Source: https://patents.google.com/patent/US9777732B2/en
Timestamp: 2019-07-23 17:03:22
Document Index: 741490738

Matched Legal Cases: ['Application No. 2007207782', 'Application No. 200780003014', 'Application No. 200780003014', 'Application No. 2014', 'Application No. 2014', 'Application No. 2008', 'Application No. 200780003014']

US9777732B2 - Hydrodynamic thrust bearings for rotary blood pump - Google Patents
Hydrodynamic thrust bearings for rotary blood pump Download PDF
US9777732B2
US9777732B2 US13/955,955 US201313955955A US9777732B2 US 9777732 B2 US9777732 B2 US 9777732B2 US 201313955955 A US201313955955 A US 201313955955A US 9777732 B2 US9777732 B2 US 9777732B2
US13/955,955
US20130317283A1 (en
2006-01-13 Priority to US75879506P priority Critical
2006-01-13 Priority to US75879306P priority
2006-01-13 Priority to US75879406P priority
2006-01-13 Priority to US75889206P priority
2007-01-16 Priority to US11/654,216 priority patent/US8512013B2/en
2013-07-31 Priority to US13/955,955 priority patent/US9777732B2/en
2013-07-31 Application filed by HeartWare Inc filed Critical HeartWare Inc
2013-11-28 Publication of US20130317283A1 publication Critical patent/US20130317283A1/en
2014-04-09 Assigned to HEARTWARE, INC. reassignment HEARTWARE, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LAROSE, JEFFREY A., SHAMBAUGH, CHARLES
2017-10-03 Publication of US9777732B2 publication Critical patent/US9777732B2/en
F04D13/066—Floating-units
This application is a continuation of U.S. Ser. No. 11/654,216, filed Jan. 16, 2007, and claims the benefit of U.S. Provisional Application Nos. 60/758,793, filed Jan. 13, 2006; 60/758,892, filed Jan. 13, 2006; 60/758,795, filed Jan. 13, 2006; and 60/758,794, filed Jan. 13, 2006, the entire contents of each of which are hereby incorporated by reference in their entirety into this application.
Ventricular assist devices may utilize a blood pump for imparting momentum to a patient's blood thereby driving the blood to a higher pressure. One example of a ventricular assist device is a Left Ventricular Assist Device (LVAD). The LVAD is attached to the left ventricle of the patient's heart where oxygenated blood enters the LVAD through a blood inlet of the LVAD. The LVAD then imparts momentum to the blood. By connecting a blood outlet of the LVAD to the patient's aorta, pumped blood may reenter the patient's circulatory system.
Several forms of magnetic bearings have been developed. In one form, passive magnetic bearings in the form of permanent magnets can be embedded in both the and the pump housing to provide magnetic coupling that may keep the impeller suspended in position within the pump casing. Such permanent magnets embedded in both the rotor and the pump casing provide repulsive forces that may keep the impeller suspended within the pump casing. Such magnetic bearings are said to be passive magnetic bearings as no control is used to keep the impeller properly centered. While passive magnetic bearings may be effective at keeping the impeller suspended in one direction, for example in the radial direction, it has been shown that such passive magnetic bearings alone cannot keep an impeller suspended in both the axial and radial directions.
Active magnetic bearings in the form of electromagnets can be used, for example in or on the pump housing, magnetically to couple with and to drive the impeller. Power to the electromagnets may then be varied, as required, to adjust the magnetic field in response to displacement so that the impeller may be kept in position.
Electromagnets may also be used, for example, in the pump casing, to provide the repulsive magnetic force. These bearings are said to be active magnetic bearings as the magnetic fields are actively controlled to maintain proper impeller position.
