Intra ventricular ambulatory implantable PV loop system

Abstract

A blood pump including a housing having an inlet element, the inlet element including a distal portion coupled to the housing and a proximal portion sized to be received within at least a portion of a heart of a patient and a rotor configured to rotate within the housing and impel blood from the heart. At least one pressure sensor is coupled to the proximal portion of the inlet element.

Claims

1. A blood pump, comprising: a housing including an inlet element defining a major longitudinal axis, the inlet element having a distal portion coupled to the housing and a proximal portion sized to be received within at least a portion of a heart of a patient, and a rotor configured to rotate within the housing and impel blood from the heart; a flange member configured to be least partially disposed around the proximal portion of the inlet element and perpendicular to the major longitudinal axis, the flange member defining an aperture, the inlet element being configured to extend through the aperture; and a pressure sensor coupled to the flange member.

2. The blood pump of claim 1, wherein the inlet element defines a first diameter, and wherein the flange member defines a second diameter larger than the first diameter.

3. The blood pump of claim 2, further including an ultrasonic transducer coupled to the distal portion of the inlet element.

4. The blood pump of claim 3, wherein the ultrasonic transducer is coupled to the flange member.

5. The blood pump of claim 4, wherein the ultrasonic transducer and the pressure sensor are coupled to a microelectromechanical system (MEMS).

6. The blood pump of claim 5, wherein the MEMS is configured to be adhered to the flange member.

7. The blood pump of claim 6, wherein the housing further includes a stator having a plurality of coils, and wherein the stator is configured to generate a magnetic force to rotate the rotor, and wherein the stator includes a plurality of conductors configured to couple with a power source.

8. The blood pump of claim 7, wherein the plurality of conductors are electrically coupled to the MEMS.

9. The blood pump of claim 8, wherein the MEMS includes a wireless transmitter, and wherein the ultrasonic transducer and the pressure sensor are in communication with a wireless transmitter coupled to the inlet element.

10. The blood pump of claim 1, further including a flange member at least partially disposed around the proximal portion of the inlet element, and wherein an ultrasonic sensor is coupled to the flange member.

11. A blood pump system, comprising: a housing including: an inlet element defining a major longitudinal axis, the inlet element having a distal portion coupled to the housing and impel blood from the heart; and two stators, each stator having a plurality of coils, and each stator is configured to generate a magnetic force to rotate the rotor and includes a plurality of conductors configured to couple with a power source; a flange member disposed around a circumference of the proximal portion of the inlet element and perpendicular to the major longitudinal axis, the flange member including a MEMS coupled to the plurality of conductors and adhered to a proximal surface of the flange member, the flange member defining an aperture, the inlet element being configured to extend through the aperture; and a pressure sensor and an ultrasonic transducer coupled to the MEMS.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) A more complete understanding of embodiments described herein, and the attendant advantages and features thereof, will be more readily understood by reference to the following detailed description when considered in conjunction with the accompanying drawings wherein:

(2) FIG. 1 is an exploded view of exemplary blood pump constructed in accordance with the principles of the present application;

(3) FIG. 2 is front view of a portion of the assembled blood pump shown in FIG. 1 with a mounting element, flange member, and MEMS device;

(4) FIG. 3 is a front view of the assembly shown in FIG. 1 with the MEMS device mounting to the MEMS device;

(5) FIG. 4 is a Pressure-Volume (PV) loop of a cardiac cycle; and

(6) FIG. 5 shows the device of FIG. 2 implanted within the left ventricle of the heart.

DETAILED DESCRIPTION

(7) As used herein, relational terms, such as first and second, top and bottom, and the like, may be used solely to distinguish one entity or element from another entity or element without necessarily requiring or implying any physical or logical relationship or order between such entities or elements.

(8) Referring now to the drawings in which like reference designators refer to like elements there is shown in FIG. 1 an exemplary blood pump constructed in accordance with the principles of the present application and designated generally 10. The blood pump 10, according to one embodiment of the disclosure, includes a static structure or housing 12 which houses the components of the blood pump 10. In one configuration, the housing 12 includes a lower housing or first portion 14, an upper housing or second portion 16, and an inlet element 18 or inflow cannula 18 which includes an outer tube 18a and an inner tube 18b. The first portion 14 and the second portion 16 cooperatively define a volute shaped chamber 20 having a major longitudinal axis 22 extending through the first portion 14 and the inflow cannula 18. The chamber 20 defines a radius that increases progressively around the axis 22 to an outlet location on the periphery of the chamber 20. The first portion 14 and the second portion 16 define an outlet 24 in communication with chamber 20. The first portion 14 and the second portion 16 also define isolated chambers (not shown) separated from the volute chamber 20 by magnetically permeable walls. The inflow cannula 18 is generally cylindrical and extends generally from the first portion 14 along the axis 22. The inflow cannula 18 has an upstream end or proximal end 26 remote from second portion 16 and a downstream end or distal end 28 proximate the chamber 20.

