Patent Grant
11964145
Patients with heart disease can have severely compromised ability to drive blood flow through the heart and vasculature, presenting for example substantial risks during corrective procedures such as balloon angioplasty and stent delivery. There is a need for ways to improve the volume or stability of cardiac outflow for these patients, especially during corrective procedures.
Intra-aortic balloon pumps (IABP) are commonly used to support circulatory function, such as treating heart failure patients. Use of IABPs is common for treatment of heart failure patients, such as supporting a patient during high-risk percutaneous coronary intervention (HRPCI), stabilizing patient blood flow after cardiogenic shock, treating a patient associated with acute myocardial infarction (AMI) or treating decompensated heart failure. Such circulatory support may be used alone or in with pharmacological treatment.
An IABP commonly works by being placed within the aorta and being inflated and deflated in counterpulsation fashion with the heart contractions, and one of the functions is to attempt to provide additive support to the circulatory system.
More recently, minimally-invasive rotary blood pumps have been developed that can be inserted into the body in connection with the cardiovascular system, such as pumping arterial blood from the left ventricle into the aorta to add to the native blood pumping ability of the left side of the patient's heart. Another known method is to pump venous blood from the right ventricle to the pulmonary artery to add to the native blood pumping ability of the right side of the patient's heart. An overall goal is to reduce the workload on the patient's heart muscle to stabilize the patient, such as during a medical procedure that may put additional stress on the heart, to stabilize the patient prior to heart transplant, or for continuing support of the patient.
The smallest rotary blood pumps currently available can be percutaneously inserted into the vasculature of a patient through an access sheath, thereby not requiring surgical intervention, or through a vascular access graft. A description of this type of device is a percutaneously-inserted ventricular support device.
There is a need to provide additional improvements to the field of ventricular support devices and similar blood pumps for treating compromised cardiac blood flow.
One aspect of the disclosure is a catheter blood pump, comprising an expandable pump portion extending distally from an elongate shaft, the pump portion including an expandable impeller housing including an expandable blood conduit that defines a blood lumen between an inflow and an outflow, one or more expandable impellers, each of which are disposed at least partially within the blood lumen, a sensor wire secured to the expandable impeller housing and extending from a proximal end of the expandable impeller housing to a distal end of the expandable impeller housing, and a sensor coupled to the sensor wire, the sensor disposed distal to a distal end of the expandable blood conduit.
In this aspect, the sensor wire may be secured to the expandable impeller housing such that it is disposed radially outside of the expandable blood conduit.
In this aspect, a sensor wire may be fixed relative to the expandable impeller housing such that it does not float within a sensor wire lumen.
In this aspect, the sensor wire may be disposed within a sensor wire lumen, the sensor wire having a size relative to the sensor wire lumen such that it floats in the sensor wire lumen. A sensor wire lumen may be defined by an inner surface of an elongate hollow shaft, the elongate hollow shaft may be secured to the expandable impeller housing. The elongate hollow shaft has a circular cross sectional configuration. The catheter blood pump may further comprise an overlay disposed about the elongate hollow shaft, the overlay positioned to secure the elongate hollow shaft to the expandable impeller housing. An overlay may comprise one or more types of material that are different than a material of an elongate hollow shaft. An overlay material may have at least one property that is different than a component of the expandable impeller housing that is radially within and adjacent to the elongate hollow shaft. A radially inner component may be stiffer, or less stiff, than an overlay. A radially inner component may comprise a membrane of the expandable impeller housing.
In this aspect, a sensor wire lumen may be defined by one of more polymeric materials.
In this aspect, a sensor wire lumen may have a radially outer surface defined by an overlay.
In this aspect, a sensor wire lumen may have a radially inner surface that is defined by an overlay, or by a component of the expandable impeller housing, such as a membrane.
In this aspect, a sensor wire lumen may be at least partially defined by a protrusion that protrudes radially outward from a generally circular cross sectional profile of the expandable impeller housing.
In this aspect, the sensor wire may extend in a helical configuration about at least a portion of the expandable impeller housing, optionally along an entire length of the expandable impeller housing.
In this aspect, the sensor wire may extend in a linear configuration along at least a portion of the expandable impeller housing, optionally along an entire length of the expandable impeller housing.
In this aspect, the sensor wire may extend in a helical configuration about a portion of the expandable impeller housing and in a linear configuration along at least a portion of the expandable impeller housing.
In this aspect, the sensor wire, may extend proximally from the expandable impeller housing and may be in communication with a proximal region of the blood pump that is positioned to remain outside of a patient when the impeller is operated. In this aspect, the sensor wire may be a fiber optic.
In this aspect, the sensor may be secured to an expandable distal strut at a pump inflow, the distal strut extending distally relative to a distal end of the expandable blood conduit.
In this aspect, the sensor may be secured to a radially outer surface of the expandable distal strut.
In this aspect, the sensor wire may also be secured to the distal strut proximal to the sensor. The sensor wire may be linearly aligned with a distal strut.
In this aspect, a sensor wire lumen may be secured to a distal strut proximal to the sensor, the sensor wire disposed within the sensor wire lumen.
In this aspect, the sensor wire may be secured to a proximal expandable strut, the proximal strut extending proximally from a proximal end of the blood conduit. The sensor wire may follow the configuration of the proximal strut.
This aspect may further comprise a sensor wire lumen in which the sensor wire is disposed, wherein the sensor wire lumen may be secured to a proximal expandable strut, and optionally wherein the sensor wire lumen follows the configuration of the proximal strut.
In this aspect, the expandable impeller housing may include one or more scaffold sections.
In this aspect, the expandable impeller housing may be stiffer in proximal and distal impeller sections than in a central section in between the distal and proximal impeller sections. The blood pump may further include a distal impeller within the distal impeller section and a proximal impeller in the proximal impeller section.
In this aspect, the sensor may be secured such that a pressure sensitive area is optionally between 1 and 89 degrees relative to a longitudinal axis, such as from 5-85 degrees, such as from 10-80 degrees.
In this aspect, the sensor wire may be secured to the expandable impeller housing but is moveable to some extent relative thereto, even if the sensor wire is fixed relative to the expandable impeller housing.
In this aspect, a sensor wire lumen may be in fluid communication with an inflation fluid source such that the sensor wire lumen is inflatable, and wherein the inflatable sensor wire lumen may have a closed distal end.
One aspect of this disclosure is a method of manufacturing a pump portion of an intravascular blood pump, comprising: creating a tubular substrate layer, the tubular substrate layer directly or indirectly defining at least a portion of a blood lumen of the pump portion; positioning an elongate hollow shaft on and extending along at least a portion of the tubular substrate layer; and depositing an overlay on the elongate shaft, optionally along substantially its entire length.
In this aspect, creating a tubular substrate layer may comprise depositing a softened polymeric material on a mandrel and allowing it to cool.
In this aspect, positioning an elongate hollow shaft on and extending along at least a portion of the tubular substrate layer comprises positioning the elongate hollow shaft such that is has one or more linear sections, optionally wherein it also has one or more helical sections.
In this aspect, depositing an overlay may comprise depositing a softened thermoplastic material on the elongate hollow shaft.
This aspect may further include positioning a sensor wire radially outside of the substrate, optionally radially within an overlay.
This aspect may include removing an elongate hollow shaft after an overlay has been deposited to thereby create a sensor wire lumen.
This aspect may further include removing a elongate hollow shaft prior to positioning a sensor wire radially within an overlay.
In this aspect, positioning the sensor wire may comprise positioning the sensor wire within an elongate hollow shaft.
This aspect may further include securing a sensor to the pump portion, the sensor coupled to the sensor wire. Securing a sensor may comprise securing the sensor to a strut, such as one or both of a proximal strut or a distal strut that extends axially from an end of a blood conduit.
