DE202009018416U1 - Diameter changeable fluid pump - Google Patents

Abstract

Variable-diameter fluid pump device, in particular for medical use, with a variable-diameter pump housing (6), a variable-diameter rotor (7) with at least one conveying element (13, 14) for the fluid and with at least one, preferably in a casing (4) extending actuating means (8), in particular movable relative to this, at whose distal end the fluid pump (3) and at whose proximal end an actuating device, in particular a pulling device, is arranged, characterized in that the pump housing (6) and the rotor ( 7) can be displaced relative to one another by actuating the actuating means (8).

Description

The invention is in the field of mechanics, in particular precision engineering, and can be used with particular advantage in the medical field.

Regardless of the use in the medical sector, however, applications in other areas are conceivable where a fluid pump to operate in confined spaces or in hard to reach places.

This, however, is particularly true for minimally invasive medical technology, where medical instruments or devices, for example, must be brought to a place of use, for example through blood vessels, while treating patients as gently as possible. In particular, in this context, the use of blood pumps has become known in connection with catheters, which can be introduced, for example, in a heart chamber to support the Herzpumptätigkeit.

Since a certain size is necessary for the optimized performance of such a pump, but this is limited by the diameter of the large, heart-ending blood vessels of the body, it is already known to use variable in radius fluid pumps for this purpose, which after the introduction into the ventricle can be expanded.

This is made possible either by special mechanisms that allow actuation of a clamping mechanism of the pump through a catheter or by the use of so-called memory materials, which can take various forms when changing the ambient temperature and are brought by a temperature change in the desired final shape.

The expandability of such pumps, however, is limited by the need to accommodate both a drive shaft and a rotor and a pump housing on a small diameter.

The present invention is in this context the object of the invention to provide a fluid pump, which allows the simplest possible and large variability of the diameter with the least possible design effort.

The object is achieved according to the invention with the features of the protection claim 1.

In this case, a variable in diameter pump housing and optionally also a variable diameter rotor with at least one conveying element for the fluid is provided and extending in a sheath actuating means, in particular a traction means, at its distal end, as seen from the point of introduction of the catheter, the fluid pump is arranged.

The actuating means is displaceable in a longitudinal direction. In order to allow efficient compression to small diameter, the pump housing and the rotor by the actuating means in the longitudinal direction relative to each other are displaceable. This can be realized in that either the pump housing or the rotor or both are displaceable relative to the actuating means.

For example, for efficient compression, the rotor may be at least partially moved out of the pump housing. The compression movement of the pump housing is then not limited by the rotor housed in it completely.

The actuating means can be used for example as a traction means and be designed as a drive shaft, at the proximal end of which a rotary drive for the pump is provided. The drive shaft is rotatable in this case and also displaceable in the longitudinal direction.

In addition to this embodiment, it is also possible to drive the pump by means of an implantable in the body at the distal end of the shell arranged miniature motor or a hydraulic microturbine. Instead of the drive shaft, the fluid pump then has a suitable actuating means such as a train or a wire or the like, which moves the rotor or other parts of the pump, in particular also draws a bearing assembly in the pump housing.

There is also the possibility in the former case, in addition to a drive shaft to use a better suitable traction means. This makes it possible to optimize the drive shaft with respect to the requirements in terms of torque transmission and transit time and to optimize the traction device independently of the train function.

Such a traction means may for example be a rope made of plastic or a wire rope but also a wire or any other suitable traction means. For example, in the case of using a miniature implantable electric motor, one could also use the cables required to operate the motor as a traction means, and in the case of using a hydraulic micro-turbine, for example, the Operation of this turbine required hydraulic lines or hoses are used as traction means.

If the actuating means is stiff enough, for example designed as a wire, a pushing movement can also be carried out in a controlled manner. Thus, for example, the pump housing to be pushed in the longitudinal direction of the actuating means to the rotor.

The pump housing may for example consist of an elastic framework, for. Example of a memory alloy or a plastic, which is coated with a membrane, for example polyurethane. On the other hand, the pump housing but also from mutually movable segments such. As scales or lamellae, which are movable and compressible as a whole, with individual scales / segments or lamellae can be stiff or flexible in itself. Optionally, the rotor may be compressible in that either individual conveying elements of the rotor are foldable or pivotable to reduce the diameter of the shaft, or that the rotor consists of a membrane which can be tensioned by one or more tensioning elements.

In addition to the above-described embodiments of the pump housing and the rotor, other compressible and expandable designs are conceivable for the use of the invention.

