permanent magnets magnetized in the direction of action. A bearing 27 supports the rear end of the motor shaft in the motor housing or the end wall 22. The shaft extends along the entire length of the motor housing 20 and projects forward therefrom.
The front end of the motor housing is formed by a stationary hub member that is an integral part of the housing 20. The outer diameter of the hub 25 member tapers towards the front end where a bearing 33 for supporting the motor shaft 25 is provided. This bearing is simultaneously designed as a shaft seal.
The motor shaft 25 protrudes forward from the hub member 30 and carries 30 an impeller wheel 34 with a hub 35 sitting on the shaft end and blades 36 or pump vanes projecting therefrom and being inclined with respect to the ~07/19/O1 15:29_FAX 418 882 7881 ~ 02352234 2001-05-22 _ -_ 1~006/O11 axis ofthe impelferwheel 34. The impeller wheel 34 is contained in a cylindrical pump housing 32 that is connected tv a ring 38 on the hub member 30, the connection being established through three circumferentially distributed webs 39. It is visible that the motor housing 20 and the pump housing 32 are rigidly 5 connected and have the same outer diameter, and that the diameter of the pump 10 is nowhere larger than this outer diameter.
During the rotation of the impeller wheel 34, blood is taken in through the take-in port 37 of the pump housing 32 and driven to the rear in the axial direction within the pump housing 32. Through the annular gap between the pump housing 32 and the motor housing 20, the blood flows outward along the hub member 30 to flow further along the motor housing 20. This guarantees the dissipation of the heat generated in the drive, without any damage to the blood caused by excessive surface temperatures (above 41' C) on the motor housing 20.
It is also possible to operate the pump portion 12 with the supply direction reversed, where the blood is drawn along the motor housing and exits axially from the front end opening 37.
A pressure sensor 68 is embedded in the circumferential wall of the motor housing 20, which communicates with a line z3a. This line z3a is encapsulated in the motor housing 20 and extends through the front wall 22 into the catheter 14. At the proximal end of the catheter, the line 23a and the wire 23 may be connected to an extracorporeal control device that controls the operation of the pump 10.
The micromotor 21 is manufactured by injection molding using an injection mold into which a mandrel is inserted that carries the stator components 24a, 24b. Polymer material is then injected into the mold. Thereafter, the injection 07/1,9/01 15: 29 FAX 416 _ 882 7881 CA 02352234 2001-05-22 - _ C~ 007/011 mold and the mandrel are removed from the motor housing 20 and the rotor 26 is finally mounted through the opening 31 of the hub member 30.
The polymer material used is preferably a liquid epoxy resin including a filler percentage of at least 40°/o by weight. The filler used is a fine powder of AL.~03.
The current-induced heat generated in the coils 24a of the stator 24 is first transferred to the yoke arrangement 24b and, through heat transfer, from there to the motor housing 20. Since the motor housing 20 has a good heat conductivity, there is a low temperature gradient to the blood flowing around the motor housing at a temperature of 37' C.
Fig. 2 illustrates the wire windings 40 of a coil 24a, where each wire is provided with an insulating sheath 41. The spaces between the wire windings yr their insulations are filled with polymer material 42 containing AIz43 as a filler.
Again the filler amount is at feast 40% by weight. The polymer material 42 filling the cavities is in full surface contact with the yoke sheet arrangement 24b, which is in full surface contact with the motor housing Z0.
Due to the improved cooling, a high mechanical power output of 5 W can be achieved at a = 30,000 rpm. Because of the substantially improved thermal conductivity in all motor components and the substantially improved heat coupling at the transition between coil, yoke and motor housing, the temperature inside the motor can be reduced significantly.
Thus, in the structure described, the transfer of 10 W of heat from within the motor tv the outside requires a mere driving temperature difference of ~a = 5 - 8 K opposed to 0~ = 1.8 - 25 K when using a non-filled polymer.
The complete filling of all winding cavities with polymer material 42 further allows for a smooth and insulating coil coating 43 on the inner surface of the 07/19/01 15: 29 FAX 418 882 7881 CA 02352234 2001-05-22 ~ 008/011 coil, When the motor is designed as a brush-less synchronous machine, it is possible to drive the motorFlled with liquid on the inside, provided the coifs are fully encapsulated.
In general, the outer diameter of such a blood pump is nowhere larger than 8 mm.