FIG. 7 is an exploded view of a magnetic assembly for supporting and driving an impeller according to an embodiment of the present invention;
With reference to FIG. 1, a motor rotor or pump impeller 22 is located within the pumping chamber 3 between the upper pump casing 1 and the lower pump casing 2. The impeller 22 is circular in cross section and may have a diameter of an inch or an inch and a quarter. The impeller is provided with a central hole 23. A center post or spindle 24 is attached to the lower pump casing 2 and protrudes from the axial, center thereof through the impeller hole 23 when the pump is assembled to support rotation of the impeller in the manner described in detail below. The center post 24 is provided with a peripheral lower flange 26 by which a lower annular ceramic disc 27 is retained to an interior surface of the lower pump casing 2. In one embodiment, the gap between the outer diameter of the center post 24 and the diameter of the impeller hole 23 is in the range of from 0.019 inches to 0.029 inches. The top portion of the center post 24 is formed as a conical surface 28. A substantial portion of the conical, surface 28 of the center post protrudes above the impeller hole 23 during operation of the pump. In one embodiment, the radius of curvature of the cone shape is a relatively constant 0.389 inches. The tip of the cone is not necessarily a sharp point having, in one embodiment, a blending radius of 0.010 inches.
In one embodiment, there is formed on each of the raised impeller bodies 32 an inwardly facing and downwardly tapered curved section 46 inside of the inner shroud 43. An axial drop distance for each section 46 is about 0.012 inches and the angle of taper is about 8°. The section 46 assists in directing blood deflected from the conical surface 28 of the central post 24 to the central portion of the impeller, which then flows from there into the slots 33 formed between the impeller bodies 32.
The impeller may be a single integral structure made of a magnetically isotropic alloy. The material of a one-piece impeller of the type described above may be biocompatible to avoid having to coat the impeller or sub-assemblies. An example of a suitable magnetically isotropic biocompatible material is an alloy of approximately 77.6% to platinum (by weight) and 22.4% (by weight) cobalt. Such a one-piece impeller may be easier and less expensive to manufacture than impellers formed from multiple parts. Each raised impeller body 32 may have a magnetized portion. Magnetization of such an impeller may be performed by techniques known in the art, such as the exposure to a relatively strong magnetic field. In one embodiment, the raised projection surfaces of each of the impeller bodies may be magnetized to provide magnetic poles. The magnetic poles of the impeller couple magnetically with magnetic poles provided by motor stators 69 (FIG. 5) thereby enabling one or both of the stators to provide both a magnetic drive force to cause the impeller to rotate within the pumping chamber and magnetic axial and radial support. In one embodiment, every other upper projection surface is magnetized to the same magnetic pole while the projection surfaces therebetween are magnetized to have the opposite magnetic pole. For example, where an upper projection surface has a North magnetic pole each projection surface on either side has a South magnetic pole. The particular arrangement of magnetic poles may be determined as desired without departing from the scope of the present invention. It will be understood that the motor stator coils that drive the impeller provide magnetic poles in a pattern complementary to those employed on the impeller.
In one embodiment, and as seen best in FIG. 6, each of the three center post bearing magnets 57 may provide a magnetic vector oriented in the axial direction, for example either north-on-top, south-on-bottom (N-S) or south-on-top, north-on-bottom (S-N). Thus, the stack of center post bearing magnets 57 may have alternating magnetization such that the polarizations of the magnets within the stack may be N-S, S-N, N-S or S-N, N-S, S-N, as desired, whereby the magnetic forces established by each ring shaped magnet 57 of the stack 56 act to repulse its adjacent magnet in the axial direction.
a pumping chamber in fluid communication with a primary fluid flow path;
an impeller rotatable on an axis within the pumping chamber and having a plurality of upper surface areas circumferentially disposed about the axis, each upper surface area facing an interior wall of the pumping chamber as the impeller rotates, each of at least a diametrically opposed pair of the upper surface areas being configured with an inclined surface area tapered in an upward axial direction and defining a hydrodynamic bearing surface having a lower pressure fluid entrance end and a higher pressure fluid exit end causing an increase in pressure acting axially downwardly on the impeller as the impeller rotates; and
each of the plurality of upper surface areas further including a pressure relief surface downstream of the higher pressure fluid exit, the pressure relief surface being configured to lower the hydrodynamic pressure from the high pressure fluid exit to form a lower pressure fluid exit end and to define a secondary fluid flow path to impel fluid into an adjacent upper surface area as the impeller rotates, the higher pressure entrance end of the downstream pressure relief surface being spaced from the higher pressure fluid exit end of the hydrodynamic bearing surface by a flat bridging surface area of the same respective upper surface area therebetween, the lower pressure fluid exit end and the lower pressure fluid entrance end of adjacent ones of the upper surface areas engaging axially directed spaced apart sidewalls having unequal surface areas, the sidewalls defining fluid flow channels therebetween.
