阅读说明：本技术 手柄上带有控制器和显示屏的血管内泵 (Intravascular pump with controller and display screen on handle ) 是由 约瑟夫·P·希金斯 马修·W·蒂尔斯特拉 本杰明·D·哈泽尔曼 马修·D·康布罗纳 特里斯坦 于 2019-07-30 设计创作，主要内容包括：本发明提供了一种血管内血泵,其包括与旋转马达和叶轮组件操作性连接和通信的手柄,该旋转马达和叶轮组件被构造为用于放置和定位在患者的脉管系统内。手柄包括用于显示与血泵程序相关的实时生理参数的显示器以及用于修改操作参数的控制器。在一些实施例中,手柄的显示部分可以连接到非显示部分和/或与非显示部分断开,以允许在随后的血泵程序中重复使用显示部分。(An intravascular blood pump is provided that includes a handle operatively connected to and in communication with a rotary motor and impeller assembly configured for placement and positioning within a patient's vasculature. The handle includes a display for displaying real-time physiological parameters associated with the blood pump procedure and a controller for modifying the operating parameters. In some embodiments, the display portion of the handle may be connected to and/or disconnected from the non-display portion to allow reuse of the display portion in subsequent blood pump procedures.)

1. A blood pump assembly adapted for use within a vasculature of a patient, the blood pump assembly comprising:

a motor in operative rotational engagement with an impeller assembly, the impeller assembly including an impeller housing, an impeller within the impeller housing, the impeller including an impeller hub and blades in operative engagement with the impeller hub; and

a handle operatively connected to and in communication with the motor, wherein the handle comprises a controller for controlling at least the motor, and a display integrated into the handle, the display being adapted to display real-time physiological parameters and operating parameters, wherein the real-time physiological parameters comprise at least one of the group consisting of blood pressure, heart rate, electrocardiographic information, and oxygen saturation, and

wherein the real-time operating parameter comprises at least one of the group consisting of a rotational speed, an ultimate blood flow caused by the blood pump within the vasculature of the patient, and an ultimate blood pressure caused by the blood pump within the vasculature of the patient.

2. The blood pump assembly of claim 1, further comprising a drive shaft in operative rotational engagement with the impeller assembly and the motor, wherein the motor is located within the handle and outside of the vasculature of the patient.

3. The blood pump assembly of claim 1, wherein the motor is located within the vasculature of the patient.

4. The blood pump assembly of claim 1, wherein the handle comprises a display portion and a non-display portion, wherein the display portion is adapted to be operatively and removably connected with the non-display portion.

5. The blood pump assembly of claim 4, wherein the display portion is adapted to be reused after disconnecting the reusable display portion from the used non-display portion after completion of a procedure within the vasculature of a patient.

6. The blood pump assembly of claim 1, wherein the impeller assembly does not include a flow guide or a flow diffuser.

7. A blood pump assembly adapted for use within a vasculature of a patient, the blood pump assembly comprising:

a motor in operative rotational engagement with an impeller assembly, the impeller assembly including an impeller housing, an impeller within the impeller housing, the impeller including an impeller hub and blades in operative engagement with the impeller hub; and

a handle operatively connected to and in communication with the motor, wherein the handle includes a controller for controlling at least the motor, and a display integrated into the handle, the display adapted to display real-time physiological and operational parameters,

wherein the handle comprises a display portion and a non-display portion, wherein the display portion is adapted to be operatively and removably connected with the non-display portion.

8. The blood pump assembly of claim 7, wherein the display portion is adapted for reuse after a procedure within the vasculature of a patient is completed and after the reusable display portion is disconnected from the used non-display portion.

9. The blood pump assembly of claim 7, wherein the real-time physiological parameter comprises at least one of the group consisting of blood pressure, heart rate, electrocardiographic information, and blood oxygen saturation.

10. The blood pump assembly of claim 7, wherein the real-time operating parameters include at least one of the group consisting of a rotational speed, an ultimate blood flow caused by the blood pump within the vasculature of the patient, and an ultimate blood pressure caused by the blood pump within the vasculature of the patient.

11. The blood pump assembly of claim 7, further comprising a drive shaft in operative rotational engagement with the impeller assembly and the motor, wherein the motor is an external motor located proximal to the impeller assembly and external to the vasculature of the patient.