The pump 10 has a drive portion 11 and a pump portion 12 rigidly connected thereto. The drive portion 11 includes an electric micromotor 21 with an elongate cylindrical housing 20. At the rear end, the housing 20 is closed by an end wall adjoined in a seating manner by a flexible catheter 14. Electric wires 23 for power supply to and control vfthe electric motor 21 extend through the catheter 14, together with further wires 23a connected to sensors of the blood pump 10.
In a conventional manner, the stator 24 of the motor has a plurality of circumferentially distributed coils 24a, as welt as a magnetic yoke z4b made of metal sheets and extending longitudinally. It is extrusion-coated with the motor housing 20. The stator 24 encloses the rotor 26 connected to the motor shaft 25 and consisting of permanent magnets magnetized in the direction of action. A bearing 27 supports the rear end of the motor shaft in the motor housing or the end wall 22. The shaft extends along the entire length of the motor housing 20 and projects forward therefrom.
The front end of the motor housing is formed by a stationary hub member that is an integral part of the housing 20. The outer diameter of the hub 25 member tapers towards the front end where a bearing 33 for supporting the motor shaft 25 is provided. This bearing is simultaneously designed as a shaft seal.
The motor shaft 25 protrudes forward from the hub member 30 and carries 30 an impeller wheel 34 with a hub 35 sitting on the shaft end and blades 36 or pump vanes projecting therefrom and being inclined with respect to the ~07/19/O1 15:29_FAX 418 882 7881 ~ 02352234 2001-05-22 _ -_ 1~006/O11 axis ofthe impelferwheel 34. The impeller wheel 34 is contained in a cylindrical pump housing 32 that is connected tv a ring 38 on the hub member 30, the connection being established through three circumferentially distributed webs 39. It is visible that the motor housing 20 and the pump housing 32 are rigidly 5 connected and have the same outer diameter, and that the diameter of the pump 10 is nowhere larger than this outer diameter.
During the rotation of the impeller wheel 34, blood is taken in through the take-in port 37 of the pump housing 32 and driven to the rear in the axial direction within the pump housing 32. Through the annular gap between the pump housing 32 and the motor housing 20, the blood flows outward along the hub member 30 to flow further along the motor housing 20. This guarantees the dissipation of the heat generated in the drive, without any damage to the blood caused by excessive surface temperatures (above 41' C) on the motor housing 20.
It is also possible to operate the pump portion 12 with the supply direction reversed, where the blood is drawn along the motor housing and exits axially from the front end opening 37.
A pressure sensor 68 is embedded in the circumferential wall of the motor housing 20, which communicates with a line z3a. This line z3a is encapsulated in the motor housing 20 and extends through the front wall 22 into the catheter 14. At the proximal end of the catheter, the line 23a and the wire 23 may be connected to an extracorporeal control device that controls the operation of the pump 10.
The micromotor 21 is manufactured by injection molding using an injection mold into which a mandrel is inserted that carries the stator components 24a, 24b. Polymer material is then injected into the mold. Thereafter, the injection 07/1,9/01 15: 29 FAX 416 _ 882 7881 CA 02352234 2001-05-22 - _ C~ 007/011 mold and the mandrel are removed from the motor housing 20 and the rotor 26 is finally mounted through the opening 31 of the hub member 30.
The polymer material used is preferably a liquid epoxy resin including a filler percentage of at least 40°/o by weight. The filler used is a fine powder of AL.~03.
The current-induced heat generated in the coils 24a of the stator 24 is first transferred to the yoke arrangement 24b and, through heat transfer, from there to the motor housing 20. Since the motor housing 20 has a good heat conductivity, there is a low temperature gradient to the blood flowing around the motor housing at a temperature of 37' C.
Fig. 2 illustrates the wire windings 40 of a coil 24a, where each wire is provided with an insulating sheath 41. The spaces between the wire windings yr their insulations are filled with polymer material 42 containing AIz43 as a filler.
Again the filler amount is at feast 40% by weight. The polymer material 42 filling the cavities is in full surface contact with the yoke sheet arrangement 24b, which is in full surface contact with the motor housing Z0.
Due to the improved cooling, a high mechanical power output of 5 W can be achieved at a = 30,000 rpm. Because of the substantially improved thermal conductivity in all motor components and the substantially improved heat coupling at the transition between coil, yoke and motor housing, the temperature inside the motor can be reduced significantly.