This aspect may further comprise securing a sensor wire lumen to one or both of a proximal strut or a distal strut, the struts extending axially from a blood conduit.
This aspect may further comprise securing a second sensor to the blood pump, the second sensor disposed at or near an outflow of the pump portion.
This aspect may further include securing the tubular substrate layer to one or more of any of the expandable scaffolds or expandable members herein, any of which may provide radial support to a blood conduit.
One aspect of this disclosure is a catheter blood pump, comprising: an expandable pump portion extending distally from an elongate shaft, the pump portion including an expandable impeller housing including an expandable blood conduit that defines a blood lumen between an inflow and an outflow, and an inflatable in fluid communication with a fluid pathway extending proximally from the expandable impeller housing, the inflatable positioned and configured to provide radial support to the blood conduit when the inflatable is inflated; and one or more expandable impellers, each of which are disposed at least partially within the blood lumen adapted to move blood through the blood conduit.
This aspect may further include a fluid source proximally spaced from the expandable housing such that the fluid source remains outside of the body when the expandable housing is at the target location, the fluid source in fluid communication with the fluid pathway. A fluid source herein may be adapted to deliver fluid therefrom one or both of manually or automatically.
In this aspect the blood conduit may be adapted and configured such that inflation of the inflatable at least partially expands the blood conduit.
In this aspect, the inflatable may be configured and positioned relative to the blood conduit such that, when inflated, the inflatable provides more radial support to the blood conduit at the location of the one or more impellers than at a region of the blood conduit adjacent to the one or more impellers.
In this aspect, the expandable impeller housing may comprise more than one inflatable, and wherein the more than one inflatable may be configured and positioned relative to the blood conduit such that, when inflated, the more than one inflatable provide more radial support to the blood conduit at the location of the one or more impellers than at a region of the blood conduit adjacent to the one or more impellers. An adjacent region may be a central region of the expandable impeller housing, and is optionally between impeller regions.
In this aspect, an inflatable may comprise an annular configuration in at least a section of the inflatable. An inflatable may have more than one annular sections axially spaced apart.
One aspect of the disclosure is a method of deploying a pump portion of a catheter blood pump within a body of a subject, comprising: exposing an expandable impeller housing from within a delivery device, the expandable impeller housing including an expandable blood conduit and an inflatable disposed along at least a portion of the expandable blood conduit; exposing an impeller from within the delivery device so that the impeller is at least partially within the blood conduit, optionally causing the impeller to at least partially expand; delivering fluid from a fluid source that is disposed outside of the body of the subject, along an inflation pathway and into the inflatable; inflating the inflatable; and radially supporting the blood conduit with the inflated inflatable.
The present disclosure is related to medical devices, systems, and methods of use and manufacture. Medical devices herein may include a pump portion (which may also be referred to herein as a working portion) adapted to be disposed within a physiologic vessel, wherein the pump portion includes one or more components configured to act upon fluid. For example, pump portions herein may include one or more rotating members that when rotated, facilitate the movement of a fluid such as blood through a blood lumen defined by an impeller housing.
Any of the disclosure herein relating to an aspect of a system, device, or method of use or manufacture may be incorporated with any other suitable disclosure herein. For example, a figure describing only one aspect of a device or method may be included with different embodiments even if that is not specifically stated in a description of one or both parts of the disclosure. It is thus understood that combinations of different portions of this disclosure are included herein unless specifically indicated otherwise.
Pump portion 1600 also includes expandable support member 1602, which in this embodiment has a proximal end 1620 that extends further proximally than a proximal end of proximal impeller 1606, and a distal end 1608 that extends further distally than a distal end 1614 of distal impeller 1616. Expandable member 1602 is disposed radially outside of the impellers along the axial length of the impellers. Expandable member 1602 can be constructed in a manner and made from materials similar to many types of expandable structures that are known in the medical arts to be able to be collapsed and expanded, examples of which are provided herein. Examples of suitable materials include, but are not limited to, polyurethane and polyurethane elastomers.
Pump portion 1600 also includes expandable blood conduit 1604, which is coupled to expandable member 1602, has a length L, and extends axially between the impellers. Blood conduits herein may simply be referred to as conduits. Conduit 1604 creates and provides a blood lumen between the two impellers. When in use, blood moves through the lumen defined by conduit 1604. The conduits herein may be non-permeable, or they may be semi-permeable, or even porous as long as they can still define a lumen. The conduits herein are also flexible, unless it is otherwise indicated. The conduits herein extend completely around (i.e., 360 degrees) at least a portion of the pump portion. In pump portion 1600, conduit extends completely around expandable member 1602, but does not extend all the way to the proximal end 1602 or distal end 1608 of expandable member 1602. The structure of the expandable member creates at least one inlet aperture to allow for inflow “I,” and at least one outflow aperture to allow for outflow “0.” Conduit 1604 improves impeller pumping dynamics, compared to a similar pump portion 1600 without the conduit.
Expandable support member 1602 may have a variety of constructions, and made from a variety of materials. For example, expandable member 1602 may be formed similar to expandable stents or stent-like devices, or any other example provided herein. For example, without limitation, expandable member 1602 could have an open-braided construction, such as a 24-end braid, although more or fewer braid wires could be used. Exemplary materials for the expandable member include nitinol, cobalt alloys, and polymers, although other materials could be used. Expandable member 1602 has an expanded configuration, as shown, in which the outer dimension (measured orthogonally relative a longitudinal axis of the working portion) of the expandable member is greater in at least a region where it is disposed radially outside of the impellers than in a central region 1622 of the expandable member that extends axially between the impeller. Drive cable 1612 is co-axial with the longitudinal axis in this embodiment. In use, the central region can be placed across a valve, such as an aortic valve. In some embodiments, expandable member 1602 is adapted and constructed to expand to an outermost dimension of 12-24 F (4.0-8.0 mm) where the impellers are axially within the expandable member, and to an outermost dimension of 10-20 F (3.3-6.7 mm) in central region 1622 between the impellers. The smaller central region outer dimension can reduce forces acting on the valve, which can reduce or minimize damage to the valve. The larger dimensions of the expandable member in the regions of the impellers can help stabilize the working portion axially when in use. Expandable member 1602 has a general dumbbell configuration. Expandable member 1602 has an outer configuration that tapers as it transitions from the impeller regions to central region 1622, and again tapers at the distal and proximal ends of expandable member 1602.
Expandable member 1602 has a proximal end 1620 that is coupled to shaft 1610, and a distal end 1608 that is coupled to distal tip 1624. The impellers and drive cable 1612 rotate within the expandable member and conduit assembly. Drive cable 1612 is axially stabilized with respect to distal tip 1624, but is free to rotate with respect to tip 1624.
In some embodiments, expandable member 1602 can be collapsed by pulling tension from end-to-end on the expandable member. This may include linear motion (such as, for example without limitation, 5-20 mm of travel) to axially extend expandable member 1602 to a collapsed configuration with collapsed outer dimension(s). Expandable member 1602 can also be collapsed by pushing an outer shaft such as a sheath over the expandable member/conduit assembly, causing the expandable member and conduit to collapse towards their collapsed delivery configuration.
Impellers 1606 and 1616 are also adapted and constructed such that one or more blades will stretch or radially compress to a reduced outermost dimension (measured orthogonally to the longitudinal axis of the working portion). For example without limitation, any of the impellers herein can include one or more blades made from a plastic formulation with spring characteristics, such as any of the impellers described in U.S. Pat. No. 7,393,181, the disclosure of which is incorporated by reference herein for all purposes and can be incorporated into embodiments herein unless this disclosure indicates to the contrary. Alternatively, for example, one or more collapsible impellers can comprise a superelastic wire frame, with polymer or other material that acts as a webbing across the wire frame, such as those described in U.S. Pat. No. 6,533,716, the disclosure of which is incorporated by reference herein for all purposes.
The inflow and/or outflow configurations of pump portion 1600 can be mostly axial in nature.
Exemplary sheathing and unsheathing techniques and concepts to collapse and expand medical devices are known, such as, for example, those described and shown in U.S. Pat. No. 7,841,976 or 8,052,749, the disclosures of which are incorporated by reference herein.
First and second expandable members 1108 and 1110 generally each include a plurality of elongate segments disposed relative to one another to define a plurality of apertures 1130, only one of which is labeled in the second expandable member 1110. The expandable members can have a wide variety of configurations and can be constructed in a wide variety of ways, such as any of the configurations or constructions in, for example without limitation, U.S. Pat. No. 7,841,976, or the tube in U.S. Pat. No. 6,533,716, which is described as a self-expanding metal endoprosthetic material. For example, without limitation, one or both of the expandable members can have a braided construction or can be at least partially formed by laser cutting a tubular element.
Pump portion 1104 also includes expandable blood conduit 1112 that is coupled to first expandable support member 1108 and to second expandable support member 1110, and extends axially in between first expandable member 1108 and second expandable member 1110 in the deployed configuration. A central region 1113 of conduit 1112 spans an axial distance 1132 where the pump portion is void of first and second expandable members 1108 and 1110. Central region 1113 can be considered to be axially in between the expandable members. Distal end 1126 of conduit 1112 does not extend as far distally as a distal end 1125 of second expandable member 1110, and proximal end of conduit 1128 does not extend as far proximally as proximal end 1121 of first expandable member 1108.
When the disclosure herein refers to a conduit being coupled to an expandable member, the term coupled in this context does not require that the conduit be directly attached to the expandable member so that conduit physically contacts the expandable member. Even if not directly attached, however, the term coupled in this context refers to the conduit and the expandable member being joined together such that as the expandable member expands or collapses, the conduit also begins to transition to a different configuration and/or size. Coupled in this context therefore refers to conduits that will move when the expandable member to which it is coupled transitions between expanded and collapsed configurations. In some descriptions, conduits may be described as including one or more expandable support members.
Any of the conduits herein may be deformable to some extent, allowing them to be collapsed for delivery to a target location. For example, conduit 1112 includes elongate member 1120 that may be made of one or more materials that allow the central region 1113 of conduit to deform to some extent radially inward (towards LA) in response to, for example and when in use, forces from valve tissue (e.g., leaflets) or a replacement valve as working portion 1104 is deployed towards the configuration shown in
Any of the conduits herein can have a thickness of, for example, 0.5-20 thousandths of an inch (thou), such as 1-15 thou, or 1.5 to 15 thou, 1.5 to 10 thou, or 2 to 10 thou.
Any of the conduits herein, or at least a portion of the conduit, can be impermeable to blood. In
Any of the conduits herein that are secured to one or more expandable members can be, unless indicated to the contrary, secured so that the conduit is disposed radially outside of one or more expandable members, radially inside of one or more expandable members, or both, and the expandable member can be impregnated with the conduit material.
In some embodiments that include more than one expandable support member, proximal and distal expandable members provide radial support and maintain the conduit in an open configuration to create the blood lumen, while each also creates a working environment for an impeller, described below. Each of the expandable members, when in the deployed configuration, is maintained in a spaced relationship relative to a respective impeller, which allows the impeller to rotate within the expandable member without contacting the expandable member. Pump portion 1104 includes first impeller 1116 and second impeller 1118, with first impeller 1116 disposed radially within first expandable member 1108 and second impeller 1118 disposed radially within second expandable member 1110. In this embodiment, the two impellers even though they are distinct and separate impellers, are in operable communication with a common drive mechanism (e.g., drive cable 1117), such that when the drive mechanism is activated the two impellers rotate together. In this deployed configuration, impellers 1116 and 1118 are axially spaced apart along longitudinal axis LA, just as are the expandable members 1108 and 1110 are axially spaced apart.
Impellers 1116 and 1118 are also axially within the ends of expandable members 1108 and 1110, respectively (in addition to being radially within expandable members 1108 and 1110). The impellers herein can be considered to be axially within an expandable member even if the expandable member includes struts extending from a central region of the expandable member towards a longitudinal axis of the working portion (e.g., tapering struts in a side view). In
In
In the exemplary embodiment shown in
The expandable members and the conduit are not in rotational operable communication with the impellers and the drive mechanism. In this embodiment, proximal end 1121 of proximal expandable member 1108 is coupled to shaft 1119, which may be a shaft of elongate portion 1106 (e.g., an outer catheter shaft). Distal end 1122 of proximal expandable member 1108 is coupled to central tubular member 1133, through which drive mechanism 1117 extends. Central tubular member 1133 extends distally from proximal expandable member 1108 within conduit 1112 and is also coupled to proximal end 1124 of distal expandable member 1110. Drive mechanism 1117 thus rotates within and relative to central tubular member 1133. Central tubular member 1133 extends axially from proximal expandable member 1108 to distal expandable member 1110. Distal end 1125 of distal expandable member 1110 is coupled to distal tip 1114, as shown. Drive mechanism 1117 is adapted to rotate relative to tip 1114, but is axially fixed relative to tip 1114.
Working portion 1104 is adapted and configured to be collapsed to a smaller profile than its deployed configuration (which is shown in
The working portions herein can be collapsed to a collapsed delivery configuration using conventional techniques, such as with an outer sheath that is movable relative to the working portion (e.g., by axially moving one or both of the sheath and working portion). For example without limitation, any of the systems, devices, or methods shown in the following references may be used to facilitate the collapse of a working portions herein: U.S. Pat. No. 7,841,976 or 8,052,749, the disclosures of which are incorporated by reference herein for all purposes.
Working portion 340 includes proximal impeller 341 and distal impeller 342, which are coupled to and in operational communication with a drive cable, which defines therein a lumen. The lumen can be sized to accommodate a guidewire, which can be used for delivery of the working portion to the desired location. The drive cable, in this embodiment, includes first section 362 (e.g., wound material), second section 348 (e.g., tubular member) to which proximal impeller 341 is coupled, third section 360 (e.g., wound material), and fourth section 365 (e.g., tubular material) to which distal impeller 342 is coupled. The drive cable sections all have the same inner diameter, so that lumen has a constant inner diameter. The drive cable sections can be secured to each other using known attachment techniques. A distal end of fourth section 365 extends to a distal region of the working portion, allowing the working portion to be, for example, advanced over a guidewire for positioning the working portion. In this embodiment the second and fourth sections can be stiffer than first and third sections. For example, second and fourth can be tubular and first and third sections can be wound material to impart less stiffness.
Working portion 340 includes proximal expandable member 343 and distal expandable member 344, each of which extends radially outside of one of the impellers. The expandable members have distal and proximal ends that also extend axially beyond distal and proximal ends of the impellers, which can be seen in
In alternative embodiments, at least a portion of any of the impellers herein may extend outside of the fluid lumen. For example, only a portion of an impeller may extend beyond an end of the fluid lumen in either the proximal or distal direction. In some embodiments, a portion of an impeller that extends outside of the fluid lumen is a proximal portion of the impeller, and includes a proximal end (e.g., see the proximal impeller in
A second impeller at another end of the fluid lumen may not, however, extend beyond the fluid lumen. For example, an illustrative alternative design can include a proximal impeller that extends proximally beyond a proximal end of the fluid lumen (like the proximal impeller in
While specific exemplary locations may be shown herein, the fluid pumps may be able to be used in a variety of locations within a body. Some exemplary locations for placement include placement in the vicinity of an aortic valve or pulmonary valve, such as spanning the valve and positioned on one or both sides of the valve, and in the case of an aortic valve, optionally including a portion positioned in the ascending aorta. In some other embodiments, for example, the pumps may be, in use, positioned further downstream, such as being disposed in a descending aorta.
In this embodiment, second expandable member 1110 has been expanded and positioned in a deployed configuration such that distal end 1125 is in the left ventricle “LV,” and distal to aortic valve leaflets “VL,” as well as distal to the annulus. Proximal end 1124 has also been positioned distal to leaflets VL, but in some methods proximal end 1124 may extend slightly axially within the leaflets VL. This embodiment is an example of a method in which at least half of the second expandable member 1110 is within the left ventricle, as measured along its length (measured along the longitudinal axis). And as shown, this is also an example of a method in which the entire second expandable member 1110 is within the left ventricle. This is also an example of a method in which at least half of second impeller 1118 is positioned within the left ventricle, and also an embodiment in which the entire second impeller 1118 is positioned within the left ventricle.
Continued retraction of an outer shaft or sheath (and/or distal movement of working end 1104 relative to an outer sheath or shaft) continues to release conduit 1112, until central region 1113 is released and deployed. The expansion of expandable members 1108 and 1110 causes conduit 1112 to assume a more open configuration, as shown in
Continued retraction of an outer shaft or sheath (and/or distal movement of working end 1104 relative to an outer sheath or shaft) deploys first expandable member 1108. In this embodiment, first expandable member 1108 has been expanded and positioned (as shown) in a deployed configuration such that proximal end 1121 is in the ascending aorta AA, and proximal to leaflets “VL.” Distal end 1122 has also been positioned proximal to leaflets VL, but in some methods distal end 1122 may extend slightly axially within the leaflets VL. This embodiment is an example of a method in which at least half of first expandable member 1110 is within the ascending aorta, as measured along its length (measured along the longitudinal axis). And as shown, this is also an example of a method in which the entire first expandable member 1110 is within the AA. This is also an example of a method in which at least half of first impeller 1116 is positioned within the AA, and also an embodiment in which the entire first impeller 1116 is positioned within the AA.
At any time during or after deployment of working portion 1104, the position of the working portion can be assessed in any way, such as under fluoroscopy. The position of the working portion can be adjusted at any time during or after deployment. For example, after second expandable member 1110 is released but before first expandable member 1108 is released, working portion 1104 can be moved axially (distally or proximally) to reposition the working portion. Additionally, for example, the working portion can be repositioned after the entire working portion has been released from a sheath to a desired final position.
It is understood that the positions of the components (relative to the anatomy) shown in
The one or more expandable members herein can be configured to be, and can be expanded in a variety of ways, such as via self-expansion, mechanical actuation (e.g., one or more axially directed forces on the expandable member, expanded with a separate balloon positioned radially within the expandable member and inflated to push radially outward on the expandable member), or a combination thereof.
Expansion as used herein refers generally to reconfiguration to a larger profile with a larger radially outermost dimension (relative to the longitudinal axis), regardless of the specific manner in which the one or more components are expanded. For example, a stent that self-expands and/or is subject to a radially outward force can “expand” as that term is used herein. A device that unfurls or unrolls can also assume a larger profile, and can be considered to expand as that term is used herein.
The impellers can similarly be adapted and configured to be, and can be expanded in a variety of ways depending on their construction. For examples, one or more impellers can, upon release from a sheath, automatically revert to or towards a different larger profile configuration due to the material(s) and/or construction of the impeller design (see, for example, U.S. Pat. No. 6,533,716, or U.S. Pat. No. 7,393,181, both of which are incorporated by reference herein for all purposes). Retraction of an outer restraint can thus, in some embodiments, allow both the expandable member and the impeller to revert naturally to a larger profile, deployed configuration without any further actuation.
As shown in the example in
Additionally, forces on a central region of a single expandable member from the leaflets might translate axially to other regions of the expandable member, perhaps causing undesired deformation of the expandable member at the locations of the one or more impellers. This may cause the outer expandable member to contact the impeller, undesirably interfering with the rotation of the impeller. Designs that include separate expandable members around each impeller, particularly where each expandable member and each impeller are supported at both ends (i.e., distal and proximal), result in a high level of precision in locating the impeller relative to the expandable member. Two separate expandable members may be able to more reliably retain their deployed configurations compared with a single expandable member.
As described herein above, it may be desirable to be able to reconfigure the working portion so that it can be delivered within a 9 F sheath and still obtain high enough flow rates when in use, which is not possible with some products currently in development and/or testing. For example, some products are too large to be able to reconfigured to a small enough delivery profile, while some smaller designs may not be able to achieve the desired high flow rates. An exemplary advantage of the examples in
The embodiment herein can thus achieve a smaller delivery profile while maintaining sufficiently high flow rates, while creating a more deformable and flexible central region of the working portion, the exemplary benefits of which are described above (e.g., interfacing with delicate valve leaflets).
There are alternative ways to construct the working portion to cause rotation of the expandable member upon collapse by elongation (and thus cause wrapping and collapse of the impeller blades). Any expandable member can be constructed with this feature, even in dual-impeller designs. For example, with an expandable member that includes a plurality of “cells,” as that term is commonly known (e.g., a laser cut elongate member), the expandable member may have a plurality of particular cells that together define a particular configuration such as a helical configuration, wherein the cells that define the configuration have different physical characteristics than other cells in the expandable member. In some embodiments the expandable member can have a braided construction, and the twist region may constitute the entire group of wires, or a significant portion (e.g., more than half), of the braided wires. Such a twisted braid construction may be accomplished, for example, during the braiding process, such as by twisting the mandrel that the wires are braided onto as the mandrel is pulled along, especially along the length of the largest-diameter portion of the braided structure. The construction could also be accomplished during a second operation of the construction process, such as mechanically twisting a braided structure prior to heat-setting the wound profile over a shaped mandrel.
Any of the conduits herein act to, are configured to, and are made of material(s) that create a fluid lumen therein between a first end (e.g., distal end) and a second end (e.g., proximal end). Fluid flows into the inflow region, through the fluid lumen, and then out of an outflow region. Flow into the inflow region may be labeled herein as “I,” and flow out at the outflow region may be labeled “0.” Any of the conduits herein can be impermeable. Any of the conduits herein can alternatively be semipermeable. Any of the conduits herein may also be porous, but will still define a fluid lumen therethrough. In some embodiments the conduit is a membrane, or other relatively thin layered member. Any of the conduits herein, unless indicated to the contrary, can be secured to an expandable member such that the conduit, where is it secured, can be radially inside and/or outside of the expandable member. For example, a conduit can extend radially within the expandable member so that inner surface of the conduit is radially within the expandable member where it is secured to the expandable member.
Any of the expandable member(s) herein can be constructed of a variety of materials and in a variety of ways. For example, the expandable member may have a braided construction, or it can be formed by laser machining. The material can be deformable, such as nitinol. The expandable member can be self-expanding or can be adapted to be at least partially actively expanded.
In some embodiments, the expandable member is adapted to self-expand when released from within a containing tubular member such as a delivery catheter, a guide catheter or an access sheath. In some alternative embodiments, the expandable member is adapted to expand by active expansion, such as action of a pull-rod that moves at least one of the distal end and the proximal end of the expandable member toward each other. In alternative embodiments, the deployed configuration can be influenced by the configuration of one or more expandable structures. In some embodiments, the one or more expandable members can be deployed, at least in part, through the influence of blood flowing through the conduit. Any combination of the above mechanisms of expansion may be used.
The blood pumps and fluid movement devices, system and methods herein can be used and positioned in a variety of locations within a body. While specific examples may be provided herein, it is understood that that the working portions can be positioned in different regions of a body than those specifically described herein.
In any of the embodiments herein in which the medical device includes a plurality of impellers, the device can be adapted such that the impellers rotate at different speeds.
In some embodiments, a common drive cable or shaft can drive the rotation of two (or more) impellers, but the blade pitch of the two impellers (angle of rotational curvature) can be different, with the distal or proximal impeller having a steeper or more gradual angle than the other impeller. This can produce a similar effect to having a gearset.
In any of the embodiments herein, the pump portion can have a compliant or semi-compliant (referred to generally together as “compliant”) exterior structure. In various embodiments, the compliant portion is pliable. In various embodiments, the compliant portion deforms only partially under pressure. For example, the central portion of the pump may be formed of a compliant exterior structure such that it deforms in response to forces of the valve. In this manner the exterior forces of the pump on the valve leaflets are reduced. This can help prevent damage to the valve at the location where it spans the valve.
The embodiment in
In a method of use, a bend formed in a housing can be positioned to span a valve, such as the aortic valve shown in
A bend such as bend 150 or 151 can be incorporated into any of the embodiments or designs herein. The bend may be a preformed angle or may be adjustable in situ.
In any of the embodiments herein, unless indicated to the contrary, the outer housing can have a substantially uniform diameter along its length.
In
One aspect of the disclosure is an intravascular blood pump that includes a distal impeller axially spaced from a proximal impeller. In one embodiment, the distal and proximal impellers are separated from each other. For example, the distal and proximal impellers may be connected solely by their individual attachment to a common driveshaft. This is distinct from an impeller having multiple blade rows. A distal impeller as that phrase is used herein does not necessarily mean a distal-most impeller of the pump, but can refer generally to an impeller that is positioned further distally than a proximal impeller, even if there is an additional impeller than is disposed further distally than the distal impeller. Similarly, a proximal impeller as that phrase is used herein does not necessarily mean a proximal-most impeller of the pump, but can refer generally to an impeller that is positioned further proximally than a proximal impeller, even if there is an additional impeller than is disposed further proximally than the proximal impeller. Axial spacing (or some derivative thereof) refers to spacing along the length of a pump portion, such as along a longitudinal axis of the pump portion, even if there is a bend in the pump portion. In various embodiments, each of the proximal and distal impellers are positioned within respective housings and configured to maintain a precise, consistent tip gap, and the span between the impellers has a relatively more flexible (or completely flexible) fluid lumen. For example, each of the impellers may be positioned within a respective housing having relatively rigid outer wall to resist radial collapse. The sections between the impellers may be relatively rigid, in some embodiments the section is held open primarily by the fluid pressure within.
Although not required for the embodiments therein, there may be advantages to having a minimum axial spacing between a proximal impeller and a distal impeller. For example, a pump portion may be delivered to a target location through parts of the anatomy that have relatively tight bends, such as, for example, an aorta, and down into the aortic valve. For example, a pump portion may be delivered through a femoral artery access and to an aortic valve. It can be advantageous to have a system that is easier to bend so that it is easier to deliver the system through the bend(s) in the anatomy. Some designs where multiple impellers are quite close to each other may make the system, along the length that spans the multiple impellers, relatively stiff along that entire length that spans the multiple impellers. Spacing the impellers apart axially, and optionally providing a relatively flexible region in between the impellers, can create a part of the system that is more flexible, is easier to bend, and can be advanced through the bends more easily and more safely. An additional exemplary advantage is that the axial spacing can allow for a relatively more compliant region between the impellers, which can be positioned at, for example, the location of a valve (e.g., an aortic valve). Furthermore, there are other potential advantages and functional differences between the various embodiments herein and typical multistage pumps. A typical multistage pump includes rows of blades (sometimes referred to as impellers) in close functional spacing such that the rows of blades act together as a synchronized stage. One will appreciate that the flow may separate as it passes through the distal impeller. In various embodiments as described herein, distal and proximal impellers can be spaced sufficiently apart such that the flow separation from the distal impeller is substantially reduced (i.e., increased flow reattachment) and the localized turbulent flow is dissipated before the flow enters the proximal impeller.
In any of the embodiments or in any part of the description herein that include a distal impeller and a proximal impeller, the axial spacing between a distal end of the proximal impeller and a proximal end of the distal impeller can be from 1.5 cm to 25 cm (inclusive) along a longitudinal axis of the pump portion, or along a longitudinal axis of a housing portion that includes a fluid lumen. The distance may be measured when the pump portion, including any impellers, is in an expanded configuration. This exemplary range can provide the exemplary flexibility benefits described herein as the pump portion is delivered through curved portions of the anatomy, such as, for example, an aortic valve via an aorta.
While some embodiments include a proximal impeller distal end that is axially spaced 1.5 cm to 25 cm from a distal impeller proximal end along an axis, the disclosure herein also includes any axial spacings that are subranges within that general range of 1.5 cm to 25 cm. That is, the disclosure includes all ranges that have any lower limit from 1.5 and above in that range, and all subranges that have any upper limit from 25 cm and below. The examples below provide exemplary subranges. In some embodiments, a proximal impeller distal end is axially spaced 1.5 cm to 20 cm from a distal impeller proximal end along an axis, 1.5 cm to 15 cm, 1.5 cm to 10 cm, 1.5 cm to 7.5 cm, 1.5 cm to 6 cm, 1.5 cm to 4.5 cm, 1.5 cm to 3 cm. In some embodiments the axial spacing is 2 cm to 20 cm, 2 cm to 15 cm, 2 cm to 12 cm, 2 cm to 10 cm, 2 cm to 7.5 cm, 2 cm to 6 cm, 2 cm to 4.5 cm, 2 cm to 3 cm. In some embodiments the axial spacing is 2.5 cm to 15 cm, 2.5 cm to 12.5 cm, 2.5 cm to 10 cm, 2.5 cm to 7.5 cm, or 2.5 cm to 5 cm (e.g., 3 cm). In some embodiments the axial spacing is 3 cm to 20 cm, 3 cm to 15 cm, 3 cm to 10 cm, 3 cm to 7.5 cm, 3 cm to 6 cm, or 3 cm to 4.5 cm. In some embodiments the axial spacing is 4 cm to 20 cm, 4 cm to 15 cm, 4 cm to 10 cm, 4 cm to 7.5 cm, 4 cm to 6 cm, or 4 cm to 4.5 cm. In some embodiments the axial spacing is 5 cm to 20 cm, 5 cm to 15 cm, 5 cm to 10 cm, 5 cm to 7.5 cm, or 5 cm to 6 cm. In some embodiments the axial spacing is 6 cm to 20 cm, 6 cm to 15 cm, 6 cm to 10 cm, or 6 cm to 7.5 cm. In some embodiments the axial spacing is 7 cm to 20 cm, 7 cm to 15 cm, or 7 cm to 10 cm. In some embodiments the axial spacing is 8 cm to 20 cm, 8 cm to 15 cm, or 8 cm to 10 cm. In some embodiments the axial spacing is 9 cm to 20 cm, 9 cm to 15 cm, or 9 cm to 10 cm. In various embodiments, the fluid lumen between the impellers is relatively unsupported.
In any of the embodiments herein the one or more impellers may have a length, as measured axially between an impeller distal end and an impeller proximal end (shown as “LSD” and “LSP”, respectively, in
In any of the embodiments herein the fluid lumen can have a length from a distal end to a proximal end, shown as length Lp in
In any of the embodiments herein the housing can have a deployed diameter, at least the location of an impeller (and optionally at a location between impellers), shown as dimension Dp in
In any of the embodiments herein an impeller can have a deployed diameter, shown as dimension Di in
In any of the embodiments herein, a tip gap exists between an impeller outer diameter and a fluid lumen inner diameter. In some embodiments the tip gap can be from 0.01 mm-1 mm, such as 0.05 mm to 0.8 mm, or such as 0.1 mm-0.5 mm.
