U.S. patent application number 14/287838 was filed with the patent office on 2014-11-06 for systems and methods for making and using percutaneously- delivered pumping systems for providing hemodynamic support.
This patent application is currently assigned to BOSTON SCIENTIFIC SCIMED, INC.. The applicant listed for this patent is BOSTON SCIENTIFIC SCIMED, INC.. Invention is credited to KEVIN D. EDMUNDS, ROGER N. HASTINGS, MICHAEL J. PIKUS, LEONARD B. RICHARDSON, SCOTT R. SMITH.
Application Number | 20140330069 14/287838 |
Document ID | / |
Family ID | 44152178 |
Filed Date | 2014-11-06 |
United States Patent
Application |
20140330069 |
Kind Code |
A1 |
HASTINGS; ROGER N. ; et
al. |
November 6, 2014 |
SYSTEMS AND METHODS FOR MAKING AND USING PERCUTANEOUSLY- DELIVERED
PUMPING SYSTEMS FOR PROVIDING HEMODYNAMIC SUPPORT
Abstract
A percutaneous pumping system for providing hemodynamic support
to a patient includes a pumping sleeve that defines a lumen
extending along the length of the pumping sleeve. The pumping
sleeve is configured and arranged for insertion into patient
vasculature. At least one rotatable magnet is disposed in the
pumping sleeve. The at least one first magnet is configured and
arranged to be driven to rotate by a magnetic field generated
external to the pumping sleeve. At least one impeller is coupled to
the at least one magnet. Rotation of the at least one magnet causes
a corresponding rotation of the at least one impeller. An anchoring
arrangement is coupled to the pumping sleeve. The anchoring
arrangement is configured and arranged to anchor the pumping sleeve
at a target pumping location when the pumping sleeve is inserted
into patient vasculature.
Inventors: |
HASTINGS; ROGER N.; (MAPLE
GROVE, MN) ; PIKUS; MICHAEL J.; (GOLDEN VALLEY,
MN) ; SMITH; SCOTT R.; (CHASKA, MN) ;
RICHARDSON; LEONARD B.; (BROOKLYN PARK, MN) ;
EDMUNDS; KEVIN D.; (HAM LAKE, MN) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
BOSTON SCIENTIFIC SCIMED, INC. |
MAPLE GROVE |
MN |
US |
|
|
Assignee: |
BOSTON SCIENTIFIC SCIMED,
INC.
MAPLE GROVE
MN
|
Family ID: |
44152178 |
Appl. No.: |
14/287838 |
Filed: |
May 27, 2014 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
12967856 |
Dec 14, 2010 |
8734508 |
|
|
14287838 |
|
|
|
|
61288719 |
Dec 21, 2009 |
|
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Current U.S.
Class: |
600/16 |
Current CPC
Class: |
A61M 1/1031 20140204;
A61M 1/1008 20140204; A61M 1/125 20140204; A61M 1/101 20130101;
A61M 1/1029 20140204; A61M 1/1086 20130101; A61M 1/127 20130101;
A61M 1/1036 20140204; A61M 1/1024 20140204; A61M 1/122
20140204 |
Class at
Publication: |
600/16 |
International
Class: |
A61M 1/10 20060101
A61M001/10; A61M 1/12 20060101 A61M001/12 |
Claims
1. (canceled)
2. A percutaneous pumping system for providing hemodynamic support
to a patient, the percutaneous pumping system comprising: a stent
defining a flow path and being sized for insertion into a blood
vessel; a rotor rotatably mounted within the stent, the rotor
defined in part by at least one blade angled with respect to the
flow path; at least one rotatable magnet configured and arranged to
be driven to rotate by a magnetic field generated adjacent the
stent, wherein rotation of the magnet causes the rotor to rotate; a
power supply configured to generate the magnetic field to drive the
rotatable magnet; and a controller operatively coupled to the power
supply to selectively control the power supply to control the
rotational speed of the rotor.
3. The system of claim 2, further comprising magnetic field
windings configured and arranged to provide the magnetic field.
4. The system of claim 3, wherein the windings are positioned
external to the patient.
5. The system of claim 3, wherein the windings are positioned
within the patient.
6. The system of claim 1, further comprising a shaft along which
the at least one magnet rotates, wherein the shaft does not extend
beyond the stent.
7. The system of claim 1, wherein the at least one rotatable magnet
comprises a plurality of link magnets coupled to one another in
series.
8. The system of claim 1, wherein the at least one blade is
expandable.
9. The system of claim 1, wherein the at least one blade is coupled
directly to the at least one rotatable magnet.
10. A percutaneous pumping system for providing hemodynamic support
to a patient, the percutaneous pumping system comprising: an
expandable stent configured and arranged for insertion into patient
vasculature; at least one rotatable magnet disposed within the
expandable stent, wherein the at least one rotatable magnet is
configured and arranged to be driven to rotate by a magnetic field;
and at least one blade coupled to the at least one rotatable magnet
such that rotation of the at least one magnet causes a
corresponding rotation of the at least one blade.
11. The system of claim 10, further comprising: a power supply
configured to generate the magnetic field to drive the rotatable
magnet; and a controller operatively coupled to the power supply to
selectively control the power supply to control the rotational
speed of the magnet.
12. The system of claim 10, wherein the magnetic field is generated
within the patient.
13. The system of claim 10, wherein the magnetic field is generated
external to the patient.
14. The system of claim 10, wherein the at least one blade is
collapsible.
15. A percutaneous pumping system for providing hemodynamic support
to a patient, the percutaneous pumping system comprising: an
expandable stent defining a flow path and being sized for insertion
into a blood vessel; a rotor rotatably mounted within the stent; at
least one blade mounted to the rotor; at least one rotatable magnet
configured and arranged to be driven to rotate by a magnetic field
generated adjacent the stent, wherein rotation of the magnet causes
the rotor to rotate; and a power supply configured to generate the
magnetic field to drive the rotatable magnet.
16. The system of claim 15, further comprising a controller
operatively coupled to the power supply to selectively control the
power supply to control the rotational speed of the rotor.
17. The system of claim 15, further comprising magnetic field
windings configured and arranged to provide the magnetic field.
18. The system of claim 17, wherein the windings are positioned
external to the patient.
19. The system of claim 17, wherein the windings are positioned
within the patient.
20. The system of claim 15, wherein the at least one blade is
collapsible.
21. The system of claim 15, wherein the at least one blade is
coupled directly to the at least one rotatable magnet.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. patent
application Ser. No. 12/967,856 filed Dec. 14, 2010, now U.S. Pat.
No. 8,734,508, which claims the benefit under 35 U.S.C.
.sctn.119(e) of U.S. Provisional Patent Application Ser. No.
61/288,719, filed on Dec. 21, 2009, the entire disclosures of which
are incorporated herein by reference.
