Pump arrangement

Abstract

Pump arrangement (1, 10, 20, 30, 40, 50) with a compressible rotor (11, 41, 51) and a casing (12, 42, 52) accommodating the rotor and delimiting a flow channel (S) with a distal intake opening (13, 43, 53) and a proximal outlet opening (14, 29, 39, 44, 54) for generating a motive current (Q) T ) by means of the rotor, wherein the rotor is arranged in a first fluid-tight section (12a, 42a, 52a) having the distal intake opening and a second fluid-tight section (12b, 42b, 52b) comprising the proximal outlet opening, characterized in that a further inlet opening (15) is provided between the first and the second section, wherein the first section and the second section are arranged to each other such that the inlet opening opens into the flow channel (S) proximal to the rotor.

Description

[0001] The invention lies in the field of mechanical engineering and precision mechanics and is particularly advantageous in the medical field.

[0002] The subject matter is a pump arrangement according to the preamble of claim 1.

[0003] Pump arrangements, particularly for use in the body's own blood vessels, are increasingly known from the state of the art. These can be used, for example, for short-term cardiac support to relieve the strain on a patient's heart muscle after cardiogenic shock (myocardial infarction). Transfemorally implanted microaxial pumps are sometimes used in this context.

[0004] Such a pump arrangement is known, for example, from EP 2 047 872 A1. The pump arrangement disclosed therein comprises a pump, a housing for the pump with a distal intake opening and a proximal outlet opening, wherein the pump generates a driving flow from the distal intake opening to the proximal outlet opening during operation. A flow channel thus extends between the intake opening and the outlet opening. The pump is arranged in a first fluid-tight section of the housing, which has the distal intake opening and is designed as a polyurethane (PU) covering of a casing. Furthermore, a second fluid-tight section of the housing is present, which includes the proximal outlet opening and is designed as a discharge hose. The discharge hose is bonded to the PU covering.The pump arrangement is designed such that the pump, which is designed as a rotor, can be placed, for example, in a heart chamber, with the outflow tube extending from the heart chamber into the aorta.

[0005] All blood entering the aorta through the outlet openings of the discharge tube passes through the intake opening into the flow channel formed by the casing and through the rotor. In other words, the flow rate delivered by the pump is identical to the total flow exiting the outlet opening.

[0006] The subjects of publications DE 41 24 299 A1, DE 10 2004 054 714 A1, WO 2007 / 112033 A2 and US 2008 / 132748 A1 also proceed according to the aforementioned principle. US 4 964 864 A should also be mentioned as a further publication.

[0007] Since all blood comes into direct contact with the pump, a particularly high level of effort is required during pump manufacturing to reduce the blood-damaging effect of the moving pump parts. This blood-damaging effect manifests itself in direct mechanical shear on moving and stationary pump parts and in shear caused by shear stress fields occurring in the fluid during its passage through the flow channel (so). Therefore, pump geometries are required that cannot be implemented using minimally invasive techniques.

[0008] The present invention aims to reduce the risk of damage to the blood or the fluid transported by the pump. Particular attention must be paid to the selection of materials for the medical use of the pump arrangement(s) described below. These materials should ideally meet the requirements for biocompatibility. In addition to the above, interactions with foreign body surfaces constitute the third major aspect of blood damage and have been extensively studied for some time.

[0009] According to the invention, a further inlet opening is provided between the first and the second section, wherein the first and the second section are arranged relative to each other such that the inlet opening opens into the flow channel proximal to the compressible pump. The further inlet opening can also be designed as an inlet channel that has its inlet opening distal or proximal to the pump, or even at the level of the pump, but which only opens into the flow channel proximal to the pump.

[0010] With the aid of the feature according to the invention, it is possible for a motive flow passing through the pump to flow past the inlet opening in the flow channel towards the outlet opening, thus causing a pressure drop compared to the fluid pressure present in the inlet opening. This pressure drop leads to fluid being drawn in through the inlet opening and into the flow channel. As a result, the total flow exiting the outlet opening is greater than the motive flow passing directly through the pump and being delivered by it, since an additional suction flow is introduced through the inlet opening.

[0011] The suction flow arises from the suction effect created by the motive flow, similar to that which occurs in some turbine types or water jet pumps. During this suction effect, momentum is transferred from the motive flow to the suction flow through friction, viscosity, or turbulent mixing of the fluid. This generates viscous, turbulent shear stresses. The momentum direction of the motive fluid flow is transferred to particles from the fluid being pumped in the suction flow, which are transported to a downstream zone within the housing.