In any of the embodiments herein that includes multiple impellers, the axial spacing between impellers (along the length of the pump portion, even if there is a bend in the pump portion) can be from 2 mm to 100 mm, or any combination of upper and lower limits inclusive of 5 and 100 mm (e.g., from 10 mm-80 mm, from 15 mm-70 mm, from 20 mm-50 mm, 2 mm-45 mm, etc.).
Blood pumps, such as any of the intravascular pumps herein, may benefit from having one or more fluid paths through which fluid can flow through the device. For example without limitation, blood pumps may benefit from having one or more fluid paths through which fluid can flow to perform any of these exemplary functions: cooling rotating components (e.g., a drive cable) to prevent their overheating; flushing small particulates that may break off rotating components (e.g., a drive cable) to prevent the rotating parts from being damaged by the small particulates; lubricating rotating components (e.g., one or more bearings), and preventing blood ingress into the pump (e.g., near or at a distal end of the pump). Fluid delivery through the one or more flow paths may provide any number of these functions. For example, the disclosure in WO 2020/073047A1 is fully incorporated by reference for all purposes.
The following disclosure provides exemplary method steps that may be performed when using any of the blood pumps, or portions thereof, described herein. It is understood that not all of the steps need to be performed, but rather the steps are intended to be an illustrative procedure. It is also intended that, if suitable, in some instances the order of one or more steps may be different.
Before use, the blood pump can be prepared for use by priming the lumens (including any annular spaces) and pump assembly with sterile solution (e.g., heparinized saline) to remove any air bubbles from any fluid lines. The catheter, including any number of purge lines, may then be connected to a console. Alternatively, the catheter may be connected to a console and/or a separate pump that are used to prime the catheter to remove air bubbles.
After priming the catheter, access to the patient's vasculature can be obtained (e.g., without limitation, via femoral access) using an appropriately sized introducer sheath. Using standard valve crossing techniques, a diagnostic pigtail catheter may then be advanced over a, for example, 0.035″ guide wire until the pigtail catheter is positioned securely in the target location (e.g., left ventricle). The guidewire can then be removed and a second wire 320 (e.g., a 0.018″ wire) can be inserted through the pigtail catheter. The pigtail catheter can then be removed (see
Once proper placement is confirmed, the catheter sheath 322 (see
The second wire (e.g., an 0.018″ guidewire) may then be moved prior to operation of the pump assembly (see
Any number of purge lines may then be attached to the proximal portion of the blood pump that is disposed outside of the patient. For example, fluid inlet(s) lines and fluid outlet(s) lines may be attached to one or more fluid ports on the proximal portion of the blood pump. A purge process can then be initiated to move fluid into the blood pump through at least one fluid pathway. One or more Confirmation steps can be performed to confirm the purge is operating as intended before turning on the pump. The pump assembly can then be operated, causing rotation of the one or more impellers. Any one of flow rate(s), pressure(s), and motor operation can be monitored at any time.
Any text that might appear in any figures is understood to be illustrative but exemplary, and does not necessitate that any particular component needs to be included in the embodiment.
The disclosure also includes catheter blood pumps that include one or more sensors thereon or therein, their methods of manufacture, and use. For example only, any blood pumps herein may include one or more sensors configured to sense pressure. A sensor configured to sense blood pressure may be included on an intravascular blood pump for a variety of purposes, such as, for example without limitation, estimating flow or detecting the position of the blood pump. Additionally, for example, one or more sensors may be axially spaced apart (e.g., one near an inflow and one near an outflow) and used to determine a differential pressure across the pump portion.
In the embodiment in
The sensor wire housings herein may have a linear configuration along at least a portion of the expandable housing, such as at least 50% of a length of the expandable housing, 55%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, 95%, or 100% of a length of the expandable housing.
The sensor wire housings herein may have a helical configuration along a portion of its length, and may have linear or other configurations along other portions of its length. The sensor wire housings herein may have helical configurations in one or more discrete axially spaced helical regions, and optionally may have linear configurations in one or more discrete axially spaced linear regions. Sensor wire housings may have other non-linear and non-helical configurations as well.
The sensor wire housings herein generally help protect the one or more sensor wires (e.g., fiber optic). Sensors wires (e.g., fiber optics) may be quite fragile and susceptible to breaking, especially when the pump portion is navigated through curved vasculature and bends. Sensor wire housings herein can be sized relative to the sensor wire such that the sensor wire may float within the lumen, which may provide space for the wire to move slightly while the pump portion is navigated and/or in use, which may reduce the likelihood of sensor wire breakage.
In some embodiments, however, a sensor wire may be fixed relative to a impeller housing such that it is not floating with a space. When described as being fixed relative to an impeller housing, there may be some degree of slight movement provided between a sensor wire and impeller housing due to the flexibility of the materials, but fixed in this context refers generally to not freely floating within an open lumen.
Any of the sensor wire housings herein that house a sensor wire may also have a non-circular cross sectional shape, such as rectilinear (e.g., triangular, rectangular, square), or curvilinear (e.g., oval), or any other non-defined, irregular, shape. In this exemplary embodiment, the sensor wire housing that defines lumen 471 is secured to the expandable housing 470 at least partially by overlay 473, and in this embodiment overlay 473 is disposed about a radially outermost portion of the sensor wire housing and lumen 471. The overlay 473 at least partially serves to help secure the sensor wire housing relative to the expandable housing. In this exemplary embodiment it may be a combination of the expandable membrane material of the housing 470 as well as overlay 473 that together surround the sensor wire housing and help secure it relative to the expandable housing 470. The membrane of the expandable impeller housing 470 is disposed radially within sensor wire housing, and overlay 473 is disposed about the sensor wire housing and lumen 471, including about a radially outmost portion of the sensor wire housing as shown. In any of the embodiments herein, the expandable housing 470 membrane may not be in direct contact with the sensor wire housing; there may be one or more layers of overlay material in between the two.
Any of the overlays herein may be different than an expandable housing membrane in one or more ways. For example, possible differences herein in this context include, for example, one or more of chemical structure, durometer, stiffness, and thickness. For example, an overlay is considered different than a conduit membrane in this context if the overlay is the same material as a membrane, but has a different durometer. Additionally, for example, an overlay is considered different than a impeller housing membrane in this context if the overlay is the same material as a membrane, but has a different thickness than the membrane.
In any of the embodiments herein, an overlay may comprise a polymeric material, optionally a urethane, and optionally polycarbonate based. In any of the embodiments herein, a membrane that at least partially defines a blood flow lumen may comprise a polymeric material, optionally a urethane, and optionally polycarbonate based. In any of the embodiments herein, the membrane may have the same chemical structure as the overlay.
In
In this embodiment (and any embodiment herein), the sensor is secured such that a pressure sensitive area of the sensor is not orthogonal to a longitudinal axis of the expandable housing, and is optionally between 1 and 89 degrees relative to the longitudinal axis, such as from 5-85 degrees, such as from 10-80 degrees. The reference angle theta is shows in
In any of the embodiments herein, the sensor wire extends along the expandable housing and is in communication with a proximal region of the blood pump that is spaced to remain outside of a patient when the impeller is in use. Information sensed from the one or more sensors can be used for one or more of the following: estimating flow, and detecting the position of the blood pump. Additionally, one or more sensors may be axially spaced apart (e.g., one near an inflow and one near an outflow, not shown), and used to determine a differential pressure across the pump portion.
The disclosure herein also describes methods of manufacturing pump portions of intravascular blood pumps. The methods of manufacturing can include creating a sensor wire lumen in the pump portion. Exemplary methods are described in the context of
An elongate shaft 492 defining a lumen therein may then be positioned on top of the tubular substrate layer 491, optionally in a helical and/or linear configuration, optionally in one or more discrete helical sections and/or one or more linear sections, and maintained in that configuration using any of a wide variety of techniques, such as by applying an adhesive (e.g., tape) to end sections axially outside of the tubular substrate layer.