12. The blood pump assembly of claim 11, wherein the motor is located within the handle.

13. The blood pump assembly of claim 7, wherein the motor is located within the vasculature of the patient.

14. A blood pump assembly adapted for use within a vasculature of a patient, the blood pump assembly comprising:

a motor in operative rotational engagement with an impeller assembly, the impeller assembly comprising an impeller housing, an impeller within the impeller housing, the impeller comprising an impeller hub and blades in operative engagement with the impeller hub, wherein the impeller assembly does not comprise a flow guide or a flow diffuser; and

a handle operatively connected to and in communication with the motor, wherein the handle includes a controller for controlling at least the motor, and a display integrated into the handle, the display adapted to display real-time physiological and operational parameters.

15. The blood pump assembly of claim 14, wherein the real-time physiological parameter comprises at least one of the group consisting of blood pressure, heart rate, electrocardiographic information, and blood oxygen saturation.

16. The blood pump assembly of claim 14, wherein the real-time operating parameters include at least one of the group consisting of a rotational speed, an ultimate blood flow caused by the blood pump within the vasculature of the patient, and an ultimate blood pressure caused by the blood pump within the vasculature of the patient.

17. The blood pump assembly of claim 14, further comprising a drive shaft in operative rotational engagement with the impeller assembly and the motor, wherein the motor is an external motor located proximal to the impeller assembly and external to the vasculature of the patient.

18. The blood pump assembly of claim 14, wherein the motor is located within the vasculature of the patient.

19. The blood pump assembly of claim 13, wherein the handle comprises a display portion and a non-display portion, wherein the display portion is adapted to be operatively and removably connected with the non-display portion.

20. The blood pump assembly of claim 19, wherein the display portion is adapted to be reused after disconnecting the reusable display portion from the used non-display portion after completion of a procedure within the vasculature of a patient.

Technical Field

The invention relates to an intravascular pump with a controller and a display screen on a handle.

Background

Referring to fig. 1, the human heart includes four chambers and four heart valves that facilitate the forward (antegrade) flow of blood through the heart. The chambers include the left atrium, left ventricle, right atrium, and right ventricle. The four heart valves include the mitral valve, the tricuspid valve, the aortic valve, and the pulmonary valve.

The mitral valve is located between the left atrium and the left ventricle and helps control the flow of blood from the left atrium to the left ventricle by acting as a one-way valve, preventing backflow into the left atrium. Similarly, the tricuspid valve is located between the right atrium and right ventricle, while the aortic and pulmonary valves are semilunar valves located in the arteries that flow blood away from the heart. The valves are all one-way valves, with leaflets that open to allow forward (antegrade) blood flow. The normally functioning valve leaflets close under the pressure exerted by the retrograde blood flow to prevent backflow of blood (retrograde flow).

Thus, as shown, the general blood flow includes deoxygenated blood returning from the body, which is received by the right atrium via the superior and inferior vena cava, and then pumped into the right ventricle, which is controlled by the tricuspid valve. The right ventricle is used to pump deoxygenated blood via the pulmonary arteries to the lungs, where it is re-oxygenated and returned to the left atrium via the pulmonary veins.

Heart disease is a health problem with high mortality. The use of temporary mechanical blood pump devices is increasingly frequently used to provide short term acute assistance during surgery or as temporary bridge assistance to help patients to crisis. These temporary blood pumps have been developed and evolved over the years to supplement the pumping action of the heart on a short-term basis and to supplement blood flow as left or right ventricular assist devices ("LVADs"), the most commonly used devices at present.

Known temporary LVAD devices are typically delivered percutaneously (e.g., via the femoral artery) such that the LVAD inlet is located or positioned in the left ventricle and the outlet is in the ascending aorta of the patient, with the body of the device disposed across the aortic valve. One skilled in the art will appreciate that an incision may be made below the groin of the patient to enable access to the femoral artery of the patient. The physician may then translate the guidewire (followed by the catheter or delivery sheath) through the femoral artery and the descending aorta until reaching the ascending aorta. The LVAD with the attached rotating drive shaft may then be translated through a delivery catheter or sheath lumen, exposing the proximal end of the drive shaft outside the patient's body, and coupled with a prime mover (such as an electric motor) or equivalent for rotating and controlling the rotational speed of the drive shaft and associated LVAD impeller.

Temporary axial flow blood pumps generally include two types: (1) axial flow blood pumps powered by a motor integrated in a device connected to the impeller of the pump (see U.S. patent nos.5,147,388 and 5,275,580); and (2) axial flow blood pumps powered by an external motor that provides rotational torque to a drive shaft, which in turn is connected to the impeller of the pump (see U.S. patent nos.4,625,712 to Wampler and 5,112,349 to Summers, each of which is incorporated herein by reference in its entirety).

Known temporary ventricular assist devices ("VAD"), including LVAD and RVAD (right ventricular assist) devices, whether with an integrated motor or an external motor, generally include the following elements mounted within a housing, listed in order from an inflow end to an outflow end: an inflow hole; a flow guide known in the art as a means of directing flow from an inflow orifice or inlet into the impeller; rotating the impeller; and flow diffusers and/or outflow structures known in the art for straightening or redirecting the rotational flow generated by a rotating impeller into an axial flow; and an outflow bore as shown in the exemplary prior art pump and/or impeller assembly cross-section and cutaway view of fig. 2.

In fig. 2, the known device 2 is oriented with the inflow end (distal end) on the left side of the figure and the outflow end (proximal) on the right side, such that the incoming blood flow in the ventricle enters the device housing through one or more inflow holes (not shown), the flow being defined by the surrounding housing 14, ultimately entering the impeller/pump assembly 4. There, the incoming blood encounters the flow guide 6 before being propelled forward by the rotating impeller 8. The blood flow may then be altered by the flow diffuser 9 and exit into the aorta via one or more outflow holes 10 of the housing.

Known VAD or LVAD devices also include a delivery configuration and a functional or working configuration, wherein the delivery configuration has a lower profile or smaller diameter than the functional or working configuration, thereby facilitating atraumatic delivery through the delivery sheath, among other things. In other words, the blades of the housing and/or impeller of the VAD or LVAD may be expanded to achieve a functional or working configuration and collapsed to achieve a delivery configuration in various ways. However, known devices collapse and expand the impeller blades and/or the casing, wherein a collapsible and expandable casing surrounds at least a portion of the impeller so as to be movable between an expanded or working configuration and/or require an integrated motor proximate the impeller. See, e.g., U.S. patent nos. 7,027,875; no.7,927,068; and No.8,992,163.

Known LVAD devices typically include an angled housing to accommodate the aortic arch, the angle or bend typically being in the range of 135 degrees.

The LVAD device with an integrated motor in the housing must be small enough to allow atraumatic intravascular translation and positioning in the heart. While various methods are known to collapse portions of the device (including the housing and/or impeller or components thereof, such as the blades) while in a catheter or delivery sheath, the size of the collapsing device may be limited by an integrated motor.

Further, known LVAD devices include delivery configurations in which the housing and/or impeller (e.g., blades on the impeller) may be reduced in diameter and the collapsed elements are expandable when delivered distally from a delivery catheter or sheath. These devices are limited in several respects. First, the collapsing and expanding includes at least a portion of the casing occupied by the impeller. Second, the inflow region of the housing, i.e., the region away from the rotating impeller and the stationary guide or flow straightener, includes regions that have the opportunity to optimize blood flow through the cannula or housing. Known LVAD or VAD devices cannot take advantage of this opportunity. Third, known LVAD or VAD devices include a stationary guide or flow straightener that blood encounters when entering the pump, which may lead to thrombosis and/or hemolysis, among other things. Fourth, for the reasons discussed herein, reducing the crossover profile of a VAD or LVAD device is critical, and design requirements become more difficult due to the need to run wires through or along the housing of the device, where the wires can be used to power and/or communicate with motors or sensors or other operational power components, for example. In this connection, the wires need to be profile reduced to keep the crossing profile as low as possible, and the insulation and/or spacing between adjacent conductors, where such insulation and/or spacing is necessary or desirable.

Various embodiments of the present invention address these problems, among others.

The figures and the detailed description that follow more particularly exemplify these and other embodiments of the invention.

The description of the invention and as set forth herein is illustrative and is not intended to limit the scope of the invention. The features of the various embodiments may be combined with other embodiments within the contemplation of the invention. Variations and modifications of the embodiments disclosed herein are possible, and practical alternatives to and equivalents of the various elements of the embodiments will be understood by those of ordinary skill in the art after studying this patent document. These and other variations and modifications of the embodiments disclosed herein may be made without departing from the scope and spirit of the invention.

Drawings

FIG. 1 is a cross-sectional view of a human heart;

FIG. 2 is a cross-sectional view of a prior art device;

FIG. 3 is a side cross-sectional view of one embodiment of the present invention;

FIG. 4 is a side cross-sectional view of one embodiment of the present invention;

FIG. 5 is a side cross-section of one embodiment of the present invention;

FIG. 6 is a top cross-sectional view of a handle of one embodiment of the present invention;

FIG. 7 is a perspective view of one embodiment of the present invention;

FIG. 8A is a top view of the handle with the display portion connected to the non-display portion; and

fig. 8B is a top view of the handle of fig. 8A with the display portion disconnected from the non-display portion.

Detailed Description

In general, various embodiments of the present invention are directed to mechanical assist devices for pumping blood within a patient. Described herein are improved temporary LVAD or VAD blood pumps for percutaneous and intravascular delivery.

Referring now to fig. 3, an exemplary LVAD blood pump 100 is shown with inflow orifice 12 on the left side of the illustration and outflow orifice 10 on the right side of the device. The motor is shown on the proximal end of the device that is outside the patient's body and is connected to a rotary drive shaft, which in turn is connected to an impeller or rotor 8 or pump assembly. However, as is well known in the art, the motor may be located within the housing of the device itself, with the motor typically being mounted on the proximal side of the rotor 8 or impeller or pump assembly. Any of these configurations may be used with the various embodiments of the invention as described herein.

The entire length of the outer housing 14 is shown to include a relatively constant diameter from the inlet or inflow orifice 12 to the outlet or outflow orifice 10. A guidewire 16 is positioned along the exterior of the device until the entry aperture 12 is reached, where it enters the lumen of the cannula C and extends distally therefrom, as shown. Thus, the guidewire 16 does not pass through the impeller or rotor 8 or pump assembly. The configuration shown in fig. 3 may include a delivery configuration with an expandable region 102, the expandable region 102 being compressed within a guide or delivery sheath or catheter 200.

Referring generally to the figures, the device 100 may include an expandable region 102 that may be positioned away from an impeller or rotor or pump assembly such that a diameter of a housing surrounding the impeller or rotor or pump assembly does not change diameter during delivery or during rotation. In other words, the proximal non-expandable region 122 may be provided and include at least an impeller or rotor or pump assembly, and the housing surrounding the assembly does not expand or contract significantly but may be flexible. In addition, a distal non-expandable region 124 may be provided that includes at least an inlet region that includes at least the inlet aperture 12. Thus, the expandable region 102 includes a proximal end and a distal end. The proximal end of the expandable region 102 abuts or is adjacent to the distal end of the proximal non-expandable region 122, while the distal end of the expandable region 102 abuts or is adjacent to the proximal end of the distal non-expandable region 124. However, the housing H surrounding the one or more non-expandable regions 122, 124 may be flexible or pliable, but they are not configured to bias expansion.

Alternatively, the housing H of the device 100 of fig. 3 may be non-expandable.

Fig. 4 illustrates an expandable embodiment of the device 100, and shows, in phantom, the change in diameter to/from a collapsed deformed expandable region extending distally along the hollow cannula from a point distal to the end of the impeller, rotor and/or pump assembly to a point just proximal to the inlet bore to an exemplary expanded undeformed expandable region. The expandable region 102 may be expanded to a maximum undeformed diameter in the range of 12-20Fr, more preferably between 16-20 Fr. In contrast, the unexpanded region maintains a substantially fixed diameter in the range of 9 to 12 Fr.

With continued general reference to fig. 3 and 4 and the remaining figures, the device 100 may include an expandable region 102 that may be partially or fully biased to an expanded configuration, and thus include a material or structure that facilitates expansion and may be biased to expand. An exemplary configuration of the expandable region 102 may include a support structure 130 surrounded by an outer material, such as a jacket or coating or sleeve composed of an expanded plastic or polymeric material that accommodates an underlying support structure known in the art. Support structure 130 may be formed from a shape memory material, such as nitinol or the like. Other materials may include gold, tantalum, stainless steel, metal alloys, aeroalloys, and/or polymers, including polymers that expand and contract when exposed to relative heat and cold. In other instances, at least a portion of the expandable region 102 (e.g., the central expandable section 104 discussed below) may include a polymer or other material sleeve configured to allow and/or accommodate expansion and collapse, and the support structure 130 may be omitted. Fig. 4 provides a rotary drive shaft connected to the impeller assembly and which, in turn, is connected to a prime mover, such as an electric motor, located outside the patient's body. However, it should be understood that the various embodiments of the invention discussed herein may also be used in conjunction with a blood pump that includes a motor integrated into the blood pump (i.e., without an external motor). Further, as discussed above, the device 100 may include an expandable shell H or region 102, or may be non-expandable.

In many of the embodiments described herein, the expandable region 102 may comprise a single expandable region without or without distinguishing between proximal, central, and/or distal transition sections.

In general, the expandable region 102 of the present invention may include a support structure 130 surrounded by a polymer coating or jacket that is adapted for expansion and collapse of the expandable region 102.