[0012] Essentially, the inventive feature implements the principle of a jet pump, wherein the driving current passing directly through and conveyed by the pump carries with it a suction current entering through the further inlet opening.

[0013] The inlet opening extends between the first and second sections, and its location can be proximal or distal to the pump. It is advantageous for the inlet to be distal to the outlet opening. Only the opening of the inlet into the flow channel should be proximal to the pump to ensure optimal use of the suction effect created by the driving flow.

[0014] A compressible pump is understood to be a preferably radially compressible pump or pump assembly. The pump, or the first and / or second section and / or the housing and / or the rotor, is designed such that the pump can be guided to the site of action within a catheter, the catheter having an inner diameter that is smaller than that of the first and second sections or the housing in its expanded state. Such pumps or pump assemblies are known, for example, from EP 2 047 872 A1, WO 2010 / 063494 A1, and WO 2010 / 127871 A1.

[0015] An inlet opening formed between the intake opening and the exhaust opening is particularly advantageous.

[0016] The first and second sections of the casing can be formed as a single piece or as separate components.

[0017] In a first embodiment, the cross-section of the proximal end of the first section is smaller than the cross-section of the distal end of the second section. This concentrates the flow onto an area of ​​the cross-section of the proximal end of the first section, allowing it to carry along additional medium upon entering the second section, which can flow in at least through inlets in the area of ​​the remaining cross-section of the distal end of the second section.

[0018] In another embodiment, the cross-section of the first section tapers towards its proximal end. This taper gives the first section a nozzle-like shape at its proximal end. This leads to an improvement in efficiency and thus to an increase in the suction flow rate. Furthermore, this feature helps to reduce the overall size of the pump assembly.

[0019] In a further embodiment, the distal end of the second section and the proximal end of the first section overlap; that is, the distal end of the second section is located more distally than the proximal end of the first section. It is advantageous if the inlet opening between the first and second sections is designed as an intake channel or channel-like structure, extending from the distal end of the second section to the proximal end of the first section. This allows the suction flow to enter the flow channel preferably almost coaxially with the direction of the motive flow, in the direction of the outlet opening. Due to the main axis of the intake channel, which is preferably oriented in the direction of the motive flow, the suction flow already receives momentum from the motive flow in the direction of the outlet opening. This leads to an improvement in efficiency.

[0020] In another embodiment, the distal end of the second section is located more proximal than, or at the same level as, the proximal end of the first section. Due to this spacing, the concentrated motive flow exiting the proximal end of the first section encounters fluids of different pressure and direction. As a result, the concentrated flow, resembling a higher-density fluid, continues into the beginning of the second section, defined by its distal end, entraining fluid located between the first and second sections. This increases the overall flow rate relative to the motive flow passing through the pump.However, care must be taken to keep the distance between the distal end of the second section and the proximal end of the first section small, in order to prevent the flow from diverting away from the flow outside the casing. The distance should be approximately 0 to 1 / 4 of the diameter of the proximal outlet of the first section.

[0021] In another embodiment, the second section comprises at least a portion made of a flexible material. This allows a second section, located between, for example, a heart chamber and a blood vessel (where the heart chamber and blood vessel are connected by a rhythmically opening and closing valve), to be pressed in by the valve, thus transporting the fluid in accordance with the rhythmic movement of the valve. Suitable materials include, for example, PU, ​​PE, PP, silicone, or parilene, provided they meet the mechanical and geometric requirements as well as the biocompatibility requirements.

[0022] In another embodiment, the pump assembly includes a housing for the pump. This is particularly suitable when the pump is a compressible pump that is transported to its working site along with the housing via a catheter. The housing also provides the pump assembly with additional stability. The housing can be made of nitinol, for example.

[0023] If a housing is present, the first section can be designed as a casing or coating of the housing, whereby only a portion of the housing, preferably an axial portion, needs to be fluid-tightly encased or coated. Suitable materials for coatings or casings include those already described in the second section, which uses a flexible material.

[0024] In another embodiment, the housing has a constriction and / or a bulge proximal to the pump. A constriction is understood to be a narrowing of the housing's cross-section compared to the area of ​​the housing that accommodates the pump. A bulge has a housing cross-section that is larger than that of a constriction or the area that accommodates the pump. Such a design makes it particularly easy and advantageous to achieve narrowings in the first section or larger cross-sections in the second section. The second section can also be connected to the housing.

[0025] In another embodiment, the first and second sections are joined together by a material bond or are preferably formed in one piece.