Thus, in the structure described, the transfer of 10 W of heat from within the motor tv the outside requires a mere driving temperature difference of ~a = 5 - 8 K opposed to 0~ = 1.8 - 25 K when using a non-filled polymer.
The complete filling of all winding cavities with polymer material 42 further allows for a smooth and insulating coil coating 43 on the inner surface of the 07/19/01 15: 29 FAX 418 882 7881 CA 02352234 2001-05-22 ~ 008/011 coil, When the motor is designed as a brush-less synchronous machine, it is possible to drive the motorFlled with liquid on the inside, provided the coifs are fully encapsulated.
Claims (6)
1. A fluid-cooled electric motor with a motor housing (20) made of polymer material and enclosing a stator (24), the length of the motor housing being at least twice the outer diameter of the motor housing, characterized in that the polymer material of the motor housing (20) contains a thermally conductive, electrically insulating filler in an amount of at least 40 percent by weight.
2. The electric motor of claim 1, wherein the filler comprises Al2O3.
3. The electric motor in particular of claim 1 or 2, wherein the stator (24) comprises coils whose cavities are filled with a polymer material (42) including a thermally conductive filler.
4. The electric motor of claim 3, wherein the polymer material (42) filling the cavities is in thermally conductive contact with a surrounding yoke sheet arrangement (24b).
5. The electric motor of one of claims 1 to 4, wherein a pump portion (12) driven by the motor also includes filler.
6. The electric motor of claim 3 or 4, wherein the coil has a smooth insulating inner surface (43) made of said polymer material.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE29821564.0 | 1998-12-02 | ||
| DE29821564U DE29821564U1 (en) | 1998-12-02 | 1998-12-02 | Fluid-cooled electric motor with high power density |
| PCT/DE1999/003748 WO2000033446A1 (en) | 1998-12-02 | 1999-11-26 | Electric motor cooled by a fluid and having high specific power |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2352234A1 true CA2352234A1 (en) | 2000-06-08 |
Family
ID=8066146
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002352234A Abandoned CA2352234A1 (en) | 1998-12-02 | 1999-11-26 | Electric motor cooled by a fluid and having high specific power |
Country Status (16)
| Country | Link |
|---|---|
| EP (1) | EP1142084B1 (en) |
| JP (1) | JP5093869B2 (en) |
| KR (1) | KR20010086066A (en) |
| CN (1) | CN1329770A (en) |
| AT (1) | ATE302495T1 (en) |
| AU (1) | AU755665B2 (en) |
| BR (1) | BR9915843A (en) |
| CA (1) | CA2352234A1 (en) |
| CZ (1) | CZ20011928A3 (en) |
| DE (3) | DE29821564U1 (en) |
| IL (1) | IL143165A0 (en) |
| NO (1) | NO20012498L (en) |
| PL (1) | PL348519A1 (en) |
| RU (1) | RU2001117822A (en) |
| WO (1) | WO2000033446A1 (en) |
| ZA (1) | ZA200104258B (en) |
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| US9327068B2 (en) | 1999-09-03 | 2016-05-03 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| EP4034221A4 (en) * | 2019-09-25 | 2023-10-11 | Shifamed Holdings, LLC | Catheter blood pumps and collapsible pump housings |
| US11964145B2 (en) | 2019-07-12 | 2024-04-23 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of manufacture and use |
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| WO2006133209A1 (en) | 2005-06-06 | 2006-12-14 | The Cleveland Clinic Foundation | Blood pump |
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| WO2010106157A2 (en) * | 2009-03-20 | 2010-09-23 | Kaltenbach & Voigt Gmbh | Electric motor arrangement for a medical, especially dental, tool holder |
| JP5453644B2 (en) | 2009-06-09 | 2014-03-26 | ミネベア株式会社 | Micro rotor member and rotating electric machine |
| DE102009037655A1 (en) * | 2009-08-14 | 2011-02-17 | Wilo Se | Production of the motor stator of a canned pump |