(9) The parts of the housing 12 mentioned above are fixedly connected to one another so that the housing 12 as a whole defines a continuous enclosed flow path. The flow path extends from the upstream end 26 at the upstream end of the flow path to the outlet 24 at the downstream end of the flow path. The upstream and downstream directions along the flow path are indicated in by the arrows U and D, respectively. A post 30 is mounted to the first portion 14 along the axis 22. A generally disc shaped ferromagnetic rotor 32 with a central hole 34 is mounted within the chamber 20 for rotation about the axis 22. The rotor 32 includes a permanent magnet and flow channels for transferring blood from adjacent the center of the rotor 32 to the periphery of the rotor 32. In the assembled condition, the post 30 is received in the central hole of the rotor 32.

(10) A first stator 36 having a plurality of coils may be disposed within the first portion 14 downstream from the rotor 32. The first stator 36 may be axially aligned with the rotor along the axis 22 such that when a current is applied to the coils in the first stator 36, the electromagnetic forces generated by the first stator 36 rotate the rotor 32 and pump blood. A second stator 38 may be disposed within the second portion 16 upstream from the rotor 32. The second stator 38 may be configured to operate in conjunction with or independently of the first stator 36 to rotate the rotor 32.

(11) Electrical connectors 41 and 43 (FIG. 1) are provided on the first portion 14 and the second portion 16, respectively, for connecting the coils to a source of power, such as a controller (not shown). The controller is arranged to apply power to the coils of the pump to create a rotating magnetic field which spins the rotor 32 around the axis 22 in a predetermined first direction of rotation, such as the direction R indicated by the arrow which is counterclockwise as seen from the upstream end of the inflow cannula 18. In other configurations of the blood pump 10, the first direction may be clockwise. Rotation of the rotor 32 impels blood downstream along the flow path so that the blood, moves in a downstream direction D along the flow path, and exits through the outlet 24. During rotation, hydrodynamic and magnetic bearings (not shown) support the rotor 32 and maintain the rotor 32 out of contact with the surfaces of the elements of the first portion 14 and the second portion 16 during operation.

(12) A first non-ferromagnetic disk 40 may be disposed within the first portion 14 upstream from the rotor 32 between the first stator 36 and the rotor 32 and a second non-ferromagnetic disk 42 may be disposed downstream from the rotor 32 within the second portion 16 between the second stator 38 and the rotor 32. The rotor 32 is configured to rotate between the first disk 40 and the second disk 42 without contacting either disk. The general arrangement of the components described above may be similar to the blood pump 10 used in the MCSD sold under the designation HVAD by HeartWare, Inc., assignee of the present application. The arrangement of components such as the magnets, electromagnetic coils, and hydrodynamic bearings used in such a pump and variants of the same general design are described in U.S. Pat. Nos. 6,688,861; 7,575,423; 7,976,271; and 8,419,609, the disclosures of which are hereby incorporated by reference herein.

(13) Referring now to FIGS. 2-3, coupled to the proximal end 26 of the inlet element 18 may be a pressure sensor 44 configured to measure the blood pressure within any one chamber of the heart. For example, the proximal end 26 may include one or an array of pressure transducers configured to measure the changing pressure within a particular chamber of the heart as the heart contracts and relaxes. In one configuration, the pressure sensor 44 is coupled to the most proximal end of the inlet element 18 without blocking the opening in the inlet element 18 and is received within the left ventricle, although the inlet element 18 may be at least partially insertable within any chamber of the heart.

(14) The pressure sensor 44 may be coupled to a flange member 46 (FIGS. 2 and 3), as described in U.S. patent application Ser. No. 15/471,575, the entirety of which is incorporated by reference. The flange member 46 functions to prevent thrombus from entering the inlet element 18. In addition, the flange member 46 is configured to be coupled to the proximal end of the inlet element 18 and defines a diameter larger than that of the inlet element 18. The most proximal end of the flange member 46 is the surface of the flange member 46 that is facing the interior of the particular chamber in which it is inserted.