In addition, the support structure 130 may include an expandable stent-like structure formed from a series of cells formed from interacting and/or interconnected wires and/or struts and that enables the structure (e.g., stent) to collapse and bias expand, as is known in the art. See, for example, U.S. Pat. Nos.5,776,183 to Kanesaka; U.S. Pat. No.5,019,090 to Pinchuk; tower's No.5,161,547; savin, U.S. Pat. No.4,950,227; fontaine No.5,314,472; U.S. Pat. Nos.4,886,062 and 4,969,458 of Wiktor; and Hillstead's No.4,856,516; the disclosure of each of these patents is incorporated herein by reference in its entirety.

The expandable region 102 described herein is merely exemplary and is not limiting in any respect. Thus, any expandable housing H of the blood pump device 100 is readily adaptable to various embodiments of the present invention involving insulation and/or spacing and/or contour reduction or integration of wires or conductors E within or along the blood pump housing. The expandable region 102 may also comprise a single region capable of expanding and collapsing.

Turning now to fig. 5, an exemplary pump assembly or impeller assembly 200 is shown. Initially, in contrast to the known impeller assembly shown in fig. 2 (which includes the flow guide 6 and the flow diffuser 9), the exemplary pump or impeller assembly of fig. 5 completely eliminates the flow guide 6 and the flow diffuser 9 of the impeller assembly that occurs in known pumps. The applicant has found that the guide 6 and/or diffuser 9 do not require effective control or manipulation for inflow of blood flow, and that the additional fixed surface area and interconnection between at least the guide 6 and the distal end of the rotating impeller 8 provides an increased risk of thrombosis. Thus, by activating the pump or impeller assembly to rotate at a predetermined speed, blood is directed to flow through the cannula without the assistance or requirement of a flow guide. Thus, blood flows directly to the rotating impeller 8, which includes the vanes 11, and is pushed out of the cannula or lumen of the device at the outlet orifice 10 by the rotating impeller vanes 11 without the aid or requirement of a flow diffuser or straightener.

Turning now to fig. 6-8B, an embodiment of a blood pump assembly including a handle with control buttons and a display on the handle is provided. In some cases, a rotary motor may be provided in operative engagement with the impeller assembly and may be disposed within the device and within the vasculature of the patient. In other embodiments, the external rotation motor may be disposed in operative engagement with a drive shaft, which in turn is in operative engagement with the impeller assembly.

In general, the blood pump assembly of the present invention may comprise:

a motor in operative rotational engagement with an impeller assembly, the impeller assembly including an impeller housing, an impeller within the impeller housing, the impeller including an impeller hub and blades in operative engagement with the impeller hub; and

a handle operatively connected to and in communication with the motor, wherein the handle comprises a controller for controlling at least the motor, and a display integrated into the handle, the display being adapted to display real-time physiological parameters and operating parameters, wherein the real-time physiological parameters comprise at least one of the group consisting of blood pressure, heart rate, electrocardiographic information, and oxygen saturation, and

wherein the real-time operating parameters include at least one of the group consisting of a rotational speed, a final blood flow rate caused by the blood pump within the vasculature of the patient, and a final blood pressure caused by the blood pump within the vasculature of the patient.

In some cases, the impeller assembly and/or impeller may include flow guides and/or flow straighteners, while in other embodiments, flow guides or flow straighteners are not required. Further, as described herein, the motor may be integrated within the device and inserted with the device into the vasculature of a patient. In other cases, the motor may be disposed within the handle with the rotary drive shaft disposed within the sheath and operatively engaged with the rotary motor and impeller assembly.

Fig. 6 shows a physiological parameter on a display with a controller for controlling an operating parameter that can be adjusted depending on whether the displayed physiological parameter is high or low or tends to be high or low compared to a desired physiological parameter target.

Fig. 7 illustrates one embodiment of a handle operatively connected to the impeller assembly and any physiological sensors along the sheath and/or in or near the impeller assembly. It will be readily appreciated that the electrical wires may be translated through the sheath to operatively connect the handle with the motor and/or impeller assembly and/or physiological parameter sensor or operational sensor (e.g., flow pressure or flow rate generated or caused by a rotating impeller).

Fig. 8A and 8B illustrate an embodiment in which the handle includes a reusable display portion and a non-reusable non-display portion. The display portion may be removably connected with and to the non-display portion to be operable to function and monitor, as described above. When the blood pump procedure is complete, the display portion may be disconnected from another non-display portion and reused with another non-display portion in another blood pump procedure.