TECHNICAL FIELD
[0002] The present invention is directed to the area of hemodynamic
support systems and methods of making and using the systems. The
present invention is also directed to hemodynamic support systems
having percutaneously-delivered pumping systems powered by magnetic
motors, as well as methods for making and using the hemodynamic
support systems, percutaneously-delivered pumping systems, and
magnetic motors.
BACKGROUND
[0003] Hemodynamic support may be used to provide perfusion of
patient tissues in order to supply the tissues with oxygen and
nutrients and remove undesired wastes. For example, hemodynamic
support is provided for patients with either temporary or long-term
inadequate blood circulation. Hemodynamic support has been provided
to patients in cardiogenic shock (e.g., from primary failure of the
ventricles of the heart), patients recovering from cardiac surgery
(e.g., post acute myocardial infarction), and patients with acute
decompensated heart failure.
BRIEF SUMMARY
[0004] In one embodiment, a percutaneous pumping system for
providing hemodynamic support to a patient includes a pumping
sleeve having a length, a distal end, and a proximal end. The
pumping sleeve defines a lumen extending along the length of the
pumping sleeve from the proximal end to the distal end. The pumping
sleeve is configured and arranged for insertion into patient
vasculature. At least one rotatable magnet is disposed in the
pumping sleeve. The at least one first magnet is configured and
arranged to be driven to rotate by a magnetic field generated
external to the pumping sleeve. At least one impeller is coupled to
the at least one magnet. Rotation of the at least one magnet causes
a corresponding rotation of the at least one impeller. An anchoring
arrangement is coupled to the pumping sleeve. The anchoring
arrangement is configured and arranged to anchor the pumping sleeve
at a target pumping location when the pumping sleeve is inserted
into patient vasculature.
[0005] In another embodiment, a percutaneous pumping system for
providing hemodynamic support to a patient includes an expandable
stent configured and arranged for insertion into patient
vasculature. At least one rotatable magnet is disposed in the
expandable stent. The at least one first magnet is configured and
arranged to be driven to rotate by a magnetic field generated
external to the expandable stent. The at least one magnet rotates
about a shaft. At least one impeller is coupled to the at least one
magnet such that rotation of the at least one magnet causes a
corresponding rotation of the at least one impeller. At least one
strut couples the at least one shaft to the expandable stent to
anchor the at least one magnet within the expandable stent.
[0006] In yet another embodiment, a method for providing
hemodynamic support for a patient includes inserting a percutaneous
pumping system into patient vasculature. The percutaneous pumping
system includes a pumping sleeve having a length, a distal end, and
a proximal end. The pumping sleeve defines a lumen extending along
the length of the pumping sleeve from the proximal end to the
distal end. At least one rotatable magnet is disposed in the
pumping sleeve. The at least one magnet is configured and arranged
to be driven to rotate by a magnetic field generated external to
the pumping sleeve. At least one impeller is coupled to the at
least one magnet such that rotation of the at least one magnet
causes a corresponding rotation of the at least one impeller. The
percutaneous pumping system is anchored to a target pumping
location within the patient vasculature using an anchoring
arrangement coupled to the pumping sleeve. A magnetic field is
generated to cause the at least one magnet to rotate.
BRIEF DESCRIPTION OF THE DRAWINGS
[0007] Non-limiting and non-exhaustive embodiments of the present
invention are described with reference to the following drawings.
In the drawings, like reference numerals refer to like parts
throughout the various figures unless otherwise specified.
[0008] For a better understanding of the present invention,
reference will be made to the following Detailed Description, which
is to be read in association with the accompanying drawings,
wherein:
[0009] FIG. 1 is a schematic longitudinal cross-sectional view of
one embodiment of a pumping assembly positioned in patient
vasculature, according to the invention;
[0010] FIG. 2 is a schematic close-up perspective view of one
embodiment of an impeller disposed over a magnet rotating on a
shaft, according to the invention;
[0011] FIG. 3 is a schematic perspective view of one embodiment of
a rotating magnet and associated magnetic field windings, according
to the invention;
[0012] FIG. 4 is a schematic perspective view of one embodiment of
portions of three orthogonal magnetic field windings positioned on
a plane that form a magnetic field above the plane, according to
the invention;
[0013] FIG. 5 is a schematic perspective view of one embodiment of
a stator winding disposed above a bed driving a motor magnet,
according to the invention;
[0014] FIG. 6 is a schematic perspective view of one embodiment of
a stator winding disposed in a vest, according to the
invention;
[0015] FIG. 7 is a schematic longitudinal cross-sectional view of
one embodiment of a link magnet electrically coupled in series to
other link magnets via electrical interconnects, according to the
invention;
[0016] FIG. 8 is a schematic transverse cross-sectional view of one
embodiment of one of the link magnets of FIG. 7, according to the
invention;
[0017] FIG. 9 is a schematic perspective view of one embodiment of
stator windings arranged in a staggered configuration and disposed
along a sheath disposed over the link magnets of FIG. 7, according
to the invention;
[0018] FIG. 10 is a schematic perspective view of one embodiment of
the link magnets of FIG. 7 having staggered magnetization vectors,
according to the invention;
[0019] FIG. 11 is a schematic side view of a second embodiment of a
pumping assembly disposed in patient vasculature, the pumping
assembly disposed across an aortic valve, according to the
invention;
[0020] FIG. 12 is a schematic side view of a third embodiment of a
pumping assembly disposed in patient vasculature, the pumping
assembly including a plurality of magnets and impellers, according
to the invention; and
[0021] FIG. 13 is a schematic side view of a fourth embodiment of a
pumping assembly disposed over the patient's aortic valve,
according to the invention.
DETAILED DESCRIPTION
[0022] The present invention is directed to the area of hemodynamic
support systems and methods of making and using the systems. The
present invention is also directed to hemodynamic support systems
having percutaneously-delivered pumping systems powered by magnetic
motors, as well as methods for making and using the hemodynamic
support systems, percutaneously-delivered pumping systems, and
magnetic motors.
[0023] A percutaneous pumping system ("blood pump") for providing
at least partial hemodynamic support to a patient utilizes a
magnetic motor to supply power to pump fluid (e.g., blood) within
patient vasculature. In at least some embodiments, the blood pump
pumps at least 5 liters of blood per minute without causing
excessive heat build-up (i.e., without producing enough sustained
heat to cause tissue damage). In at least some embodiments, the
blood pump includes a pumping assembly and an external stator. In
at least some embodiments, the pumping assembly is configured and
arranged for insertion into a patient via an insertion device with
a bore that is no greater than 9 French. In at least some
embodiments, the pumping assembly is configured and arranged to
reduce non-uniform rotation distortion caused by patient tissue
pressing against the blood pump, such as at a bend in patient
vasculature.