(15) An ultrasound transducer 48 may further be coupled to the proximal end 26 of the inlet element 18 or the flange member 46. The ultrasound transducer 48 may include one or an array of ultrasound transducers configured to measure the volume within a chamber of the heart as the heart contracts and relaxes. In one configuration, a microelectromechanical system (MEMS) device 50 may be adhered to or otherwise coupled to the surface of the flange member 46 and the pressure sensor 44 and the ultrasonic transducer 48 may be integrated as arrays into the surface of the MEMS device 50. For example, the MEMS device 50 may be a sticker that is adhered to the flange member 46 or alternatively may be attached or etched into the surface of the flange member 46. The MEMS device 50 may be coupled to an independent voltage source (not shown) or the voltage source configured to power the pump 10. The MEMS device 50 may further include a wireless transmitter and receiver (not shown) such that information measured by the ultrasonic transducer 48 and/or the pressure sensor 44 may be transmitted to a remote controller (not shown) outside of the patient.

(16) In an exemplary configuration, the most proximal end 26 of the inlet element 18 is inserted within the left ventricle of the patient. The flange member 46 may be positioned on the proximal end 26, as described U.S. patent application Ser. No. 15/471,575 referenced above. The MEMS device 50 may be adhered to the flange member 46 prior to affixation to the inlet element 18.

(17) The pressure sensor 44 and the ultrasonic transducer 48 be in the form of independently activated sensors in an array such that multiple measurements along multiple vectors may be measured. For example, the pressure sensors 44 may be included on the MEMS device 50 or directly on the flange member 46. As the measured pressure may be variable during the diastole and systole cycle and may be variable based on the position of the sensor 44 with respect to the chamber, the MEMS device 50 may be configured to individually activate the pressure sensors 44 of the array on the MEMS device to make multiple measurements either simultaneously or sequentially.

(18) Similar to the pressure sensor 44, the ultrasonic transducer 48 may be in the form of an array of ultrasonic transducers 48 facing different directions on the MEMS device 50 to create different vectors of measurement within the left ventricle, for example. Owing to the position of the ultrasonic transducer 48 on the MEMS device 50 when implanted within the left ventricle and owing to the shape of the left ventricle, to measure the volume of the left ventricle, the array of ultrasonic transducers 48 may be configured to sweep across the left ventricle. In particular, such sweeping may include ultrasonic transducers 48 either having a scanning range or being movable to angle themselves to measure the volume of the left ventricle. In one configuration, a first plurality of the ultrasonic transducers 48 may be timed to measure the volume of the left ventricle during systole and another plurality of the ultrasonic transducers 48 may be timed to measure the volume of the left ventricle during diastole. The combined pressure and volume measurements may be used to produce a PV loop, as shown in FIG. 4, to measure the efficiency of the particular chamber of the heart in real time.

(19) With reference to FIG. 5, as discussed above, in one exemplary configuration, the proximal end 26 of the inlet element 18 of the blood pump 10 is inserted within the left ventricle of the heart. The flange member 46 is coupled to the inlet element 18 with the MEMS device 50 being coupled to the surface of the flange member 46 which faces the interior of the left ventricle such that the measurements of the pressure and/or volume within the left ventricle may be obtained.

(20) Although the above embodiments are described with respect to a dual stator system, it is contemplated that the above sensors may be used in the manner describe herein in axial flow pumps having a single stator, as described in U.S. Pat. No. 8,007,254 and U.S. Patent Application Publication No. 2015/0051438 A1, sold under the designation MVAD by HeartWare, Inc., assignee of the present application. Moreover, the embodiments described above are independent from the type of pump. For example, the sensor array described above may be positioned on any supporting device configured to hold the pump either to the heart or within the heart. In one configuration, the sensor array may continue to work after the pump is removed and replaced by a plug, for example, as the grommet/sewing ring implanted in the apex of the heart would remain in place.

(21) It will be appreciated by persons skilled in the art that the present embodiments are not limited to what has been particularly shown and described herein above. In addition, unless mention was made above to the contrary, it should be noted that all of the accompanying drawings are not to scale. A variety of modifications and variations are possible in light of the above teachings without departing from the scope of the following claims.