| DE102010044639A1 (en) | 2010-09-07 | 2012-03-08 | Innovative Fertigungstechnologie Gmbh (Ift) | Cooling device for electric motor of submersible pump, has heat exchanger provided with closed inner cooling circuit, and tubular parts respectively provided for cooling medium supply and -discharge and lying in region of cooling layer |
| CA2868853C (en) | 2012-03-26 | 2021-02-09 | Procyrion, Inc. | Systems and methods for fluid flows and/or pressures for circulation and perfusion enhancement |
| AU2013259287B2 (en) | 2012-05-11 | 2017-02-02 | Heartware, Inc. | Silver motor stator for implantable blood pump |
| EP3128654A1 (en) * | 2014-03-31 | 2017-02-08 | Namiki Seimitsu Houseki kabushikikaisha | Micro motor, micro-geared motor using micro motor, and micro motor manufacturing method |
| CA2999986A1 (en) | 2015-09-25 | 2017-03-30 | Procyrion, Inc. | Non-occluding intravascular blood pump providing reduced hemolysis |
| FR3042325B1 (en) * | 2015-10-13 | 2017-11-17 | Ifp Energies Now | THERMAL INSULATION DEVICE BETWEEN A TURBINE WHOSE WHEEL IS DRIVEN IN ROTATION BY A HOT FLUID AND AN ELECTRIC GENERATOR WITH A ROTOR FITTED TO THIS WHEEL, IN PARTICULAR FOR A TURBOGENERATOR. |
| EP3634528B1 (en) | 2017-06-07 | 2023-06-07 | Shifamed Holdings, LLC | Intravascular fluid movement devices, systems, and methods of use |
| CN107412894A (en) * | 2017-08-08 | 2017-12-01 | 长治市久安人工心脏科技开发有限公司 | A kind of heat sink of implantable cardiac auxiliary blood pump |
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| DE102018201030A1 (en) | 2018-01-24 | 2019-07-25 | Kardion Gmbh | Magnetic coupling element with magnetic bearing function |
| EP4085965A1 (en) | 2018-02-01 | 2022-11-09 | Shifamed Holdings, LLC | Intravascular blood pumps and methods of use and manufacture |
| CA3094838A1 (en) * | 2018-03-23 | 2019-09-26 | Abiomed Europe Gmbh | Method of manufacturing a blood pump |
| DE102018208853A1 (en) | 2018-06-05 | 2019-12-05 | Magna Powertrain Bad Homburg GmbH | pump |
| DE102018211327A1 (en) | 2018-07-10 | 2020-01-16 | Kardion Gmbh | Impeller for an implantable vascular support system |
| US11654275B2 (en) | 2019-07-22 | 2023-05-23 | Shifamed Holdings, Llc | Intravascular blood pumps with struts and methods of use and manufacture |
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| IL293625A (en) | 2019-12-03 | 2022-08-01 | Procyrion Inc | Blood pumps |
| AU2020403115A1 (en) | 2019-12-13 | 2022-07-14 | Procyrion, Inc. | Support structures for intravascular blood pumps |
| DE102020102474A1 (en) | 2020-01-31 | 2021-08-05 | Kardion Gmbh | Pump for conveying a fluid and method for manufacturing a pump |
| DE102021212835A1 (en) | 2021-11-16 | 2023-05-17 | Volkswagen Aktiengesellschaft | Stator with end winding cooling, electric machine, motor vehicle and manufacturing process |
| TW202337515A (en) * | 2022-01-28 | 2023-10-01 | 德商阿比奥梅德歐洲有限公司 | Blood pump |
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| CA938331A (en) * | 1970-01-29 | 1973-12-11 | W. Dochterman Richard | Dynamoelectric machine and method of making same |
| CA921097A (en) * | 1970-01-29 | 1973-02-13 | W. Dochterman Richard | Wet motor |
| JPS52137601A (en) * | 1976-05-12 | 1977-11-17 | Hitachi Ltd | Resin mold stator |
| JPS5442603A (en) * | 1977-09-09 | 1979-04-04 | Hitachi Ltd | Plastic resin moulded electric motor |
| JPS55155530A (en) * | 1979-05-23 | 1980-12-03 | Mitsubishi Electric Corp | Canned motor |
| DE3738592C1 (en) * | 1987-11-13 | 1989-05-24 | Licentia Gmbh | Electric motor for driving a liquid pump, and a method for its production |
| JP2823412B2 (en) * | 1992-02-21 | 1998-11-11 | ファナック株式会社 | Motor cooling device |
| US5783888A (en) * | 1994-03-17 | 1998-07-21 | Fuji Electric Co., Ltd. | Rotary electric machine |
| DE19613564C1 (en) * | 1996-04-04 | 1998-01-08 | Guenter Prof Dr Rau | Intravascular blood pump |