[0024] The blood pump includes a magnetic motor that includes a
rotor and a stator. The rotor is a rotatable magnet. In at least
some embodiments, the stator includes a plurality of magnetic field
windings configured and arranged to rotate the magnet by generating
a rotating magnetic field. In at least some embodiments, the
windings are positioned external to a pumping assembly containing
the magnet and a pumping sleeve or stent. In at least some
embodiments, the windings are positioned external to patient
vasculature. In at least some embodiments, the windings are
positioned external to the cardiovascular system of the patient. In
at least some embodiments, the windings are subcutaneously
implanted in the patient. In at least some embodiments, the
windings are positioned external to the patient.
[0025] It may be an advantage to position the windings external to
the patient. Externally positioned windings are not wrapped over an
outer surface of the magnet. Thus, the diameter of a pumping
assembly (and an associated insertion device), which is insertable
into the patient, may be smaller. Blood pumps using extracorporeal
windings may be insertable into patient vasculature that was
previously too small to be accessed with conventional blood pump
systems.
[0026] Extracorporeal windings may also have the advantage of
eliminating the inclusion of motor conductors within the patient
for providing power to operate the motor. Moreover, another
potential advantage to extracorporeal windings is that the windings
may be formed from lower-cost materials than internal windings
because the windings may not be miniaturized or do not need to be
fabricated from materials suitable for insertion into a patient. In
at least some embodiments, suitable extracorporeal windings do not
need to be cooled or use superconductors to generate a large enough
magnetic field to drive rotation of the magnet. Additionally, when
an imaging system uses windings that are cooled or use
superconductors (e.g., to generate a larger magnetic field, or the
like), it is typically easier to cool the windings or use
superconductors when the windings are disposed external to a
patient than when the windings are disposed within a patient.
[0027] In at least some embodiments, the pumping assembly may be
inserted percutaneously into a patient via an accessible blood
vessel, such as the femoral artery, at a site remote from the
target pumping location. The pumping assembly may be guided to many
different target pumping locations, such as the left ventricle, the
aortic valve, the ascending aorta, the descending aorta, or the
like.
[0028] In at least some embodiments, the pumping assembly is
delivered to a target pumping location by an insertion device
(e.g., an introducer sheath, a guidewire, or the like). In at least
some embodiments, the pumping assembly is configured and arranged
for percutaneous insertion into a patient by an insertion device
having a bore that is no greater than 11 French. In at least some
embodiments, the pumping assembly is configured and arranged for
percutaneous insertion into a patient by an insertion device having
a bore that is no greater than 10 French. In at least some
embodiments, the pumping assembly is configured and arranged for
percutaneous insertion into a patient by an insertion device having
a bore that is no greater than 9 French. In at least some
embodiments, the pumping assembly is configured and arranged for
percutaneous insertion into a patient by an insertion device having
a bore that is no greater than 8 French.
[0029] In at least some embodiments, the pumping assembly includes
a pumping sleeve, a rotation apparatus disposed in the pumping
sleeve, and an anchoring arrangement for maintaining the position
of the pumping sleeve at a target pumping location during
operation. In at least some embodiments, the rotation system is
configured and arranged such that rotation of the magnet causes a
corresponding rotation of one or more impellers. In at least some
embodiments, the one or more impellers are configured and arranged
to expand upon release from an insertion device. The one or more
impellers may be formed from any materials suitable for
implantation and expansion from an insertion device including, for
example, shape memory metal or metal mesh material covered with one
or more polymers. In at least some embodiments, the shape memory
metal is magnetic. In at least some embodiments, the shape memory
metal is formed as a permeable magnet. In at least some
embodiments, the shape memory metal is formed as a permanent
magnet.
[0030] In at least some embodiments, the one or more impellers have
expanded diameters of at least 10 mm. In at least some embodiments,
the one or more impellers have expanded diameters of at least 11
mm. In at least some embodiments, the one or more impellers have
expanded diameters of at least 12 mm. In at least some embodiments,
the one or more impellers have expanded diameters of at least 13
mm. In at least some embodiments, the one or more impellers have
expanded diameters of at least 14 mm.
[0031] In at least some embodiments, the pumping assembly is
configured and arranged for temporary insertion into the patient.
In at least some embodiments, the pumping assembly is configured
and arranged to be removed when hemodynamic support is no longer
needed by the patient. In at least some embodiments, the pumping
assembly may be retrieved once hemodynamic support is no longer
needed by the patient. In at least some embodiments, a retrieval
device, such as a retrieval sheath, may be used to retrieve the
pumping assembly. In at least some embodiments, the retrieval
device expands to a diameter that is larger than a diameter of the
pumping sleeve. In at least some embodiments, magnetic attraction
may be used between the pumping assembly and the retrieval device.
For example, a magnet may be disposed on one of the pumping
assembly or the retrieval device and a magnetic material may be
disposed on the other of the pumping assembly or the retrieval
device. In at least some embodiments, a safety line may be used to
facilitate removal of the pumping assembly. In at least some
embodiments, one end of the safety line is attached to the pumping
assembly and the other end of the safety line extends from the
entry point of the pumping assembly into the patient.
[0032] FIG. 1 is a schematic longitudinal cross-sectional view of
one embodiment of a pumping assembly 102 positioned in patient
vasculature, such as a patient's descending aorta 104. The pumping
assembly 102 includes an elongated pumping sleeve 106. One or more
rotatable magnets 108 and one or more impellers 110 are disposed in
the pumping sleeve 106. The one or more impellers 110 are coupled
to the one or more magnets 108 such that rotation of the one or
more magnets 108 causes a corresponding rotation of the impellers
110. In at least some embodiments, the one or more impellers 110
are directly coupled to the one or more magnets 108. In at least
some embodiments, the one or more impellers 110 are disposed, at
least partially, over the one or more magnets 108.
[0033] In at least some embodiments, the one or more magnets 108
are coupled to a magnet support structure 112 that includes a shaft
114 on which the one or more magnets 108 rotate and one or more
struts 116 securing the one or more magnets 108 to the pumping
sleeve 106. In at least some embodiments, the shaft 114 does not
extend beyond the pumping sleeve 106. In at least some embodiments,
the shaft 114 is coupled directly to the one or more struts.
[0034] In at least some embodiments, the shaft 114 is a driveshaft
that rotates with the one or more impellers 110. In at least some
embodiments, such as when the shaft 114 is a driveshaft, the shaft
114 is coupled to the one or more struts 116 via bushings or jewel
bearings (not shown). In at least some embodiments, the one or more
struts 116 are configured and arranged to expand upon release from
an insertion device. In at least some embodiments, the one or more
struts 116 expand such that the one or more magnets 108 are
transversely centered within the pumping sleeve 106.