[0026] In another embodiment, the second section is designed as a drain hose.

[0027] In a further embodiment, the first section, the second section, or any housing comprises support elements, such as a support ring, plastic threads, wires, connecting struts, or a preferably compressible sleeve, for spacing the first and second sections apart. This prevents a suction flow through the inlet opening from causing a surface of the second section to be drawn against the surface of the first section and thus interrupting the suction flow, or ensures that the second inlet opening remains permanently open during pump operation. The support elements are connected to the first or second section in such a way that they are compressible along with the pump. This can be achieved, for example, using flexible support elements, support elements made of hyperelastic materials, or support elements made of memory materials such as Nitinol.

[0028] Furthermore, the second section can have a support ring in the area of ​​the inlet opening, which ensures a distance between the first and second sections in the area of ​​the inlet opening, so that a suction flow through the inlet opening does not cause a surface of the second section to be drawn against the surface of the first section and thus interrupt the suction flow. This is particularly advantageous if the second section is made of a flexible material, such as an exhaust hose.

[0029] In a further embodiment, the second section comprises a sleeve encompassing, or partially encompassing, the further inlet device. This sleeve can be connected, for example, to a flexible area of ​​the second section as an additional special component. It is advantageous if the sleeve is dimensionally stable in its operating state, which is defined, for example, by the deployment of the pump assembly at its operating location within the body, and thus forms a suitable resistance to a fluid, so that the suction flow is channeled through the sleeve and enters the flow channel.

[0030] Instead of a sleeve, another section of hose or a pipe can also be used.

[0031] In another embodiment, the pump is a compressible pump, which makes it easier to insert the pump into the bloodstream or a vessel.

[0032] Furthermore, it is advantageous if the pump is an axial pump, which is mounted on a rotatable shaft that drives the pump.

[0033] The invention will now be explained in more detail using several exemplary embodiments. The figures shown are: Fig. 1 the use of a pump arrangement in a heart; Fig. 2 a schematic representation of an embodiment of the pump arrangement; Fig. 3 a schematic representation of an inlet opening of an embodiment of the pump arrangement; Fig. 4 an embodiment of a pump arrangement; Fig. 5a another embodiment of a pump arrangement; Fig. 5b a schematic representation of the pump arrangement of the Fig. 5a; Fig. 6 another embodiment of a pump arrangement; Fig. 7 another embodiment of a pump arrangement; Fig. 8a-8c Cross-sections through different pump arrangements.

[0034] In the Fig. Figure 1 shows one possible use for the pump assembly 1. The pump assembly 1 comprises an elongated catheter extending through the blood vessel 2, within which a shaft runs that drives the pump, designed as a rotor, located within the pump assembly 1. The proximal end of the pump assembly (excluding the catheter) is located in the blood vessel 2, whereas the distal end of the pump assembly 1, which contains the pump, is located in the heart chamber 3. The blood vessel 2 is bounded by the vessel wall 4. Furthermore, the valve 5, which opens and closes rhythmically, borders the heart chamber 3 and allows blood flow from the heart chamber 3 into the blood vessel 2.

[0035] In addition to the illustrated use of a pump arrangement according to the invention, other uses are possible. For example, the pump can be used in another bodily vessel to increase the delivery rate.

[0036] Based on the Fig. Section 2 will explain the operating principle of a pump arrangement according to the invention. The pump arrangement 10 comprises a pump 11, which is designed as a rotor. The pump 11 is set in rotation by means of a shaft shown, but not labeled, and is thus able to generate a driving current Q. T to transport. The pump arrangement 10 has a casing 12, which comprises a first section 12a and a second section 12b. In the first section 12a there is a suction opening 13, through which a fluid can enter the lumen of the first section 12a, be drawn in by the pump 11 and transported as the driving flow Q. Tis transported towards the outlet opening 14. The casing 12 defines the flow channel S between the intake opening 13 and the outlet opening 14, which in the exemplary embodiment of the Fig. 2 the lumen of the first section 12a completely and a lumen of the second section 12b partially encompasses.

[0037] The first and second sections overlap between the proximal end of the first section 12a and the distal end of the second section 12b. This overlap defines an inlet opening 15 through which fluid from an area outside the lumen of the first section 12a can enter the flow channel S. This is due to the motive flow Q delivered by the pump. T In the area of ​​the proximal end of the first section 16, a pressure drop occurs in area 17. This is in the Fig. 3 shown.