It is advantageous for a particularly good compressibility of the arrangement that the pump housing and the rotor are so far in the longitudinal direction of the actuating means against each other, that they can be arranged one behind the other in the longitudinal direction or with a mutual overlap in the longitudinal direction, which is less than the overlap during the operation of the fluid pump. The various parts may be displaceable on a drive shaft which either forms the actuating means or whose extension is in the region of the pump when an implantable miniature motor is provided at the end of the shell.

A particularly advantageous embodiment of the invention also provides that at the distal end of the actuating means or its extension, seen from the rotary drive behind the rotor, a bearing assembly is disposed on the actuating means or its extension.

A particularly smooth and stable running of the rotor is achieved in that, in particular in addition to a bearing at the proximal end of the pump housing, a further bearing is provided at the distal end of the pump housing. The corresponding bearing arrangement may also be movable relative to the pump housing within the scope of the invention. It is advantageously displaceable on the actuating means or its extension in its longitudinal direction or at least displaceable with the actuating means or the extension relative to the rotor and the pump housing, provided that the actuating means itself is displaceable in the longitudinal direction.

In this way, after the expansion of the fluid pump device, the bearing assembly can be brought by a further displacement movement to its place of use at the distal end of the pump housing.

A further advantageous embodiment of the invention provides that the bearing assembly is displaceable relative to the rotor in the longitudinal direction of the actuating means.

Thus, both the bearing assembly and the rotor can be compressed and expanded independently of each other and moved after attaching the fluid pump device in the longitudinal direction against each other to achieve the operating arrangement.

If the bearing assembly is axially displaceable on the actuating means or the extension, then a stop body should be provided on this, for example at its / its end, which entrains the bearing assembly during retraction of the actuating means in the direction of the actuating device.

The bearing assembly in turn can then push against the rotor and also move it in the direction of the pump housing to the final position.

It can then also be provided that the bearing assembly with the rotor in the interior of the pump housing is movable and that radially arranged struts are provided which elastically tension between a hub of the bearing assembly and the pump housing.

This can be achieved particularly advantageous in that the struts are elastically pivotally attached to the hub of the bearing assembly.

For this purpose, the struts as well as bearing assembly may for example consist of an elastic plastic or rubber or of a resilient metal.

It can also be advantageously provided that the struts are radially extended by axial compression of the bearing assembly in the course of movement of the drive shaft by folding. This is z. B. then possible if the bearing assembly two mutually displaceable in the axial direction rings has, between which the struts are fixed, wherein the struts lie flat at a greater distance of the rings and are expanded like a bead when pushed together the rings.

The struts can advantageously form a Einströmkäfig at the distal end of the fluid pump in the clamped state, on the one hand prevents the rotor comes into contact with body tissue, on the other hand ensures that about located in the fluid to be conveyed larger coagulated masses can not penetrate into the pump housing ,

It is also advantageous, the actuating means relative to the shell in the longitudinal direction, in particular to the rotary drive at the proximal end of the shell, slidably to design, to effect the different axial displacement movements of the pump housing, rotor and bearing assembly against each other.

The sheath is usually formed in the field of medical application as a catheter. Such a catheter is flexible, but so stiff that it can be pushed through a blood vessel. The catheter is usually fluid-tightly connected to the pump housing, wherein the actuating means, for example a drive shaft, is inserted as tight as possible through a rotary feedthrough into the pump housing.

At the proximal end, which is usually outside the patient's body, the catheter is fluid-tightly connected to an actuating device and, for example, also to an electromotive drive, unless an implanted micromotor in the region of the fluid pump is preferred.

Advantageously, the catheter is filled with a biocompatible liquid such as saline, on the one hand necessarily to prevent the ingress of gas bubbles in the body and on the other hand optionally to lubricate and cool the shaft, which usually moves at 20,000-35,000 revolutions per minute.

The present invention, in the case that a drive shaft is provided within the shell, further advantageously be configured in that the drive-side end of the drive shaft is connected to a arranged in a sealed housing, from outside the housing magnetically driven by rotary drive body.

This embodiment allows the drive of the drive shaft without a rotary union to be sealed, through a magnetically inactive housing, in that a rotating field is applied, which sets the drive body located in the housing and thus the drive shaft in rotation.

A displacement of the drive shaft in the longitudinal direction is achieved according to the invention in that the drive body is displaceable in the longitudinal direction of the drive shaft and is driven on the shell side by a variable magnetic field.

Due to the shell-side transmission of the drive forces, this is independent of an axial displacement of the drive body when pulling or pushing the shaft.

However, it can also be provided that the drive shaft is fixedly connected to a driving body, which in turn is guided in the longitudinal direction of the drive shaft displaceable directly in the rotor.

In this case, the drive body is arranged stationary in the axial direction of the drive shaft, and only a driving body, which is non-rotatably connected to the rotor, in turn is axially displaceable with the drive shaft. Such a driving body can be formed, for example, as polygonal cross-section, for example, octagon body.

It is possible that the fluid pump device is brought to a place of use in a compressed state, that thereafter at least partially expands the pump housing and that thereafter the pump housing and the rotor in the longitudinal direction of an actuating means, in particular a drive shaft of the rotor are shifted against each other that the rotor completely absorbed in the pump housing.

In the above procedure, namely that first brought the individual elements pump housing, rotor and bearing assembly to the site, there at least partially expanded and only then brought by relative axial displacement in the constellation required for operation, is a stronger compression of the individual parts by their Graduation in the longitudinal direction of the actuating means possible.

For example, after inserting the assembly into a patient's body, the drive shaft may be withdrawn with the means of the invention and both the bearing assembly and the rotor moved toward the pump housing until the rotor is entirely within the pump housing and optionally through the bearing assembly is supported.

Whether the rotor is expanded before or after it is inserted into the pump housing, remains open, as well as the possibility of expanding the pump housing only partially before the introduction of the rotor, as far as necessary to introduce the rotor or whether the pump housing is already fully expanded prior to insertion of the rotor.

In the following the invention will be shown by means of an embodiment in a drawing and described below. Showing:

1 a schematic overview of a fluid pump device, wherein the pump is inserted into a heart chamber,

2 a three-dimensional image of a pump rotor,

3 a side view of the pump housing, the rotor and a bearing assembly,

4 a side view of the pump housing with rotor therein,

5 a detail of the pump housing in three-dimensional representation,

6 a bearing arrangement in a side view,

7 the bearing assembly 6 in a front view,

8th another bearing arrangement,

9 a bearing assembly like out 8th in compressed state,

10 another bearing arrangement in a side view,

11 the proximal end of a drive shaft with a coupling to a rotary drive and

12 another embodiment of the proximal shaft end with another coupling to a drive.

1 shows a ventricle that is connected to a blood vessel 2 connected, in which blood is to be pumped. To support the pumping action is a fluid pump 3 into the heart chamber 1 introduced, which draws blood there and this in the blood vessel 2 inflated.

Into the blood vessel 2 is a catheter 4 through a lock 5 introduced, through which the catheter can be pulled out again. The catheter 4 carries at its distal end the pump 3 in the form of a pump housing connected to the catheter 6 and a rotor 7 , The rotor 7 is on a drive shaft 8th rotatably mounted and has conveying elements which rotate the blood in the direction of the arrows 9 suck in or in the direction of the arrows 10 in the blood vessel 2 emit. For this purpose, the conveying elements in the illustration shown, which shows the expanded position of the fluid pump, a helically arranged conveying blade surface.

On the construction of the pump housing and the rotor will be discussed in more detail below.

The drive shaft 8th is from the drive 11 driven, in a housing 12 is housed. The drive elements are in the 1 shown only schematically and will be explained in more detail below.

2 shows in detail a pump rotor with two helical conveying blades 13 . 14 at the periphery of the drive shaft 8th offset from each other by 180 °. The individual conveyor blades consist of clamping elements such as struts 13a . 13b as well as a frame 13c which is covered with a membrane, for example made of polyurethane or polyethylene. For example, the frame and the struts may be made of memory material that takes its shape as a function of temperature. Such a pump rotor could then be introduced in compressed form with a first temperature, preferably cooled, in the patient's body and unfold there automatically after heating to the body temperature or subsequent further heating.

However, it is also conceivable to automatically set up the pump rotor by a rotary operation in the operating direction by the fluid to be pumped, so in the example case of blood, in the bucket and leads to an erection of the bucket through the fluid back pressure.

The design of the rotor may also differ from that described above by using partially hinged or hinged elements to form a bucket surface. The pivotable parts can then be folded in a compressed state usefully to the drive shaft.

The aspiration 13a . 13b as well as the frame 13c the pump rotor are usefully covered, but the frame runs 13c in the direction of the pump housing still a little way beyond the covering and there forms an inlet slope, which serves to facilitate the displacement of the rotor into the pump housing.

3 shows a pump housing 6 , a rotor 7 and a bearing assembly 15 spaced apart axially on the drive shaft 8th are distributed. This condition is maintained at least until the said parts are brought into place within a patient's body.

After that, the drive shaft 8th in the direction of the arrow 15 be retracted to form a functional unit of a fluid pump by a relative displacement of the rotor, pump housing and bearing assembly.

When retracting the drive shaft 8th first comes the driver 17 against the hub 18 the bearing arrangement 15 , Upon further retraction of the shaft, the bearing assembly is taken and against the rotor 7 pressed. This is also taken and further retract the drive shaft 8th into the interior of the pump housing 6 drawn. The rotor moves 7 so far into the pump housing until it is completely covered by this.

The pump housing 6 carries at its open end a fixing ring 19 in which are the struts of the bearing assembly 15 can get stuck.

4 shows the pump housing, the rotor and the bearing assembly in axially collapsed form. The fixation ring 19 is in the 5 described in more detail. It consists of two single rings 19a . 19b which are also positioned coaxially with each other and connected by ladder-type connecting bars. Between the connecting spars 19c . 19d find each end of the struts 20 . 21 the bearing arrangement 15 Place, so that after insertion, the bearing assembly there both radially centered and axially relative to the ring 19 is positioned. The bearing assembly is shown schematically in FIG 6 shown and has a hub 18 and striving 20 . 21 on. The aspiration 20 . 21 are at the hub 18 either pivotally mounted by means of a joint or by their flexibility.

If the bearing assembly is moved by retracting the drive shaft relative to the pump housing, so put the ends of the struts 20 . 21 elastic in the compartments between the bars 19c . 19d of the ring 19 , There, the bearing assembly automatically braced and centered in its hub mounted drive shaft relative to the pump housing 6 ,

The 6 shows a long bearing assembly, in which both before and axially behind the struts respectively a considerably long hub piece is arranged. The bearing assembly can also be made shorter by only one side of the struts a hub is provided as in the 8th shown.

7 shows a front view of the bearing assembly 6

The 9 shows the mobility of the struts in the compressed state.

Upon insertion of the fluid pump device through a blood vessel into a human body, the struts become 20 . 21 initially tight against the hub body, as long as the bearing assembly is still within the vessel, and then expanded elastically. This elasticity, after expansion and axial contraction of the pump elements, ensures that the bearing assembly in the ring 19 the pump housing remains fixed.

10 shows a further embodiment of the bearing assembly with a double shaft bearing, in the field of bearings 22 . 23 , The struts are formed by and radially extended that two hub parts 22 . 23 the bearing assembly are approximated by axial train on the drive shaft to each other. The struts are folded like a bead upon approach of the two hub parts and extend radially away from the drive shaft. With sufficient expansion, these struts can also be in the ring 19 tense.

11 shows the proximal end of the shaft 8th and its coupling to a drive, which is to allow axial displacement of the drive shaft by 10 to 14 mm in order to retract after the introduction of the individual elements of the fluid pump to the site by retracting the drive shaft, the bearing assembly and the rotor in the pump housing.

11 in this context provides a gas-tight coupling of the catheter 4 , the shell for the wave 8th forms, to a fluid-tight housing 24 in the housing 24 there is a drive body 25 , which at its periphery magnetic elements 26 . 27 which is in one of the outside of the housing 24 applied variable magnetic field can be driven on the shell side. This is achieved by the fluid-tight wall of the housing 24 in a simple way transmit a drive movement. For example, outside the case may be 24 a second drive body 28 rotate with permanent magnets or electromagnets, or there may be arranged windings which generate a rotating field.

On the ground 29 of the housing 24 is a bolt 30 attached, a thread 31 carries, which is stationary in the axial direction.

The rotor 25 carries a ring 32 with an internal thread on the thread 31 running.

Upon rotation of the drive body 25 in the operating direction, the drive body is due to the interaction of internal and external thread 25 in the direction of the arrow 33 moves, causing the drive shaft 8th is withdrawn. The inner ring 32 runs after completion of the return movement of the shaft of the thread 31 and, as a consequence, the drive body 25 rotate axially stationary. The fluid pump is thus axially pushed together and put into operation.

12 shows another embodiment at the proximal end of the drive shaft 8th , In the presentation of the 12 are only the magnets 26 . 27 of the drive body 25 represented within a fluid-tight housing 34 are located. The drive body 25 can in the case 34 be stored axially stationary and is rotationally driven from the outside. He transfers the rotational movement to a polygon 35 that in a complementarily shaped opening (lock) 36 in the drive body relative to this rotation, but is guided axially displaceable. For example, the lock 36 and the polygon 35 be designed as a regular octagonal, square or hexagonal.