| US5964694A (en) * | 1997-04-02 | 1999-10-12 | Guidant Corporation | Method and apparatus for cardiac blood flow assistance |
-
1998
- 1998-12-02 DE DE29821564U patent/DE29821564U1/en not_active Expired - Lifetime
-
1999
- 1999-11-26 BR BR9915843-4A patent/BR9915843A/en not_active Application Discontinuation
- 1999-11-26 CN CN99813971A patent/CN1329770A/en active Pending
- 1999-11-26 KR KR1020017006754A patent/KR20010086066A/en not_active Application Discontinuation
- 1999-11-26 JP JP2000585984A patent/JP5093869B2/en not_active Expired - Lifetime
- 1999-11-26 AU AU18566/00A patent/AU755665B2/en not_active Expired
- 1999-11-26 EP EP99962070A patent/EP1142084B1/en not_active Expired - Lifetime
- 1999-11-26 CZ CZ20011928A patent/CZ20011928A3/en unknown
- 1999-11-26 AT AT99962070T patent/ATE302495T1/en not_active IP Right Cessation
- 1999-11-26 IL IL14316599A patent/IL143165A0/en unknown
- 1999-11-26 DE DE19982578T patent/DE19982578D2/en not_active Expired - Fee Related
- 1999-11-26 RU RU2001117822/09A patent/RU2001117822A/en not_active Application Discontinuation
- 1999-11-26 WO PCT/DE1999/003748 patent/WO2000033446A1/en active IP Right Grant
- 1999-11-26 PL PL99348519A patent/PL348519A1/en unknown
- 1999-11-26 DE DE59912438T patent/DE59912438D1/en not_active Expired - Lifetime
- 1999-11-26 CA CA002352234A patent/CA2352234A1/en not_active Abandoned
-
2001
- 2001-05-21 NO NO20012498A patent/NO20012498L/en not_active Application Discontinuation
- 2001-05-24 ZA ZA200104258A patent/ZA200104258B/en unknown
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US10279095B2 (en) | 1999-09-03 | 2019-05-07 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US9327068B2 (en) | 1999-09-03 | 2016-05-03 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US9561314B2 (en) | 1999-09-03 | 2017-02-07 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US9597437B2 (en) | 1999-09-03 | 2017-03-21 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US9789238B2 (en) | 1999-09-03 | 2017-10-17 | Maquet Cardiovascular, Llc | Guidable intravascular blood pump and related methods |
| US10238783B2 (en) | 1999-09-03 | 2019-03-26 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US9545468B2 (en) | 1999-09-03 | 2017-01-17 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US10300185B2 (en) | 1999-09-03 | 2019-05-28 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US10328191B2 (en) | 1999-09-03 | 2019-06-25 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US10322218B2 (en) | 1999-09-03 | 2019-06-18 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US10300186B2 (en) | 1999-09-03 | 2019-05-28 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US10357598B2 (en) | 1999-09-03 | 2019-07-23 | Maquet Cardiovascular Llc | Guidable intravascular blood pump and related methods |
| US11964145B2 (en) | 2019-07-12 | 2024-04-23 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of manufacture and use |
| EP4034221A4 (en) * | 2019-09-25 | 2023-10-11 | Shifamed Holdings, LLC | Catheter blood pumps and collapsible pump housings |
Also Published As
| Publication number | Publication date |
|---|---|
| WO2000033446A8 (en) | 2000-08-24 |
| RU2001117822A (en) | 2003-06-27 |
| JP5093869B2 (en) | 2012-12-12 |
| KR20010086066A (en) | 2001-09-07 |
| DE59912438D1 (en) | 2005-09-22 |
| WO2000033446A1 (en) | 2000-06-08 |
| EP1142084B1 (en) | 2005-08-17 |
| BR9915843A (en) | 2001-09-04 |
| CZ20011928A3 (en) | 2002-03-13 |
| EP1142084A1 (en) | 2001-10-10 |
| DE29821564U1 (en) | 2000-07-13 |
| JP2002532047A (en) | 2002-09-24 |
| AU1856600A (en) | 2000-06-19 |
| ZA200104258B (en) | 2002-07-01 |
| PL348519A1 (en) | 2002-06-03 |
| NO20012498D0 (en) | 2001-05-21 |
| ATE302495T1 (en) | 2005-09-15 |
| DE19982578D2 (en) | 2002-01-10 |
| NO20012498L (en) | 2001-07-12 |
| AU755665B2 (en) | 2002-12-19 |
| IL143165A0 (en) | 2002-04-21 |
| CN1329770A (en) | 2002-01-02 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |