ENDO-LEAK FREE AORTIC ADAPTER ASSEMBLY AND METHOD OF DEVICE DELIVERY
An aortic adapter assembly is provided, including a T-shaped flow connector, including: an inserted conduit portion, having a blood-contacting surface which is smooth; an extruded neck portion, wherein the inserted conduit portion is joined with the extruded neck portion; and a truss, disposed in the inserted conduit portion; wherein the T-shaped flow connector has a polymeric elastomer reinforced by the truss having a Nitinol material; wherein the inserted conduit portion has an inner wall which is gradually thinning at two conduit ends of the inserted conduit portion, with a proper distance of a tip of the conduit end to the outmost boundary of the truss, and the conduit end possesses a compliance-matching effect to an implant site artery; wherein a proximal end of the extruded neck portion is configured to be joined with an inlet adapter of a blood pump. The aortic adapter assembly is accompanied with a quick-connector type coupler and a deployment method to accomplish an insertion type flow communication between a ventricular assist device and the human circulation.
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The application relates in general to an inflow/outflow cannula associated with blood pump connection to large arteries, and more specifically to para-aortic counterpulsatile circulatory support devices for cardiac insufficiency and the associated less invasive method of cannula delivery.
Description of the Related ArtMechanical circulatory support systems, in particular the left ventricular assist device (LVAD), continuously evolves into a treatment standard for advanced heart failure salvage. The LVAD systems can generally be classified into continuous-flow and pulsatile-flow pumps depending on the mechanical design of the blood pumps. Continuous-flow devices are constructed based on rotary machinery propelled by axial or centrifugal flow impellors. Pulsatile-flow devices, on the other hand, are designed using displacement type blood pump and often diaphragm blood sac is employed for receiving and ejecting blood into and/or out of the pump.
Inflow/outflow cannulas are artificial flow conduits for connecting the LVAD systems, either in series or in parallel, to the human circulatory system. Historically, the flow cannula design received less attention compared to the blood pump actuators. It is found, not surprisingly, that a significant number of post-operative complications arose in relation to the inflow/outflow cannula malfunctions. Adverse events such as cannula mal-positioning, obstruction, thrombus formation and the resultant distorted flow leading to pump thrombosis and thromboembolism. For rotary pump implantation, flow passage establishment is mostly carried out by connecting inflow cannula to the heart chamber whereas outflow cannula to the ascending or descending aorta. To date, almost all rotary pump outflow cannulas adopted Dacron graft or its alike, made of flexible fabric materials, and the connection to artery is via end-to-side anastomotic suturing method. Such end-to-side anastomosis is skill-dependent, and complications caused by unqualified suturing or incorrect flow direction to aorta may lead to clot formation, stroke, or thromboembolism and infarction in downstream organs.
Rotary pumps offer full-support (4-10 L/min) cardiac output and is currently indicated for terminal stage heart failure. For less sick patients, a less invasive implantable LVAD with partial-support (2-3 L/min) is thought more appropriate. Partial-support LVADs are intended to early intervene in heart failure to improve the treatment outcome. In this new trend of partial-support, less invasive LVAD implantation, counterpulsatile blood pump has been a main focus because of its proven efficacy of systolic unloading to the heart, and diastolic augmentation of blood perfusion to myocardium and major organs. Counterpulsatile pumping ought to follow stringent timing control criteria in reference to the heart rhythm. Typically, ventricular contraction unloading is initiated around the end-diastolic time point, while organ perfusion augmentation being carried out at the aortic valve closing time point (dicrotic notch on the aortic pressure waveform). The therapeutic effects provided, in fact, reside on two aspects including first, unloading of the ventricular contraction leading to myocardial oxygen consumption reduction, and second, elevation of diastolic arterial pressure to help increase perfusion in myocardium, brain, and major organs.