Material (e.g., 473, 467, 477, 483) may then be deposited on and around elongate shaft 492 such that it overlays the elongate shaft. Depending on the material, it may be allowed to harden as it cools. For example, the material may be a material that becomes soft when heated and hardens when cooled, such as a thermoplastic. The overlay material can be any of the exemplary materials described herein, and can have any of the exemplary properties described herein.
In any of the embodiments herein, the overlay may be deposited only in the region of the elongate shaft (e.g., 473, 467, 477) such that the overlay has the same configuration as the elongate shaft along the tubular substrate layer. One exemplary method to do this is masking the region where the overlay material is not to be deposited (e.g., masking all but a helical or linear region where the elongate shaft is located). In any of the embodiments herein, however, the overlay made be deposited over the entire tubular substrate (including the elongate shaft), essentially creating an additional tubular layer of material.
If the elongate shaft (e.g., tubular shaft) is to be left in place (e.g., as in
If the elongate shaft is to be removed during the manufacturing process (e.g.,
Any of the methods herein can include securing the sensor to one or more reinforcing elements of the pump portion, such as to a strut (e.g.,
Any of the methods herein can include securing a second sensor to the pump portion at or adjacent to the outflow portion. For example, a second sensor can be secured to a reinforcing element of the pump portion, such as a proximal strut, or to any portion of the elongate shaft (e.g., 455 in
The disclosure herein includes blood pumps that can include one more inflatable members, which may facilitate one or more functions. Inflatable members may also be referred to herein as inflatables. In some exemplary embodiments, an inflatable member may be inflated to at least partially assist in expanding an expandable impeller housing. In some exemplary embodiments, an inflatable member may be inflated to provide radial support along at least a portion of the expandable impeller housing, which may help maintain a tip gap between an impeller blade and a blood lumen conduit. In some embodiments, an inflatable may also function as a housing for a structural component (i.e., not fluid). In some examples an inflatable may house therein a part of a sensor system, such as a sensor wire (e.g., a sensor wire coupled to a sensor). Any of the inflatable members herein may be adapted to provide more than one of these functions, or other functions provided herein by an inflatable member. Any of the expandable impeller housings herein may include or incorporate any of the inflatable members described herein.
In some examples, an inflatable (e.g., inflatable 504) may be disposed at one or both ends of a blood conduit of an expandable impeller housing, as shown, and one or more inflatables may be disposed in between ends of the blood conduit. After inflation, the inflatable member may provide radial support to the expandable impeller housing, which may help maintain tip gap between one or more blades and the blood conduit wall, particular in an impeller region of the impeller housing. Once inflated, the stiffness of the inflatable member may increase, providing radial support to the expandable impeller housing. Once inflated, the inflatable member may help provide and/or maintain circularity to the expandable impeller housing at the location of the inflatable. An expandable impeller housing may have one or more inflatables along its length, such as from one to fifty. Any number of inflatable members 504 may be included along the length of the blood conduit as may be desirable to increase radial support at one or more particular locations. For example, the expandable housing may include inflatable members at one or both ends of one or more expandable support members surrounding an impeller, which are described elsewhere herein.
Inflatable members 504 are also examples of annular inflatable members.
If inflatable members are in fluid communication, they may also be considered to be a single inflatable, even if some embodiments herein describe them as separate inflatables. For example, all of the inflatables 532′, 532″, 532′″ and lumen 534 may be considered to a single inflatable if they are all in fluid communication.
As an alternative to
Any of the fluids herein may be a gas or a liquid, for example. For example, one inflatable member may be inflated with a gas, and a second inflatable member may be inflated with a fluid.
In some alternative embodiments, an inflatable member forms a part of a fluid conduit (e.g., a dual-layered region of the fluid conduit that is in fluid communication with a fluid source), but does not form the entirety of the fluid conduit. For example, an inflatable member may comprise a generally cylindrical configuration (in at least part of the inflatable member), and an impeller may be at least partially disposed within the cylindrical configuration. In other embodiments, an inflatable member has two generally cylindrical axially-spaced regions, each of which has an impeller at least partially disposed therein. In embodiments in which a blood pump includes at least two axially-spaced cylindrical inflatable regions (which may form part of a fluid conduit; whether part of the same inflatable member or different inflatable members), a central region of the pump portion may extend between the two cylindrical regions, and wherein the central region may include or may not include an inflatable member. For example, a central region in between the two cylindrical regions may include an inflatable member that is at least one of linear, curvilinear, or helical, and may be in fluid communication with one or both of the cylindrical inflatable regions. Alternatively, the central region may not include an inflatable member, although it may include a fluid lumen that is in fluid communication with the one or more inflatable members axially spaced from the central region.
In some embodiments, an inflatable member forms a part of the blood conduit (e.g., a dual-layered region of the fluid conduit that is in fluid communication with a fluid source), and in another region of the pump portion, the inflatable member is also partially disposed on an outer surface of the blood conduit. For example, in some embodiments the pump portion includes a cylindrical inflatable section (e.g., in which any of the impellers herein is at least partially disposed) that forms a portion of the blood conduit, and axially adjacent to the cylindrical inflatable section the pump portion includes a second region that includes a non-cylindrical inflatable member that is one or more of on the blood conduit, embedded within the blood conduit, or within the blood conduit.
In any of the embodiments here, any of the inflatable members (or at least portions thereof) may be sandwiched between two layers of material (e.g., an inner layer and an outer layer). For example, any of the inflatable members in
The disclosure herein also includes methods of deploying a blood pump that includes one or more inflatable members. The methods that follow can include any of the methods of deployment described herein. The pump portion can be advanced in a collapsed configuration within a fluid delivery device such as a sheath or other lumen. The method can include exposing an expandable impeller housing from within the delivery device, the expandable housing including a conduit and an inflatable member. The method can include exposing an impeller from within the delivery device so that the impeller is at least partially within the conduit, wherein the impeller may expand to at least some extent when exposed. The methods can also include delivering fluid from within a fluid source, along an inflation pathway, and into the inflatable member to inflate the inflatable member. In various embodiments, any of the methods herein can include collapsing the one or more inflatable members. In various embodiments, a vacuum is applied to remove fluid (or optionally gas in the case of a closed system) from the inflatable member. In any of the embodiments herein, the inflatable member can be inflated using a purge fluid from the console purge system. In these cases, the purge fluid pressure may be decreased to allow the inflatable member to collapse. In the case of certain expandable pumps as described herein, when the pump is collapsed by sheathing, the purge fluid can be pushed out of the inflatable member and into the waste line which allows the pump portion to collapse.
In various embodiments, the inflatable member may be inflated using a purge fluid and the inflatable member is configured as a lumen for the purge fluid. For example, the inflatable member may extend from a proximal end of the pump to a distal bearing to allow for purging of the distal bearing. In this manner, the inflatable member may perform several functions, e.g., housing the sensor wire, delivering purge fluid, and adding structural support to the shroud/blood conduit.
In any of the methods, inflating an inflatable member can at least help expand the conduit, if not be a significant part of the conduit expansion process. For example, expandable support members (scaffolds) may or may not be included in the pump portion. For any method herein, inflating the inflatable member may increase radial support (increase stiffness) at the location of the inflated member, which may help maintain circularity of the lumen and thereby help maintain tip gap between an impeller blade and the conduit wall.
Any of the methods herein may include inflating a second inflatable member, which may be inflated with a fluid from a second fluid source or from the first fluid source.
As used herein, an inflatable member refers to an inflatable component, even if portions of it have different configurations.
Any of the methods herein can include inflating a tubular member that houses therein a sensor component, such a a sensor wire (e.g., fiber optic).