[0035] In alternate embodiments, the shaft 114 extends from at
least one of the ends of the one or more magnets 108. In at least
some embodiments, at least one of the one or more impellers 110 is
disposed on one of the portions of the shaft 114 extending from one
of the ends of the one or more magnets 108. In at least some
embodiments, at least one of the one or more impellers 110 is
positioned axially from the one or more magnets 108 within the
pumping sleeve 106.
[0036] The pumping assembly 102 also includes an anchoring
arrangement 118 for maintaining the positioning of the pumping
sleeve 106 at the target pumping location during operation. In at
least some embodiments, the anchoring arrangement 118 includes one
or more expandable struts 120 that expand to anchor the pumping
assembly 102 to patient vasculature, such as an inner wall of the
descending aorta 104.
[0037] In at least some embodiments, the target pumping location is
the descending aorta. In at least some embodiments, the pumping
assembly 102 is delivered to a target pumping location in the
descending aorta that is superior to the renal arteries. In at
least some embodiments, the pumping assembly 102 is delivered to a
target pumping location in the descending aorta that is proximal to
the renal arteries. In at least some embodiments, the target
pumping location is in the ascending aorta. In at least some
embodiments, the target pumping location is in both the ascending
aorta and the descending aorta. In at least some embodiments, the
target pumping location is in the vena cava. In at least some
embodiments, the target pumping location is in a proximal coronary,
carotid, or renal artery. In at least some embodiments, the target
pumping location is in a proximal femoral or saphenous vein. In at
least some embodiments, the target pumping location is in another
blood vessel within patient vasculature. In at least some
embodiments, the target pumping location is in another location in
the cardiovascular system.
[0038] In at least some embodiments, the anchoring arrangement 118
is configured and arranged to expand upon release from an insertion
device. In at least some embodiments, the anchoring arrangement 118
is configured and arranged to anchor the pumping assembly to the
target pumping location such that the pumping sleeve 106 is
transversely centered within a lumen of the target pumping
location, such as the descending aorta 104.
[0039] In at least some embodiments, the pumping assembly 102 is
configured and arranged to pump blood downstream to facilitate
perfusion of the lower peripheral arteries. In at least some
embodiments, the pumping assembly 102 is configured and arranged to
pump blood upstream to one or more arterial branches of the aortic
arch to facilitate perfusion of the coronary, cerebral, and upper
peripheral arteries. In at least some embodiments, the pumping
assembly 102 is configured and arranged to alternately pump blood
upstream and downstream. In at least some embodiments, the pumping
assembly 102 is configured and arranged to pump blood downstream
during systole and upstream during diastole.
[0040] FIG. 2 is a schematic close-up perspective view of one
embodiment of a magnet 108 rotating on the shaft 114. In FIG. 2,
the impeller 110 is shown disposed over the magnet 108. In at least
some embodiments, the one or more magnets 108 define a longitudinal
axis 202, shown in FIG. 2 as a two-headed arrow. In at least some
embodiments, the longitudinal axis 202 of the one or more magnets
108 is parallel to a longitudinal axis of the pumping sleeve 106.
In at least some embodiments, the longitudinal axis 202 of the one
or more magnets 108 is parallel with the directionality of blood
flow of the target pumping location within which the one or more
magnets 108 is disposed.
[0041] In at least some embodiments, the one or more magnets 108
are cylindrical. In at least some embodiments, the one or more
magnets 108 each have a magnetization M of no less than 1.4 T. In
at least some embodiments, the one or more magnets 108 each have a
magnetization M of no less than 1.5 T. In at least some
embodiments, the one or more magnets 108 each have a magnetization
M of no less than 1.6 T. In at least some embodiments, the one or
more magnets 108 each have a magnetization vector that is
perpendicular to the longitudinal axis of the one or more magnets
108.
[0042] In at least some embodiments, the one or more magnets 108
each have a diameter that is no greater than 3 mm. In at least some
embodiments, the one or more magnets 108 each have a diameter that
is no greater than 2.5 mm. In at least some embodiments, the one or
more magnets 108 each have a diameter that is no greater than 2 mm.
In at least some embodiments, the one or more magnets 108 each have
a diameter that is no greater than 1.5 mm. In at least some
embodiments, the one or more magnets 108 each have a diameter that
is no greater than 1 mm. In at least some embodiments, the one or
more magnets 108 each have a length that is at least 12 mm. In at
least some embodiments, the one or more magnets 108 each have a
length that is at least 13 mm. In at least some embodiments, the
one or more magnets 108 each have a length that is at least 14 mm.
In at least some embodiments, the one or more magnets 108 each have
a length that is at least 15 mm. In at least some embodiments, the
one or more magnets 108 each have a length that is at least 16 mm.
In at least some embodiments, the one or more magnets 108 each have
a length that is at least 17 mm. It will be understood that larger
or smaller magnets may also be used.
[0043] A magnetic field generated by externally positioned windings
causes the one or more magnets 108 to rotate about the longitudinal
axis 202 of the one or more magnets 108. An applied current creates
the rotating magnetic field in the windings. In at least some
embodiments, the one or more magnets 108 are permanent magnets. The
one or more magnets 108 may be formed from many different magnetic
materials suitable for implantation including, for example,
neodymium-iron-boron, or the like. One example of a suitable
neodymium-iron-boron magnet is available through Hitachi Metals
America Ltd, San Jose, Calif.
[0044] The windings provide a rotating magnetic field to produce a
torque on the one or more magnets 108. Two or more windings
oriented parallel to the longitudinal magnet axis 108 wrap around
the ends one or more magnets 108 as one or more turns to form a
rotating magnetic field. The windings may be powered from any
suitable power source (e.g., an external control module, batteries,
or other power source).
[0045] FIG. 3 is a schematic perspective view of one embodiment of
an exemplary rotatable magnet 302 and associated windings,
represented as orthogonal rectangular boxes 304 and 306. Although
the windings 304 and 306 are shown as two orthogonal rectangles, it
will be understood that the each of the windings 304 and 306 may
represent multiple turns of wire. When the windings 304 and 306 are
spread out, a band of current may be generated instead of the lines
of current shown in FIG. 3. It will also be understood that, as
discussed below, there may be more than two orthogonal windings.
For example, as discussed above and below, (e.g., 108 in FIG. 1;
1108 in FIG. 11; 1210 and 1214 in FIG. 12; and 1308 in FIG. 13) may
be rotated by one or more windings.
[0046] The magnet 302 has a longitudinal (z) axis 308 about which
the magnet 302 rotates. In order for the magnet 302 to rotate about
the longitudinal axis 308, the torque must be about the
longitudinal axis 308. Therefore, the magnetic field generated by
the windings 304 and 306 must lie in a plane perpendicular to the
longitudinal axis 308 with a magnetic field vector H for the
windings 304 and 306 rotating about the longitudinal (z) axis 308
to torque and rotate the magnet 302. FIG. 3 also shows an x-axis
310 and a y-axis 312 that are orthogonal to each other and to the
longitudinal axis 308. As shown in FIG. 3, the magnetization vector
M 314 of the magnet 302 is in an x-y plane that is perpendicular to
the longitudinal axis 308. The winding 304 produces a magnetic
field at the center of the winding 304 that is parallel to the
y-axis 312. The winding 306 produces a magnetic field at the center
of the winding 306 that is parallel to the x-axis 310.
