阅读说明：本技术 一种旋转容积血泵 (Rotary volumetric blood pump ) 是由 高斌 薛清心 符珉瑞 于 2020-12-21 设计创作，主要内容包括：一种旋转容积血泵,属于生物医学工程领域,主要用于体外膜肺氧合的血液驱动。该血泵包括血泵本体与其驱动装置两部分。其中血泵本体主要由泵壳、端盖、两个滑块、管轴等部分组成。该血泵通过两个相互独立的滑块在泵腔内分别旋转而产生的正负压来驱动血液。本发明克服了主流血泵的一些缺点,具有便携、血液损伤较小、溶血指标较低、可长期使用等优势。(A rotary volumetric blood pump belongs to the field of biomedical engineering and is mainly used for blood drive of extracorporeal membrane oxygenation. The blood pump comprises a blood pump body and a driving device thereof. The blood pump body mainly comprises a pump shell, an end cover, two sliding blocks, a tubular shaft and the like. The blood pump drives blood by positive and negative pressure generated by respectively rotating two mutually independent sliding blocks in a pump cavity. The invention overcomes some defects of a mainstream blood pump, and has the advantages of portability, small blood damage, low hemolysis index, long-term use and the like.)

1. A rotary positive displacement blood pump is characterized by comprising a blood pump body and a driving device thereof; wherein the blood pump body mainly comprises a pump shell (1), an end cover, a slide block A (2), a slide block B (3), a tubular shaft A (4), a tubular shaft B (5), a blood inlet (6) and a blood outlet (7); the pump shell is a cylindrical cavity structure, two ends of the pump shell are provided with end cover seals, the pump shell and the end covers are combined to form a blood pump cavity, the tubular shaft A and the tubular shaft B are coaxially and parallelly arranged along the axial direction of the pump shell shaft, the sliding block A and the sliding block B are respectively arranged in the annular part between the pump shell and the tubular shaft A and the annular part between the pump shell and the tubular shaft B, the sliding block A and the sliding block B divide the annular part between the pump shell and the tubular shaft A and between the pump shell and the tubular shaft B into two parts, the sliding block A is fixed with the tube shell A, the sliding block B is fixed with the tube shell B, the tube shell A and the tube shell B;

the side surface of the pump shell is provided with two inlets and outlets which are respectively used as a blood inlet and a blood outlet, and the blood inlet and the blood outlet are arranged side by side along the circumferential direction of the pump shell; permanent magnets for magnetic driving are embedded in the sliding blocks A and B.

2. A rotary volumetric blood pump according to claim 1, wherein the two slides are of the same shape and size.

3. A rotary positive-displacement blood pump according to claim 1, in which the axes of the tube axes a, B are mechanical bearings, hydrodynamic suspension bearings or magnetic suspension bearings.

4. The rotary positive-displacement blood pump according to claim 1, wherein the slide blocks a and B are independent of each other and move in the pump chamber in a circular motion around the tubular shaft, and positive pressure and negative pressure are generated at the front and rear ends of the slide blocks a and the front and rear ends of the slide blocks B to drive the blood flow in the pump chamber. In the movement process, a sliding block is always stopped between the blood inlet and the blood outlet to play a role in blocking the reverse flow of blood.

5. A rotary positive-displacement blood pump according to claim 1, in which the length of the slides a (2) and B (3) in the axial direction of the pump housing (1) is equal to the axial length of the pump housing (1). The sum of the lengths of the pipe shaft A (4) and the pipe shaft B (5) along the axial direction of the pump shell (1) is equal to the axial length of the pump shell (1).

6. A mode of operation of a rotary volumetric blood pump according to any of claims 1 to 5, characterized in that before the first run of the blood pump, an angle is formed between the slide A and the slide B, the blood inlet (6) is in front of the blood outlet (7) according to the circumferential direction of movement of the slide A and the slide B, the slide A is located in front of the blood inlet (6), the slide B is located between the blood inlet (6) and the blood outlet (7), and neither slide blocks the blood inlet (6) at the blood outlet (7); starting the blood pump, wherein the two sliders in the pump cavity independently run and circularly move around the tubular shaft in the same direction, the slider A firstly runs and the slider B is static on the assumption that the running direction is clockwise, negative pressure is generated behind the slider A at the moment, and then blood is sucked into the pump cavity from the blood inlet (6); when the front end of the slide block A is about to move to the edge behind the blood outlet (7), the slide block B and the slide block A start to move simultaneously, and the positive pressure in front of the slide block B pushes the blood to continuously flow forwards clockwise until the blood is pumped out through the blood outlet (7); when the slide block A moves to a position between the blood inlet (6) and the blood outlet (7), namely the initial position of the slide block B, the slide block A stops operating, the slide block B still continues operating at the moment, the front end of the slide block B pushes blood, and the rear end of the slide block B sucks the blood, and the process is a working cycle of the rotary volumetric blood pump.

7. The operating mode of claim 6, wherein the sliders A and B are driven to rotate by means of separate magnetic drives.

8. The operating mode according to claim 6, wherein the sliders A and B are driven to rotate at a speed of 60-120 rpm.

Technical Field

The invention belongs to the field of biomedical engineering, and relates to a novel rotary positive displacement blood pump which is mainly used for blood drive of extracorporeal membrane oxygenation.

Background

Extracorporeal membrane pulmonary oxygenation (ECMO) is an adjunctive treatment that uses an extracorporeal circulation system as its primary device and employs extracorporeal circulation techniques for operation and management. ECMO is a support means aiming at the core of severe heart-lung function failure at present, and the essence of the ECMO is an improved artificial heart-lung machine, and a blood pump is one of the core parts of the ECMO, and plays the role of an artificial heart and provides power for blood flowing in a pipeline.

The blood pump clinically applied to the ECMO at present mainly comprises a rolling pump and a centrifugal pump. The rolling pump presses the outer wall of the pump pipeline through the roller pressing shaft to drive blood to flow, the volume is large, blood damage is large, and excessive positive pressure or negative pressure can be generated to cause the rupture of the pump pipeline. The centrifugal pump generates centrifugal force to drive blood through high-speed circular motion, and higher shearing stress can be generated in the running process of the centrifugal pump, so that blood damage is caused. And because the internal flow passage of the centrifugal pump is communicated, the output flow of the centrifugal pump is directly influenced by afterload, thereby bringing great difficulty to the clinical control of the flow.

Disclosure of Invention

In order to solve the problems in the prior art, the invention provides a rotary volumetric blood pump which integrates the characteristics of the two blood pumps and has the advantages of small volume, low rotating speed, small blood damage, decoupling of flow and afterload and the like.

In order to achieve the above purpose, the invention adopts a technical scheme that:

a rotary volumetric blood pump comprises a blood pump body and a driving device thereof; wherein the blood pump body mainly comprises a pump shell (1), an end cover, a slide block A (2), a slide block B (3), a tubular shaft A (4), a tubular shaft B (5), a blood inlet (6) and a blood outlet (7); the pump shell is a cylindrical cavity structure, two ends of the pump shell are provided with end cover seals, the pump shell and the end covers are combined to form a blood pump cavity, the tubular shaft A and the tubular shaft B are coaxially and parallelly arranged along the axial direction of the pump shell shaft, the sliding block A and the sliding block B are respectively arranged in the annular part between the pump shell and the tubular shaft A and the annular part between the pump shell and the tubular shaft B, the sliding block A and the sliding block B divide the annular part between the pump shell and the tubular shaft A and between the pump shell and the tubular shaft B into two parts, the sliding block A is fixed with the tube shell A, the sliding block B is fixed with the tube shell B, the tube shell A and the tube shell B;

the side surface of the pump shell is provided with two inlets and outlets which are respectively used as a blood inlet and a blood outlet, and the blood inlet and the blood outlet are arranged side by side along the circumferential direction of the pump shell; permanent magnets for magnetic driving are embedded in the sliding blocks A and B.

The two sliding blocks are the same in shape and size.

The axes of the tubular shaft A and the tubular shaft B are mechanical bearings, hydraulic suspension bearings or magnetic suspension bearings. The slide block A and the slide block B are independent from each other, respectively run in the pump cavity and do circular motion around the tubular shaft, and the front end and the rear end of the slide block A and the front end and the rear end of the slide block B can generate positive pressure and negative pressure so as to drive blood in the pump cavity to flow. In the movement process, a sliding block is always stopped between the blood inlet and the blood outlet to play a role in blocking the reverse flow of blood.

The lengths of the sliding block A (2) and the sliding block B (3) along the axial direction of the pump shell (1) are respectively equal to the axial length of the pump shell (1). The sum of the lengths of the pipe shaft A (4) and the pipe shaft B (5) along the axial direction of the pump shell (1) is equal to the axial length of the pump shell (1).

The working mode of the volumetric blood pump is as follows: before the blood pump runs for the first time, an included angle is formed between the sliding block A and the sliding block B, the blood inlet (6) is located in front of the blood outlet (7) according to the circumferential motion direction (such as the clockwise direction) of the sliding block A and the sliding block B, the sliding block A is located in front of the blood inlet (6), the sliding block B is located between the blood inlet (6) and the blood outlet (7), and the two sliding blocks do not block the blood inlet (6) from the blood outlet (7); starting the blood pump, wherein the two sliders in the pump cavity independently run and circularly move around the tubular shaft in the same direction, the slider A firstly runs and the slider B is static on the assumption that the running direction is clockwise, negative pressure is generated behind the slider A at the moment, and then blood is sucked into the pump cavity from the blood inlet (6); when the front end of the slide block A is about to move to the edge behind the blood outlet (7), the slide block B and the slide block A start to move simultaneously, and the positive pressure in front of the slide block B pushes the blood to continuously flow forwards clockwise until the blood is pumped out through the blood outlet (7); when the slide block A moves to a position between the blood inlet (6) and the blood outlet (7), namely the initial position of the slide block B, the slide block A stops operating, the slide block B still continues operating at the moment, the front end of the slide block B pushes blood, and the rear end of the slide block B sucks the blood, and the process is a working cycle of the rotary volumetric blood pump.

The mode of driving the slide block A and the slide block B to rotate is a mode of independently driving by adopting respective magnetic driving devices.

The invention has the beneficial effects that: compared with the traditional rolling pump, the invention drives blood by the independent operation of the two sliding blocks, has no rolling effect on the blood, has less damage to the blood, does not need a pump pipeline made of silica gel or PVC material, avoids the problem of pump pipe bursting and cracking caused by overhigh pressure of a pipeline behind the pump, and can be used for long-time blood driving. In addition, the invention is equivalent to a centrifugal pump in volume and is more portable than the traditional rolling pump. Compared with the traditional centrifugal pump, the positive displacement blood pump is a positive displacement blood pump, the blood is pushed by the slider rotating for one circle and the blood is the same as the normal heart discharge volume of a human body, so that the rotating speed of the slider only needs 60-120 rpm. Compared with the rotating speed of more than 3000rpm when the centrifugal pump moves, the shearing force generated by the invention is obviously reduced and is closer to physiological indexes, and the problem of obviously increasing hemolysis indexes caused by the high rotating speed of the centrifugal pump is avoided. In addition, the invention is a volumetric blood pump, so the output flow is mainly influenced by the rotating speed of the sliding block and is less influenced by the change of afterload. Thereby facilitating subsequent clinical control of output blood flow.

Drawings

Fig. 1 is a schematic structural view of a rotary volumetric blood pump provided by the present invention (end caps are omitted in the figure).

In the figure: 1-a pump casing; 2-a slide block A; 3-a slide block B; 4-pipe axis A; 5-pipe axis A; 6-blood inlet; 7-blood outlet.

Detailed Description

In order to make the objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below. All other embodiments, which can be derived by a person skilled in the art from the embodiments of the invention without inventive step, such as for example embodiments relating to the basic concept only with a changed use and without changing the claims, belong to the protective scope of the invention.

Example 1

As shown in fig. 1, the novel rotary positive displacement blood pump provided by the invention comprises a blood pump body and a driving device thereof. The blood pump body mainly comprises a pump shell, a tubular shaft, a slide block A, a slide block B, an end cover and the like. The pump shell 1 is 39mm in outer diameter and 35mm in axial length, and is provided with two radial side surface inlets and outlets which are parallel to each other and arranged circumferentially, namely a blood inlet 6 and a blood outlet 7, and the circumferential lengths of the blood inlets and outlets are both 50 mm; the pump shell 1 and the end cover are combined to form a blood pump cavity, the slide block A and the slide block B are arranged in the pump cavity and divide the pump cavity into two parts, blood in the two cavities flows independently, the tubular shaft A and the tubular shaft B are respectively connected with the two slide blocks and penetrate through the center of the pump cavity, permanent magnets for magnetic driving are embedded in the two slide blocks, and the rest parts in the pump body are made of non-magnetic materials.

When the blood sucking pump works, the two sliding blocks in the pump cavity independently run and circularly move around the tubular shaft in the same direction, and positive and negative pressure differences are generated in the pump cavity, so that blood is sucked by the chamber on one side, and blood is pumped by the chamber on the other side. Through in vitro experiments and hemolysis experiments, the rotating speed is 60rpm, the corresponding flow is 5L/min, the maximum inlet-outlet pressure difference is 500mmHg, and the generated maximum shear stress is less than 100Pa and far lower than that of a centrifugal pump when the centrifugal pump runs.

Features of combinations of parts not described in detail in the specification are readily ascertainable and would not be objectionable to those skilled in the art or to practice the present invention. The embodiments described in the above schemes are only a part of embodiments of the present invention, and not all embodiments, but the scope of the present invention is not limited thereto, and the scope of the present invention shall be subject to the claims.