[0038] Due to the pressure drop in area 17, further fluid is drawn through the inlet opening 15 towards the outlet opening 14, which is called suction flow Q. S The inlet opening 15 enters the flow channel proximal to the proximal end of the first section 16. Thus, the inlet opening 15 opens into the flow channel S.

[0039] The first section 12a and the second section 12b each comprise a lumen. The lumen of the first section 12a has a cross-sectional area A1, and the lumen of the second section 12b has a cross-sectional area A2. In the present embodiment, the cross-sections A1 and A2 remain the same over the entire length of the respective section; however, this is not a mandatory feature. The suction flow is already given an impulse direction towards the outlet opening 14 by the channel, designed as an inlet opening 15, which runs parallel to the driving flow between the distal end of the second section 12b and the proximal end of the first section 12a. The additional suction flow Q S Q is the volume of water flowing out at outlet 14 per unit of time. A greater than the driving current Q passing through the pump T .

[0040] Another embodiment of a pump arrangement is described in the Fig. The pump assembly 20 is located in a blood vessel which is bounded by the vessel walls 4. The distal end of the pump assembly 20 is located distal to the valve 5, the proximal end is located proximal to the valve 5.

[0041] The pump assembly 20 comprises a compressible rotor 21, which is mounted on one side of the shaft 22. The bearing is located at the proximal end of the rotor. The rotor 21 is surrounded by a housing 23, which may be made of nitinol. The housing consists of individual nitinol threads, wires, or struts that intersect to form a diamond pattern. The fluid can pass through the diamonds and thus reach the rotor 21.

[0042] The housing 23 is partially covered by a fluid-tight sheath 24. The sheath 24 extends over a length L. 24 , so that a tractive current Q driven by the rotor Tis bundled and exits the housing 23 at the proximal end of the sheathing 24 and flows towards the outflow openings 29, which are arranged in an outflow hose 25.

[0043] In the design of the pump assembly 20, the casing 24 forms the first section of the enclosure, and the discharge hose 25 forms the second section of the enclosure. The distal end of the discharge hose is attached to the housing 23 and is located more distally than the proximal end of the casing 24.

[0044] The enclosure 24 tapers from the area of ​​the rotor 21 in a proximal direction. Thus, the lumen formed by the enclosure 24 has a cross-sectional area A in the area of ​​the rotor 21. 1D on, which is larger than the cross-sectional area A 1P of the proximal end of the casing 24. This creates a nozzle effect which increases the driving flow Q TThe fluid is accelerated according to the principle of a Venturi tube, so that it flows at a higher velocity at the proximal end of the casing 24 towards the outlet openings 29. The intake channel 26, accessible through the inlets 27, is located between the casing 24 and the outlet hose 25. Fig. Figure 4 shows that several inlets 27 are present, the inlets being designed as circular cutouts in the outflow hose in the region of its distal end. Due to the area of ​​the exiting driving current Q T Reduced pressure results in a suction flow Q S through entrance 27 and is drawn into the intake channel 26 and flows into the flow channel S, which transports the entire flow to the outlet openings 29.

[0045] Proximal to the inlets 27 and radially surrounding the discharge hose 25, there is a support ring 28, which is dimensionally stable when the pump is operating. This prevents the surface of the discharge hose 25 from being drawn against the casing 24 by the suction flow. The intake channel 26 thus remains open, and further fluid is drawn through the intake channel 26 by the driving flow Q. T , sucked into the flow channel S.

[0046] Another embodiment of the pump arrangement according to the invention is described in the Fig. Figure 5a shows the pump assembly 30, which comprises a rotor 31 mounted on both sides, i.e., distally and proximally, on an axis 32. The rotor 31 is arranged in a housing 33, which is partially encased by a PU coating 34. The PU coating 34 extends over a length L 34up to a region located proximal to the proximal end of the rotor 31. The housing 33 has a constriction 33a and widens proximal to the constriction 33a into a bulge 33b. In the region of the bulge 33b, the outflow hose 35 is bonded to the housing 33. The bulge 33b and the constriction 33a are spaced apart along the axis 32 by a distance d, which is approximately 0 to 1 / 4 of the diameter of the constriction 33a. The distance d is chosen such that, due to the motive current Q exiting the proximal end of the PU coating 34 and driven by the rotor 31, T a suction flow Q S The fluid is drawn in through the inlet opening 36 located between the PU coating 34 and the outlet hose 35. The motive current Q exiting the sheathing TThe fluid is expelled at a pressure P1. Outside the casing 34, a pressure P2 exists, which is lower than the pressure P1. This pressure difference creates a suction flow Q. S drawn into the inlet opening 36 and transported through the outflow hose to the outlet opening 39, where it flows under a pressure P3, which is greater than the pressure P2, as a total flow Q A is emitted. The total flow Q A is greater than the driving current Q T .