[0047] As discussed above, in at least some embodiments the
windings are disposed external to the patient into which the magnet
is disposed. The extracorporeal windings form a magnetic field
within the patient at a target pumping site. FIG. 4 is a schematic
perspective view of one embodiment of portions of three orthogonal
windings 402-404 positioned on a plane 406. Currents Ix 408, Iy
409, and Iz 410 transmit through the portions of the orthogonal
windings 402-404, respectively, as shown by arrows. When currents
408-410 are transmitted through the windings 402-404 in the
directions indicated, a magnetic field 412 is formed having three
orthogonal components Bx 414, By 415, and Bz 416, respectively, at
the intersection 418 of the orthogonal components Bx 414, By 415,
and Bz 416. In at least some embodiments, the intersection 418
represents a hypothetical location of a rotatable magnet (see e.g.,
108 in FIG. 1) within a patient. In at least some embodiments, the
portions of the windings 402 and 403 positioned on the plane 406
are straight. In at least some embodiments, the portion of the
winding 404 positioned on the plane 406 is a circular loop.
[0048] In at least some embodiments, the plane 406 is positioned
within a surface suitable for supporting a patient. In at least
some embodiments, the plane 406 is positioned above or below a
surface suitable for supporting a patient. In at least some
embodiments, the windings 402-404 are configured such that the
magnetic field 412 is formed within the patient lying on the
surface. In at least some embodiments, the magnetic field 412 has a
constant amplitude.
[0049] Each of the portions of the orthogonal windings 402-404
positioned on the plane 406 includes a return path (not shown). The
return paths of the windings 402-404 may be in any configuration.
In preferred embodiments, the return paths are positioned away from
the portions of the windings 402-404 positioned on the plane 406.
It will be understood that each of the windings 402-404 represents
one or more turns of a wire.
[0050] When the magnetic field 412 is formed at a height (z) above
the plane 406, the magnetic field 412 is given by:
H.sub.x,y=M.sub.x,y/(27.pi.z); and
H.sub.z=NI.sub.Z/(D[l+(2z/D).sup.2].sup.2);
It will be appreciated that adjusting the currents I.sub.x, I.sub.y
and I.sub.z independently allows the above magnetic field
components to take on any value. In particular, the magnetic field
vector may be directed perpendicular to the axis of a pump magnet
located at point z. By varying the field components over time, the
magnetic field may be rotated about the longitudinal axis of a pump
magnet located at point z.
[0051] In at least some embodiments, z is formed at a location such
that the magnetic field is within a patient lying on a surface at,
or adjacent to, the plane 406. For example, when a target pumping
location is the patient's aorta, and when the patient is lying on a
surface at, or adjacent to, the plane 406, z, in this example, is
no greater than approximately 0.3 meters. In one embodiment, N=200
and I.sub.x,y=3 amps, where N=the number of turns in the winding.
In at least some embodiments, the windings 402-404 are formed from
stranded wire that forms a flexible band of current.
[0052] FIG. 5 is a schematic perspective view of one embodiment of
a three-phase winding 502 generating a magnetic field that drives
rotation of a motor magnet 504 around a longitudinal axis 506 of
the magnet 504. A controller 508 is coupled to the three-phase
winding 502 by one or more conductors 510. In at least some
embodiments, the controller 508 provides power for generating the
magnetic field. In FIG. 5, the three-phase winding 502 is shown
disposed on a plane 512. In at least some embodiments, the plane
512 is a bed on which a patient may lie. In at least some
embodiments, the three-phase winding 502 may be repositioned to
allow patient access to the bed. In at least some embodiments, the
three-phase winding 502 may be used by the patient as a bed
railing, an arm rest, or the like during a procedure.
[0053] In alternate embodiments, the windings are disposed in a
garment that may be worn by a patient. FIG. 6 is a schematic view
of one embodiment of a vest 602 (shown in dotted lines) that may be
worn by a patient. The vest 602 includes three-phase winding
604-606. In at least some embodiments, the vest 602 includes a
controller 608 coupled to the vest 602. In at least some
embodiments, the controller 608 includes an electronic subsystem
for controlling one or more operations of the blood pump, such as
drive electronics and controls. In at least some embodiments, the
controller 608 includes a power supply, such as one or more
batteries. It will be understood that the three-phase winding
604-606 may be incorporated into many different types of garments
besides vests including, for example, jackets, coats, sweaters,
shirts, overalls, coveralls, robes, wraps, or the like.
[0054] In at least some embodiments, the windings are formed from
rigid or semi-rigid materials using multiple-phase winding
geometries. It will be understood that there are many different
multiple-phase winding geometries and current configurations that
may be employed to form a rotating magnetic field. For example, the
windings may include, for example, a two-phase winding, a
three-phase winding, a four-phase winding, a five-phase winding, or
more multiple-phase winding geometries. It will be understood that
a motor may include many other multiple-phase winding geometries.
In a two-phase winding geometry, for example, the currents in the
two windings are out of phase by 90.degree.. For a three-phase
winding, there are three lines of sinusoidal current that are out
of phase by zero, 120.degree., and 240.degree., with the three
current lines also spaced by 120.degree., resulting in a uniformly
rotating magnetic field that can drive a cylindrical rotor magnet
magnetized perpendicular to the current lines.
[0055] In at least some embodiments, the magnet may include a
plurality of link magnets coupled to one another in series. FIG. 7
is a schematic longitudinal cross-sectional view of one embodiment
of a link magnet 702 mechanically coupled in series to other link
magnets 704 and 706 via a flexible drive shaft 720 that includes
flexible drive shaft segments 708 and 710, respectively. Magnets
702, 704, and 706 are surrounded by a flexible sheath 712. The wall
of sheath 712 contains three lines of electrical conductors that
form a three phase winding. In at least some embodiments, one or
more movement limiting structures may be disposed at one or more
locations anywhere along the sheath. In FIG. 7, indents 714 and 716
are positioned between the link magnets. The indents 714 and 716
serve as stops that limit longitudinal movements of the magnets
relative to the sheath. The indents 714 and 716 contain the three
phase windings, continuing the flow of current down the length of
the sheath.
[0056] FIG. 8 is a schematic transverse cross-sectional view of one
embodiment of the link magnet 702. In at least some embodiments, a
sheath 712 is disposed over the link magnets 702, 704, and 706.