The drive shaft 8th is in her end area 37 with a socket 38 rotatably connected. In the socket 38 is rotatable with an undercut an anchor 39 not included with the jack 38 rotates, but this fixed axially. The anchor 39 is with a ring 40 provided by a drawstring 41 is drawn. Becomes the anchor 39 by means of the drawstring 41 manually in the direction of the arrow 42 withdrawn, the anchor pulls the bushing 38 that can turn against the anchor, in the direction of the arrow 42 a short distance from the catheter 4 out so that the necessary shifts are made in the fluid pump. The drive body 25 can be driven meanwhile, without disturbing the train movement.

To a tightness of the housing 34 to ensure the anchor can 39 by means of a bellows or a tightly connected membrane 43 fluid-tight to the housing 34 be attached.

The invention thus provides an efficient type of drive with a displaceability of the drive shaft, wherein the displacement of the drive shaft is used in an optimized manner for completing the fluid pump after introduction to the operating location by a relative axial displacement of rotor, bearing assembly and pump housing.

Claims (16)

Diameter changeable fluid pump device, in particular for medical use, with a variable in diameter pump housing ( 6 ), a variable diameter rotor ( 7 ) with at least one conveying element ( 13 . 14 ) for the fluid and with at least one, preferably in a shell ( 4 ) extending, in particular with respect to this movable actuating means ( 8th ), at whose distal end the fluid pump ( 3 ) and at the proximal end of an actuating device, in particular a pulling device is arranged, characterized in that the pump housing ( 6 ) and the rotor ( 7 ) by actuating the actuating means ( 8th ) are displaceable relative to each other. Fluid pump device according to claim 1, characterized in that the actuating means has a longitudinal direction in which it is displaceable and that the pump housing ( 6 ) and the rotor ( 7 ) so far in the longitudinal direction of the actuating means ( 8th ) are mutually displaceable, that they can be arranged one behind the other in the longitudinal direction or with a mutual overlap in the longitudinal direction, which is less than the overlap during operation of the fluid pump. Fluid pump device according to claim 1 or 2, characterized in that at the distal end of the actuating means ( 8th ) seen from the actuator behind the rotor ( 7 ) a bearing arrangement ( 15 ) on the actuating means ( 8th ) or its extension is arranged. Fluid pump device according to claim 3, characterized in that the bearing arrangement ( 15 ) on the actuating means ( 8th ) or its extension in its / its longitudinal direction is displaceable. Fluid pump device according to claim 3 or 4, characterized in that the bearing arrangement ( 15 ) in the longitudinal direction of the actuating means ( 8th ) is displaceable relative to the rotor. Fluid pump device according to claim 3, 4 or 5, characterized in that the actuating means ( 8th ) or its extension a stop body ( 17 ), which upon retraction of the actuating means in the direction of the actuating device, the bearing assembly ( 15 ) takes along. Fluid pump device according to claim 3, 4, 5 or 6, characterized in that the bearing arrangement ( 15 ) with the rotor ( 7 ) into the interior of the pump housing ( 6 ) is movable and that star-shaped struts ( 20 . 21 ) provided between a hub ( 18 ) of the Bearing arrangement and the pump housing elastically brace. Fluid pump device according to claim 7, characterized in that the struts ( 20 . 21 ) elastically pivotable on the hub ( 18 ) of the bearing assembly ( 15 ) are attached. Fluid pump device according to claim 8, characterized in that between two and eight struts ( 20 . 21 ) are provided. Fluid pump device according to claim 7, 8 or 9, characterized in that the struts ( 20 . 21 ) form a Einströmkäfig at the distal end of the fluid pump in the clamped state. Fluid pump device according to claim 1 or one of the following, characterized in that the actuating means ( 8th ) against a shell ( 4 ) in the longitudinal direction, in particular on the actuating device, is displaceable. Fluid pump device according to claim 1 or one of the following, characterized in that the actuating means is a displaceable in its longitudinal direction drive shaft. Fluid pump device according to claim 1 or one of the following, characterized in that the actuating device is part of a rotary drive. Fluid pump device according to claim 12 or 13, characterized in that the drive-side end of the drive shaft ( 8th ) with one in a sealed housing ( 24 . 34 ) arranged, from outside the housing magnetically rotatably driven drive body ( 25 ) connected is. Fluid pump device according to claim 14, characterized in that the drive body ( 25 ) in the longitudinal direction of the drive shaft ( 8th ) is displaceable and is driven on the shell side by a variable magnetic field. Fluid pump device according to claim 14, characterized in that the drive shaft ( 8th ) fixed with a driving body ( 35 ), which in turn in the longitudinal direction of the drive shaft ( 8th ) slidably rotatably in the drive body ( 25 ) is guided.

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