[0047] Even though the flow channel S, which extends between the intake opening distal to the rotor 31 and the outlet opening 39, is fluid-permeable between the proximal end of the PU coating 34 and the distal end of the exhaust hose 35, the inlet opening 36 still opens into the flow channel, which is defined by the flow path of the motive current. If the motive current is sufficiently high, it enters the exhaust hose almost directly.

[0048] Due to the inlet opening located distal to the intake opening 31, it is possible for a partial flow of the total flow Q exiting at the outlet opening 39 to be drawn into the intake opening. A The rotor 31 does not pass through, and therefore there is no risk of blood damage from the rotor 31.

[0049] The embodiment of the pump arrangement 30 of the Fig. 5a is in the Fig. Figure 5b is shown schematically again. Here it can be seen that the distal end of the PU coating 34 has a cross-sectional area A. 1D exhibits which is larger compared to the cross-sectional area A 1P is located at the proximal end of the PU coating 34. This narrows the lumen enclosed by the PU coating 34, resulting in an improvement in efficiency. The cross-sectional area A 2D The lumen of the outflow hose 35 is again larger than the cross-sectional area A 1PThus, at least through the area of ​​the cross-sectional area A 2D , which after subtracting the cross-sectional area A 1P This leaves an inlet opening 36 defined. This in turn leads into the flow channel S.

[0050] Another embodiment of a pump arrangement is described in the Fig. Figure 6 is shown. A detailed description of the axis and the pump drive is omitted here. The pump assembly 40 comprises a rotor 41 and a first section 42a and a second section 42b of a casing. At the distal end of the first section 42a is the intake opening 43, which supplies fluid to the pump 41. The fluid supplied to the pump 41 is accelerated and used as the driving current Q. TThe first section 42a is ejected at its proximal end. The second section 42b consists of a flexible area 420b, which is connected to a compressible, rigid, dimensionally stable sleeve 421b when the rotor is in its operating state. The compressible sleeve 421b is connected to the first section 42a by means of plastic threads or wires 422b. The cross-section, which tapers from the distal end of the sleeve 421b to the proximal end of the sleeve 421b, in conjunction with the motive current Q, causes T a suction of a suction flow Q S through the inlet opening 45, which is formed between the sleeve 421b and the first section 42a, whereby the suction flow Q S with the driving current Q T combined and in the flow channel S as total flow Q A out of the outlet opening 44. From the Fig. 6 again makes it obvious that the inlet opening 45 leads into the flow channel S.

[0051] Another embodiment of a pump arrangement is described in the Fig. Figure 7 shows the pump arrangement 50. It comprises a pump 51, which is designed as an axial pump with a rotor. Furthermore, it includes a casing 52, which can be divided into a first section 52a and a second section 52b. The first and second sections are bonded together or manufactured as a single piece. At the distal end of the casing 52 is an inlet opening 53, which supplies fluid to the rotor, so that a motive flow Q is present when the rotor is in operation. T is promoted. The driving current Q T is conveyed towards the outlet opening 54. Between the first section 52a and the second section 52b is an inlet opening 55, through which a flow of motive current Q is conveyed. T induced suction flow Q Scan enter the flow channel S defined by the covering 52. The special feature of this embodiment is that the covering 52 is made in one piece, in contrast to the embodiments described so far, in which the first section is a separate component from the second section.

[0052] Based on the Fig. Figures 8a-c are intended to illustrate some different geometries of the inlet openings.

[0053] In the Fig. 8a is a cross-section of the exemplary embodiment of the Fig. Figure 6 shows the intake opening 43 with a cross-sectional area A. 1P Proximal to this, i.e. further into the image plane, is the sleeve 421b with the cross-section A measured at its widest circumference. 2D The plastic threads 422b connect the sleeve 421b to the first section 42a.

[0054] In the Fig. 8b is the embodiment of the Fig. Figure 5a shows the intake opening 33, which is defined by the PU coating 34. The PU coating 34 also defines a lumen, which has a cross-sectional area A in the rotor area. 1D exhibits. The axis 32 is also visible in the center of the intake opening 33. Proximal to the rotor (cf. Fig. 5a) The casing 33, which is formed by nitinol threads, wires or struts, tapers to a cross-sectional area A 1P , which is defined by the constriction 33a. Proximally, the housing 33 widens into a bulge 33b, in the area of ​​which the outlet hose 35 is connected to the housing. Based on the Fig. In the illustration shown in 8b, it is clearly evident that the area 36 located between the outflow hose 35 and the PU coating 34 serves as an inlet opening for a suction flow.

[0055] In the Fig. 8c is the embodiment of the Fig. Figure 4 shows the cross-section at the level of the support ring 28. The lumen defined by the casing 24 of the first section, with cross-sectional area A, is visible. 1D Between the casing 24 and the discharge hose 25 is the intake channel 26, through which additional fluid is drawn in, driven by the motive flow running proximally through the lumen of the casing 24. The discharge hose 25 has a cross-sectional area of ​​A in this region. 2D The support ring 28 is clearly visible, as are the connecting struts 28a, which connect the support ring to the casing 24. The support ring is made up of several segments 28b, which can be folded to allow insertion of the pump assembly using a catheter. Reference symbol list 1, 10, 20, 30, 40, 50 Pump arrangement 2 Blood vessel 3 heart chamber 4 Vessel wall 5 Heart valve 6. Vascular valve 11, 41, 51 Pump 12, 42, 52 Envelope 12a, 42a, 52a 1st section of the covering 12b, 42b, 52b 2nd section of the encasing 13, 43, 53 Intake opening 14, 44, 54 Outlet 15 Entrance opening 16 proximal end of section 1 17 Area pressure drop 21, 31 Rotor 22, 32 axis 23, 33 Cases 24, 34 sheathing L24, L34 Length of the casing 25, 35, 420b Drain hose 26, 36 Intake manifold 27 entrances 28 Support ring / spacer 33a Constriction 33b Bulging 421b sleeve 422b Spacer Q T Flow Q S Suction current Q A Total current A1, A2, A1D , A 1P , A 2D Cross section

Claims

[1] Pump arrangement (1, 10, 20, 30, 40, 50) with a compressible rotor (11, 41, 51) and a casing (12, 42, 52) accommodating the rotor and delimiting a flow channel (S) with a distal inlet opening (13, 43, 53) and a proximal outlet opening (14, 29, 39, 44, 54) for generating a motive current (Q T ) by means of the rotor, wherein the rotor is arranged in a first fluid-tight section (12a, 42a, 52a) having the distal intake opening and a second fluid-tight section (12b, 42b, 52b) comprising the proximal outlet opening, characterized by , that between the first and the second section there is a further inlet opening (15), wherein the first section and the second section are arranged to each other such that the inlet opening opens proximal to the rotor into the flow channel (S). [2] Pump arrangement according to claim 1, characterized by , that the cross-section (A 1P) of the proximal end of the first section smaller than the cross-section (A 2P ) of the distal end of the second section. [3] Pump arrangement according to one of the preceding claims, characterized by , that the cross-section (A 1D , A 1P ) of the first section tapers towards its proximal end. [4] Pump arrangement according to one of the preceding claims, characterized by , that the distal end of the second section is located more distal than the proximal end of the first section and the inlet opening is designed as an intake channel (26, 36) running between the first and second sections. [5] Pump arrangement according to one of the preceding claims, characterized by , that the distal end of the second section is located more proximal than or at the same level as the proximal end of the first section. [6] Pump arrangement according to one of the preceding claims, characterized by, that the second section (12b, 42b, 52b) includes an area made of a flexible material. [7] Pump arrangement according to one of the preceding claims, characterized by , that a housing (23, 33) to accommodate the pump is present. [8] Pump arrangement according to claim 7, characterized by , that the first section is a sheath (24, 34) of the housing (23, 33). [9] Pump arrangement according to one of claims 7 or 8, characterized by , that the second section is connected to the housing (23, 33). [10] Pump arrangement according to one of the preceding claims, characterized by that the first and second sections are materially bonded together. [11] Pump arrangement according to one of the preceding claims, characterized by , that the second section includes a discharge hose (25, 35, 420b). [12] Pump arrangement according to one of the preceding claims, characterized bythat the first or second section has support elements to space the first and second sections. [13] Pump arrangement according to claim 12, characterized by , that the second section in the area of ​​the inlet opening has a support ring (28). [14] Pump arrangement according to one of the preceding claims, characterized by , that the second section comprises a sleeve (421b) encompassing the further inlet opening (15). [15] Pump arrangement according to one of the preceding claims, characterized by , that a rotatable shaft (16, 22, 32) is present, on which the rotor (11) is arranged.

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