Electrical windings 802, 803, and 804 carry three phase currents
that apply equal torques to magnets 702, 704, and 706. In at least
some embodiments, the link magnet 702 is mechanically coupled to
link magnets 704 and 706 via the flexible drive shaft 720. In at
least some embodiments, the flexible drive shaft 720 rotates along
with magnets 702, 704, and 706 over a guidewire (not shown) which
passes through the center lumen 806 of the flexible drive shaft
720.
[0057] In at least some embodiments, a gap 718 may be formed
between the link magnet 702 and the sheath 712. In at least some
embodiments, the gap 718 may be at least partially filled with
lubricant to reduce friction as the link magnet 702 rotates against
a non-rotating sheath 712. In at least some embodiments, the
lubricant is a magnetic fluid (e.g., a ferrofluid, or the like)
that adheres to the link magnet 702 and shears at or near the
sheath 712 when the link magnet 702 rotates.
[0058] Motor torque is proportional to the product of the number of
link magnets and the length of each link magnet. Motor torque is
also proportional to the diameters of the link magnets. Thus, a
sliding scale relationship exists between the number of magnet
links and the size of the link magnets. For example, when the size
of the link magnets is reduced, the number of link magnets may
increase to produce a given amount of motor torque on the flexible
drive shaft 720.
[0059] As discussed above, rotation of the link magnets 702, 704,
and 706 may be powered by a magnetic field generated by external
stator windings as described for the previous embodiments. It will
be understood, however, that in alternate embodiments rotation of
the link magnets 702, 704, and 706 may be powered by stator
windings disposed in the sheath 712. For example, FIG. 9 is a
schematic perspective view of one embodiment of windings 902
disposed along the sheath 712 in a staggered configuration. When
motor torque is applied to the flexible drive shaft 720, the motor
torque may be designed to twist the flexible drive shaft 720 along
its length. The staggered configuration of windings 902 are
configured and arranged to compensate for drive shaft twisting so
that the angle between the magnetic field of the windings and the
individual magnet magnetization vectors is the same for each
magnet. Thus the torque exerted by each magnet on the drive shaft
is the same for each magnet as the drive shaft rotates. In
alternate embodiments, the windings 902 may extend linearly along a
longitudinal axis of the sheath 712. Twisting of the flexible drive
shaft 720 may also be compensated for by forming a distal end of
the sheath 712 such that the distal end of the sheath 712 is
twisted to form a spiral configuration of the windings.
[0060] Another way to compensate for twisting of flexible drive
shaft 720 is to stagger the direction of the magnetization vector
of the link magnets. FIG. 10 is a schematic perspective view of one
embodiment of the link magnets 702, 704, and 706, each having
magnetization vectors, indicated by arrows, that are staggered in
orientation from one another to compensate for twisting of the
flexible drive shaft 720.
[0061] As discussed above, it is desirable to be able to pump at
least 5 liters of blood per minute in order to provide total
hemodynamic support for a patient, although there are applications
for blood pumps with less throughput. Without wishing to be held to
any particular values, it is believed the pumping assembly 102 can
pump 5 liters of blood per minute using one or more impellers
having diameters of 12 mm and a magnet having a 2.5 mm diameter and
a 15 mm length. The power to pump 5 liters per minute against a
blood pressure head of nominally 100 mm Hg can be calculated using
the formula:
P=p dV/dt;
where P=power in Watts; p=pressure head in Nt/m.sup.2; and
dV/dt=blood flow rate in m.sup.3/sec. Using the known values 100 mm
Hg=1.3.times.10.sup.4 Nt/m.sup.2 and 5
liters/min=8.3.times.10''.sup.5 m.sup.3/sec, then P=1.1 Watts of
mechanical power. In other words, nominally 1.1 Watts of power are
used to provide hemodynamic support to a human. The actual
mechanical input power requirement may depend upon the efficiency
of the impeller design. Some of the input power is often dissipated
in backflow and eddy formation, or in more extreme phenomena, such
as cavitation. Assuming a mechanical efficiency of 50%, 2.2 Watts
of mechanical power can pump 5 liters of blood per minute.
[0062] Small electrical-motor-driven pumps are often less efficient
than larger pumps because of Ohmic heat generated in the stator
windings by the relatively high current needed to create the
pumping torque. A larger winding volume often generates less heat
for a given torque output. Thus, small electric pumps may use rapid
blood flow to dissipate heat. In low blood flow, or near the wall
of an artery, the pump temperature may rise, thereby resulting in
shut down for safety.
[0063] One advantage of utilizing external stator windings is that
heat build-up can occur external to the pumping assembly. Thus,
heat build-up is less of a concern at the target pumping location.
Additionally, as discussed above, external windings may not have
the same size constraints as windings would have if the windings
were disposed on a pumping assembly. Thus, the mass of the external
windings may be orders of magnitude larger than windings disposed
on an internal pumping assembly. Therefore, pumping assemblies
utilizing external windings may be enabled to convert electrical
energy to mechanical energy with less heat generated within the
patient than pumping assemblies utilizing windings within the
pumping assemblies.
[0064] When windings are disposed in a sheath surrounding link
magnets as in FIG. 7, it may be an advantage to use a plurality of
link magnets because increasing the number of link magnets may
decrease the amount of current used to create a given torque. Also,
increasing the number of link magnets may decrease the amount of
heat generated by the motor. Furthermore, increasing the number of
link magnets may increase the efficiency of the motor.
[0065] The mechanical power output of a two-pole magnet rotor
driven by a rotating magnetic field generated by extracorporeal
stator windings is given by:
P=.tau..omega.;
where P=mechanical power output in Watts; .tau.=magnetic torque in
Nt-m; .omega.=angular speed in rad/sec=2 .pi.f; and f=rotation
speed in revolutions/sec, or Hz.
[0066] The mechanical torque for an oriented rare earth magnet for
which magnetization is constant throughout the magnet volume (e.g.,
a neodymium-iron-boron magnet, or the like) is given by:
.tau.=MVH;
where M=magnet magnetization in Tesla; V=magnet volume in m.sup.3;
and H=winding magnetic field in Amp/m.
[0067] Without wishing to be held to any particular values,
consider a magnet having a volume of 7.4.times.10.sup.-8 m.sup.3
and magnetization of 1.5 Tesla rotating at 500 Hz with a power
output of 2.2 Watts. Combining the previous two equations and
solving for the winding magnetic field (H) in Amp/m, H=6,300 Amp/m,
or about 80 Gauss.
[0068] The magnetic field from a three-phase winding is given
by:
H=3NI/4.pi.r;
where N=number of turns of each winding; I=current amplitude in
Amps; r=distance from a winding to a center of the winding in m;
and H=6,300 Amps/m. If r=6 inches=0.15 m, or about half the
back-to-front width of a large person, and N=1000 turns, then
solving for I yields 1=4 Amps to create a magnetic field sufficient
to power the magnet.