Any of the inflatable members herein can be deflated using one or more techniques. For example, any of the inflatable members herein can be at least partially deflated by pulling a vacuum to at least partially remove fluid from within the inflatable member. In addition to or alternatively, any of the inflatable members herein can be at least partially deflated by applying one or more forces to the inflatable members to displace fluid therein towards a waste or fluid reservoir. For example, a shaft may be pushed distally over one or more inflatable members to apply force to the inflatable member(s) and push fluid out of the inflatable member. Additionally or alternatively, a radially inward force can be applied to the one or more inflatable members to push fluid out of the inflatable member(s). The one or more forces can be applied such that fluid is pushed towards a proximal end of the blood pump towards a waste device or fluid source.
The conduit can be made from a variety of materials. For example, the conduits herein can comprise one or more of a polyurethane rubber, a silicone rubber, an acrylic rubber, an expanded polytetrafluoroethylene, a polyethylene, or a polyethylene terephthalate, including any combination thereof.
The inflatable member 4103 may be the same material as the conduit, or it may be a different material. Inflatable member 4103 can comprise one or more of a polyurethane rubber, a silicone rubber, an acrylic rubber, an expanded polytetrafluoroethylene, a polyethylene, or a polyethylene terephthalate, including any combination thereof.
Inflatable member 4103 is an example of an inflatable member that has a helical configuration along at least a section of its length. Inflatable member 4103 is an example of an inflatable member that has a helical configuration along its entire length. Inflatable member 4103 is an example of an inflatable member that does not form the entirety of an inner surface of the conduit. Inflatable member 4103 is an example of an inflatable member that does not form any portion of an inner surface of the conduit. Inflatable member 4103 is an example of an inflatable member that extends from a proximal end to a distal end of the conduit. Inflatable member 4103 is an example of an inflatable member that is disposed completely radially outside of a flexible conduit. Inflatable member 4103 is an example of an inflatable member that does not have a cylindrical configuration along the length of the conduit.
Inflatable member 4103 is an example of an inflatable lumen that is not parallel with a pump portion longitudinal axis over at least 50% of the length of the inflatable member, over at least 60% of the length of the inflatable member, over at least 70% of the length of the inflatable member, over at least 80% of the length of the inflatable member, and over at least 90% of the length of the inflatable member.
Inflatable member 4103 is also an example of a lumen secured to an expandable conduit, the lumen having a proximal end that is aligned with a proximal end of the expandable conduit, wherein the lumen has a configuration along its length that is not solely axial between the lumen proximal end and a lumen distal end. In this embodiment, a distal end of the lumen extends to the distal end 4110 of the conduit, and the proximal end of the lumen is aligned with (or at least substantially axially aligned with) the proximal end 4111 of the conduit.
The inflation pathway 4104 (which is in fluid communication with inflatable member) can be secured to a proximal strut 4105 using a variety of techniques, such as suturing and/or adhesive.
The one or more impellers and the drive mechanism(s) that cause their rotation can be any of the impellers and drive mechanism(s) herein.
The helical inflatable member may be separately manufactured, then adhered to the collapsible and expandable conduit. For example, a conduit can first be advanced onto a mandrel. The helical inflatable member can then be positioned around the conduit and secured thereto using, for example, an adhesive and/or heat securing process. The inflation pathway may be secured to the inflatable member before or after the inflatable member is secured to the collapsible and expandable conduit.
The inflatable member can be inflated to cause the expandable conduit to assume a deployed configuration, creating the blood lumen. Any of the methods of use herein are expressly incorporated by reference herein for all purposes into the exemplary methods of use that follow. For example, pump portion 4100 can be deployed adjacent an aortic valve, such as is shown in
Inflation of the inflatable member increases the fluid pressure within the inflatable member, stiffening the inflatable member, causing the expandable conduit to expand toward the fully deployed configuration shown in
Pump portion 4160 is an example of a pump portion in which one or more inflatable members, when inflated, are configured and positioned relative to the blood conduit such that more radial support is provided at the location of the impeller(s) from the inflatable(s) than at a non-impeller region (which may be referred to as a region that is axially-adjacent to an impeller region). For example, the one or more inflatable members radially support expandable conduit 4162 more in impeller proximal region 4163 and in impeller distal region 4165 than in central region 4164, which is axially in between the two impellers. This may help provide more structural support at the region of the impeller(s), which may help maintain tip gap between edges of impeller blades and the blood conduit. Providing less radial support in central region 4164 may help maintain a certain degree of flexibility in the central region, which may help provide more flexibility where valve leaflets contact the pump portion (described in more detail herein and incorporated by reference into this section for all purposes), if the pump portion is positioned at such a location (see
Pump portion 4160 includes one or more inflatable members that provide radial support to expandable conduit 4162. An inflatable member may include multiple sections that are provided herein with different reference numbers. For example, an inflatable member may be considered to be a combination of individually labeled inflatable members, and as such the combination of inflatable members may itself be considered a single inflatable member. For example,
In some instances, an individual inflatable member can be considered any and all sections of a pump portion that are in fluid communication with a single fluid source. For example, sections 4170 and 4171 may be in fluid communication with a single fluid source, and may be inflated simultaneously when fluid is delivered from the fluid source. And section 4172 may be in fluid communication with a second fluid source (and not in fluid communication with 4170 and 4171). In this example, sections 4170 and 4171 may be considered sections of a first inflatable member, while section 4172 may be considered a second inflatable member. This disclosure is thus illustrative and not intended to limit the definition of an inflatable member, and an inflatable member herein may in fact comprise other structural elements described as a separate inflatable member herein.
In the exemplary embodiment in
In other embodiments there may only be a single impeller (e.g., a proximal impeller, or a distal impeller). In such instances there may only be a single region (e.g., region 4163 or region 4165) that provides greater radial support to the conduit than an axially-adjacent, non-impeller region.
The pitches of all three sections 4170-4172 are less in impeller regions 4163 and 4165 than in central non-impeller region 4164. The pitches gradually increase between the distal end of the proximal impeller and the middle of the conduit, and gradually decrease in the distal direction as the helical sections near the distal impeller, as shown. The pitches of any of sections 4170-4172 may be constant in at least a portion of impeller regions 4163 and 4165.
In an alternative embodiment, one or more impeller regions may each have a generally cylindrically shaped inflatable member that surrounds all or substantially all of the impeller, and a non-cylindrically shaped inflatable member may extend axially from the one or more cylindrically shaped inflatable members. For example, a pump portion may include one or more inflatable sections in a central region that have linear configurations and extend axially away from a cylindrically shaped inflatable member in an impeller region. Alternatively, a pump portion may include one or more inflatable sections in a central region that have helical configurations and extend axially away from a cylindrically shaped inflatable member in an impeller region. Alternatively, a pump portion may include one or more inflatable sections in a central region that have curvilinear (e.g., serpentine) configuration and extend axially away from a cylindrically shaped inflatable member in an impeller region. A pump pump portion may have more than one inflatable section in a central region that do not have the same general configuration as the other central region inflatable sections (e.g., one may be linear, one may be serpentine, one may have a different curvilinear configuration, etc.). Any of these sections may be considered part of the same inflatable member, a further discussion of which is described herein.
This application claims priority to U.S. Provisional Application No. 62/873,722, filed Jul. 12, 2019; U.S. Provisional Application No. 62/873,736, filed Jul. 12, 2019; and U.S. Provisional Application No. 62/881,176, filed Jul. 31, 2019, all of which are incorporated by reference herein for all purposes. This application is related to and incorporates by reference herein the disclosures of the following applications for all purposes: WO2018/226991, WO2019/094963, WO2019/152875, and WO2020/028537. All publications and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication or patent application was specifically and individually indicated to be incorporated by reference.
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| Number | Date | Country | |
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| 20210008261 A1 | Jan 2021 | US |
| Number | Date | Country | |
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| 62881176 | Jul 2019 | US | |
| 62873722 | Jul 2019 | US | |
| 62873736 | Jul 2019 | US |