2. The rotary blood pump of claim 1 in which an angle of inclination of each hydrodynamic bearing surface is less than one degree relative to the horizontal.
3. The rotary blood pump of claim 1 in which the flat bridging surface is about 0.050 inches wide at its narrowest point with a tolerance of ±0.028 inches.
4. The rotary blood pump of claim 1 in which an angle of taper of each pressure relief surface is more severe than the angle of inclination of each hydrodynamic bearing surface.
5. The rotary blood pump of claim 1 in which each of the upper surface areas defines a hydrodynamic bearing surface and an associated pressure relief surface.
6. The rotary blood pump of claim 1 in which each upper surface area is formed on one of a plurality of raised bodies, a selected portion of one or more of which is configured for magnetization.
7. The rotary blood pump of claim 1 comprising a one-piece ferromagnetic impeller made from an alloy of approximately 77.6% platinum by weight and 22.4% cobalt by weight.
8. The rotary blood pump of claim 6 in which each raised body is configured with two straight sidewalls of unequal length which intersect at approximately 90°.
9. The rotary blood pump of claim 8 in which the longer side wall faces the shorter side wall of an adjacent raised body across a respective secondary fluid flow path therebetween.
10. The rotary blood pump of claim 6 in which each hydrodynamic bearing surface comprises an inwardly facing and downwardly tapered concave inner wall section of a raised body.
11. The rotary blood pump of claim 10 in which an angle drop for each such downwardly tapered concave inner wall section is about 0.012 inches and an angle of downward taper thereof is about 8°.
12. The rotary blood pump of claim 6 in which a cavity in each raised body is fitted with a permanent magnet, the permanent magnets being approximately 90° apart at a periphery of the impeller with solid wall members therebetween.
US13/955,955 2006-01-13 2013-07-31 Hydrodynamic thrust bearings for rotary blood pump Active 2028-10-02 US9777732B2 (en)
US75879506P true 2006-01-13 2006-01-13
US75879306P true 2006-01-13 2006-01-13
US75879406P true 2006-01-13 2006-01-13
US75889206P true 2006-01-13 2006-01-13
US11/654,216 US8512013B2 (en) 2006-01-13 2007-01-16 Hydrodynamic thrust bearings for rotary blood pumps
US13/955,955 US9777732B2 (en) 2006-01-13 2013-07-31 Hydrodynamic thrust bearings for rotary blood pump
US15/689,567 US20180010608A1 (en) 2006-01-13 2017-08-29 Hydrodynamic thrust bearings for rotary blood pump
US11/654,216 Continuation US8512013B2 (en) 2006-01-13 2007-01-16 Hydrodynamic thrust bearings for rotary blood pumps
US15/689,567 Continuation US20180010608A1 (en) 2006-01-13 2017-08-29 Hydrodynamic thrust bearings for rotary blood pump
US20130317283A1 US20130317283A1 (en) 2013-11-28
US9777732B2 true US9777732B2 (en) 2017-10-03
ID=38288115
US11/654,226 Active 2029-02-06 US7976271B2 (en) 2006-01-13 2007-01-16 Stabilizing drive for contactless rotary blood pump impeller
US11/654,216 Active 2027-04-24 US8512013B2 (en) 2006-01-13 2007-01-16 Hydrodynamic thrust bearings for rotary blood pumps
US11/654,217 Active 2028-09-08 US7997854B2 (en) 2006-01-13 2007-01-16 Shrouded thrust bearings
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US13/955,955 Active 2028-10-02 US9777732B2 (en) 2006-01-13 2013-07-31 Hydrodynamic thrust bearings for rotary blood pump
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2007-01-12 AU AU2007207782A patent/AU2007207782B2/en active Active
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2013-09-23 US US14/034,357 patent/US8932006B2/en active Active
2014-02-26 JP JP2014035942A patent/JP6067606B2/en active Active
2014-12-11 US US14/567,194 patent/US9242032B2/en active Active
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