[0069] As shown in FIG. 5, in at least some embodiments the stator
windings are disposed in bed railings. Again, without wishing to be
held to any particular values, if the windings utilize a winding
length of 20 inches wrapped into 1000 turns of AWG #10 copper
magnet wire having a resistance of 0.001 Ohms/ft, then the winding
bobbin may be about 3 inches by 3 inches and may double as bed
railings. The total length of wire in each bobbin, accordingly, is
about 5,000 feet and has a resistance of about 5 Ohms. At a maximum
output of 5 liters per minute at 4 Amps (as calculated above), the
heat generated in the windings=I.sup.2R/2 (for sinusoids)=40 Watts,
which is easily dissipated in bed railings in an ambient
environment. Using heavier windings generates less heat. Design
trade-offs may include, for example, the volume of the windings,
the diameter of the bed railings, the temperature rise of the bed
railings above ambient temperature (if any), and the power
requirement of the external current supply. For example, in at
least some embodiments, the windings may be actively cooled to
enable a given magnetic field to be generated using smaller
diameter windings.
[0070] As shown in FIG. 6, in at least some embodiments the stator
windings are disposed in a garment. Smaller windings (e.g.,
windings disposed in a garment, as opposed to winding disposed in
bed railings) may use less current to generate the same output, so
smaller and lighter windings may be used. When winding length is
reduced, resistance is also reduced. For example, when all of the
distances of a three-phase winding are cut in half from the bed
railing example, the generated heat may be reduced by a factor of
eight, to 5 Watts (using the values from the previous
calculations). Design trade-offs between heat generation, power
output, and winding weight can be varied across a broad spectrum of
winding geometries. As shown in FIGS. 7-10, in at least some
embodiments the magnet is segmented into link magnets to enable the
length of the magnet to be increased, while maintaining adequate
flexibility to bend in patient vasculature. Doubling the overall
length of the magnets may yield the same pump output with half the
current and one-quarter the heat generation.
[0071] In at least some embodiments, the stator windings are formed
from one or more magnetic materials including, for example, iron,
nickel-iron, iron-cobalt-chromium, or the like. Forming the
windings from one or more magnetic materials may increase the
efficiency of the windings by reducing the winding volume or
winding current needed to generate a magnet field sufficient to
rotate the magnet. In at least some alternate embodiments, the
external magnetic field is generated by one or more permanent
magnets rotating external to the patient. In at least some
embodiments, the one or more permanent magnets rotating external to
the patient are rotated by a power source, such as a windings
surrounding the permanent magnet, a conventional motor, or the
like. In at least some embodiments, external magnets are
mechanically rotated or tilted by conventional electric motors.
[0072] FIG. 11 is a schematic side view of one embodiment of a
pumping assembly 1102 disposed in the left ventricle of a patient's
heart. Blood is pumped across the patient's aortic valve 1104 and
into the patient's aorta. The pumping assembly 1102 includes an
elongated pumping sleeve 1106. A rotatable magnet 1108 and one or
more impellers 1110 are disposed in the pumping sleeve 1106. The
one or more impellers 1110 are coupled to the one or more magnets
1108 such that rotation of the one or more magnets 1108 causes a
corresponding rotation of the impellers 1110. In at least some
embodiments, the one or more impellers 1110 are disposed, at least
partially, over the one or more magnets 1108.
[0073] In at least some embodiments, the one or more magnets 1108
are coupled to a support structure 1112 that includes a shaft 1114
on which the one or more magnets 1108 rotate, and one or more
struts 1116 that secure the one or more magnets 1108 to the pumping
sleeve 1106 via the shaft 1114 and, optionally, bushings. In at
least some embodiments, the one or more struts 1116 are configured
and arranged to expand upon release from an insertion device. In at
least some embodiments, the one or more struts 1116 expand such
that the magnet 1108 is transversely centered within the pumping
sleeve 1106. In at least some embodiments, at least one of the one
or more impellers 1110 are coupled to the shaft 1114. In at least
some embodiments, at least one of the one or more impellers 1110
are coupled to the shaft 1114 such that the at least one of the one
or more impellers 1110 is separated axially from the one or more
magnets 1108.
[0074] The pumping assembly 1102 also includes an anchoring
arrangement 1118 for maintaining the positioning of the pumping
sleeve 1106 at the target pumping location during operation. In at
least some embodiments, the anchoring arrangement 1118 includes one
or more stops (e.g., mesh stops) 1120 disposed along a length of
the pumping sleeve 1106 such that, when the pumping sleeve 1106 is
extended across the patient's aortic valve 1104, the one or more
stops 1120 are positioned on one or more sides of the aortic valve
1104. In at least some embodiments, the one or more stops 1120 are
configured and arranged to expand upon release from an insertion
device. In at least some embodiments, the one or more stops 1120
expand such that the pumping assembly is transversely centered
within the aortic valve 1104.
[0075] In at least some embodiments, the target pumping location is
the region surrounding the patient's aortic valve 1104. In at least
some embodiments, the target pumping location includes the
patient's left ventricle 1124. In at least some embodiments, the
target pumping location includes the patient's ascending aorta
1126. In at least some embodiments, the target pumping location
extends from the patient's left ventricle 1124 to the patient's
ascending aorta 1126. In at least some embodiments, the target
pumping location extends from the patient's left ventricle 1124 to
the patient's descending aorta (see e.g., FIG. 12).
[0076] The pumping sleeve 1106 has an inlet 1128 at a proximal end
of the pumping sleeve 1106 and an outlet 1130 at a distal end of
the pumping sleeve 1106. In at least some embodiments, the inlet
1128 is disposed in the patient's left ventricle 1124. In at least
some embodiments, the outlet 1130 is disposed in the patient's
ascending aorta 1126.
[0077] In at least some embodiments, the pumping sleeve 1106 is
cylindrical. In at least some embodiments, the pumping sleeve 1106
is isodiametric. In at least some embodiments, the pumping sleeve
1106 has a reduced-diameter region 1132 disposed along the length
of the pumping sleeve 1106 such that, when the pumping sleeve 1106
is extended across the patient's aortic valve 1104, the
reduced-diameter region 1132 aligns with the patient's aortic valve
1104. In at least some embodiments, the reduced-diameter portion
1132 of the pumping sleeve 1106 facilitates reduction of damage to
the aortic valve 1104 caused by the pumping assembly 1106
contacting the aortic valve 1104.
[0078] In at least some embodiments, at least one of the inlet 1128
or the outlet 1130 of the pumping sleeve 1106 are configured and
arranged to expand upon release from an insertion device. In at
least some embodiments, the pumping assembly 1102 operates without
an electrical lead extending from the target pumping location to
the entry point of the pumping assembly 1102 into the patient. In
at least some embodiments, the pumping assembly 1102 operates
without the shaft 1114 extending from the target pumping location
to the entry point of the pumping assembly 1102 into the
patient.
[0079] The pumping assembly 1102 is configured and arranged to pump
blood downstream from the left ventricle 1128 through the pumping
sleeve 1106. In at least some embodiments, the pumping assembly
1102 continuously pumps blood during operation. In at least some
embodiments, the pumping assembly 1102 cycles between pumping blood
and not pumping blood. In at least some embodiments, such as when
the pumping assembly is disposed in the descending aorta, the
pumping assembly 1102 cycles between pumping blood downstream
(e.g., down the descending aorta) and pumping blood upstream (e.g.,
back up the aorta to one or more branching vessels, such as the
left subclavian artery, the left common carotid artery, the
brachiocephalic trunk, or the coronary arteries).
[0080] In at least some embodiments, there may be multiple target
pumping locations. In at least some embodiments, a different
pumping assembly may be disposed at each of the multiple target
pumping locations. In at least some embodiments, a single pumping
assembly may be used to pump blood at multiple target pumping
locations. In at least some embodiments, a single set of stator
windings may be used to generate a magnetic field for rotating a
plurality of magnets (and impellers coupled to the magnets).
[0081] FIG. 12 is a schematic side view of one embodiment of a
pumping assembly 1202 disposed in patient vasculature, such as a
region extending from the patient's left ventricle 1204 to the
patient's descending aorta 1206. The pumping assembly 1202 includes
an elongated pumping sleeve 1208. A first magnet 1210 is positioned
in the pumping sleeve 1208 such that the first magnet 1210 is
disposed in the patient's left ventricle 1204 and a second magnet
1214 is positioned in the pumping sleeve 1208 such that the second
magnet 1214 is positioned in the patient's descending aorta 1206.
In at least some embodiments, one or more first impellers 1218 are
coupled to the first magnet 1210 and one more second impellers 1220
are coupled to the second magnet 1214. In at least some
embodiments, longitudinal axes of magnets 1210 and 1214 are aligned
approximately in the same direction in space, so that a single
external rotating magnetic field may simultaneously rotate both
magnets 1210 and 1214 and both impellers 1218 and 1220.
[0082] In at least some embodiments, the magnets 1210 and 1214 are
coupled to expandable magnet support structures 1222 and 1224,
respectively, that secure the magnets 1210 and 1214 to the pumping
sleeve 1208. The pumping assembly 1202 also includes anchoring
arrangements 1226 and 1228 positioned in proximity to magnets 1210
and 1214, respectively, for maintaining the positioning of the
pumping sleeve 1206 at the target pumping location(s) during
operation.
[0083] The pumping sleeve 1208 has a first inlet 1230 at a proximal
end of the pumping sleeve 1208 and a first outlet 1232 at a distal
end of the pumping sleeve 1208. In at least some embodiments, the
first inlet 1230 is positioned in the patient's left ventricle 1204
during operation of the pumping assembly 1202. In at least some
embodiments, the first outlet 1232 is disposed in the patient's
descending aorta 1206. In at least some embodiments, at least one
of the first inlet 1230 or the first outlet 1232 of the pumping
sleeve 1208 is configured and arranged to expand upon release from
an insertion device.
[0084] In at least some embodiments, the pumping sleeve 1208
defines one or more additional inlets, such as second inlet 1234.
The one or more additional inlets may be disposed anywhere along a
length of the pumping sleeve 1208. In at least some embodiments,
the second inlet 1234 is defined in the pumping sleeve 1208 such
that the second inlet 1234 is disposed in the patient's descending
aorta 1206 during operation. In at least some embodiments, the
pumping sleeve 1208 defines one or more additional outlets, such as
second outlet 1236. The one or more additional outlets may be
disposed anywhere along a length of the pumping sleeve 1208. In at
least some embodiments, the second outlet 1236 is defined in the
pumping sleeve 1208 such that the second outlet 1236 is disposed in
the patient's ascending aorta 1238 during operation.
[0085] In at least some embodiments, the one or more first
impellers 1218 pump blood from the first inlet 1230 to the second
outlet 1236 and to a region in proximity to the one or more second
impellers 1220. In at least some embodiments, the one or more first
impellers 1218 pump blood continuously during operation. In at
least some embodiments, the one or more second impellers 1220 pump
blood primarily between the second inlet 1234 to the first outlet
1232. In at least some embodiments, the one or more second
impellers 1220 pump blood from the second inlet 1234 to the first
outlet 1232 during systole. In at least some embodiments, the one
or more second impellers 1220 pump blood from the first outlet 1232
to the second inlet 1234 to during diastole.
[0086] In at least some embodiments, the pumping assembly does not
include a pumping sleeve. FIG. 13 is a schematic side view of one
embodiment of a pumping assembly 1302 disposed over the patient's
aortic valve 1304. The pumping assembly 1302 includes a support
frame 1306, such as an expandable stent, to anchor the pumping
assembly 1302 in position at a target pumping location, such as the
patient's aortic valve 1304. A rotatable magnet 1308 and one or
more impellers 1310 are disposed in the support frame 1306. In at
least some embodiments, the one or more impellers 1310 are coupled
to the magnet 1308. In at least some embodiments, the one or more
impellers 1310 are coupled to the magnet 1308 such that rotation of
the magnet 1308 causes a corresponding rotation of the impellers
1310. In at least some embodiments, the one or more impellers 1310
are disposed, at least partially, over the magnet 1308.
[0087] In at least some embodiments, the magnet 1308 is configured
and arranged to rotate on a shaft 1314. In at least some
embodiments, the pumping assembly 1302 includes one or more struts
1316 securing the magnet 1308 to the support frame 1306 via the
shaft 1314. In at least some embodiments, the one or more struts
1316 are configured and arranged to expand upon release from an
insertion device. In at least some embodiments, the one or more
struts 1316 expand such that the magnet 1308 is transversely
centered within the support frame 1306.
[0088] In at least some embodiments, the pumping assembly 1302 is
configured and arranged to pump blood continuously across the
aortic valve 1304. In at least some embodiments, the external
stator windings may be implanted in the patient in proximity to the
aortic valve 1304 including, for example, the pericardial space,
right atrium, a subcutaneous pocket formed in the thorax. In at
least some embodiments, an associated electronic subassembly and
controllers may also be implanted in the patient in proximity to
the aortic valve 1304. In at least some embodiments, the pumping
assembly 1302 and stator windings may be powered by implanted
batteries that inductively recharged while implanted in the
patient.
[0089] The above specification, examples and data provide a
description of the manufacture and use of the composition of the
invention. Since many embodiments of the invention can be made
without departing from the spirit and scope of the invention, the
invention also resides in the claims hereinafter appended.
* * * * *