Counterpulsatile support efficacy is clinically demonstrated by intra-aortic balloon pump via a peripheral subcutaneous delivery of the balloon pump. However, the peripheral delivery to the descending aorta is frequently afflicted with insertion site vascular complications and finds difficulty in long-term use. In heart failure treatment, it is of high interest to extend counterpulsatile support from acute (less than a week) to longer term (months to years) support. To meet this requirement, it takes novel surgical method and device innovation to attain this long-term counter-pulsatile support goal.
The present counter-pulsatile support is carried out via left thoracotomy with device connected to the thoracic artery. This counter-pulsatile invention, called para-aortic blood pump, is implanted from a lateral pump connection through an access hole made in the descending aortic wall. In a sharp contrast to the intra-aortic balloon pump, the para-aortic blood pump does not occlude the blood flow passage, hence is more flexible in the counter-pulsatile timing control. It has been shown in animal studies that the hemodynamic support efficacy of para-aortic counterpulsation is better than that of the intra-aortic balloon pump. However, it is unknown whether para-aortic pump support may induce long-term complications. As a matter of fact, the challenge resides in the construction of a flow cannula, implanted in a less invasive manner, which can enable long-term fluid communication safely between the pump and the connected artery.
Para-aortic blood pump implantation requires a prosthetic conduit to be instituted to allow blood flow entering into and ejected out of the blood pump. Fast pump filling is generally required for an effective afterload reduction to the left ventricle as well as for creating a strong vortex washout to prevent pump thrombosis from occurring. Such fast pump filling often experiences with transient low-pressure that leads to the buckling collapse of the flow conduit. The use of conventional Dacron graft type cannula, hence, is not feasible because the fabric conduit cannot sustain compression force and the collapsed graft may occlude the inflow during pump fill phase. Moreover, the high- and low-pressure pulse induced by fast pump ejection and filling will pose bleeding concern to the suturing site, in particular in the acute period when the surgical anastomosis is not yet healed. It is of paramount importance that a flow cannula be engineered to overcome all these particular flow characteristics associated with para-aortic counterpulsation.
The hemodynamic characteristics of the para-aortic blood pump flow are not physiological. Blood flow sucked into or ejected out of the connected blood pump is not laminar in the arterial direction as usually seen in the natural aorta. Such side-dump, artificially generated pump flow is highly turbulent and complex. During pump filling phase, the flow makes a sharp turn into the blood pump, with flow separation and recirculation zone generated around the corner of flow turn. In the pump ejection phase as flow is accelerated into the descending aorta, the flow is characterized by an impinging flow with ultra-high pressure and shear stresses imparted on the opposing aortic wall region. This device-induced flow characteristics include low-speed recirculation zone and high-pressure, high-shear impinging jet flow, which would potentially cause endothelia cell erosion, lipid infiltration, smooth muscle cell proliferation, chronically resulting in stenosis of aortic wall or thrombus formation, or aortic dissection due to hypertension. Therefore, a long-term implantable counterpulsatile device design must innovate a prosthetic flow cannula that can avert or mitigate the aforementioned device-induced pathophysiological flow phenomena and the resulting vascular maladaptation as well as thrombotic or aortic dissection adverse events.
Safety in surgical anastomosis is another requirement requested for a flow cannula design of the para-aortic counterpulsatile pump. Conventional graft suturing may encounter challenging bleeding complication when subject to the excessive high-pressure fluctuation associated with the counterpulsatile flow. High- and low-pressure cycling is a main driving force for material fatigue failure, particularly when the implanted aorta is diseased (atherosclerosis or calcified), degenerated (thinning in wall thickness) or aged (stiffened wall). Note that aortic wall structure is adaptive in response to the imposed stress condition. The cells and tissues around the implant site would remodel along with the surgical injury healing process and further develop according to the device-induced, non-physiologic mechanistic environment. Even if short term success of implantation is attained, it does not guarantee that long-term graft failure would not be incurred in the post-operative course due to gradual cellular and morphologic maladaptation in the vascular wall.
To date, all viable solutions for end-to-side connection of artificial grafts to arteries are based on flexible, woven fabric tubes via suturing methods. There exist no long-term cannula solutions in the device industry that can address the problems related to the fluctuation level in the flow and pressure produced by a counterpulsatile para-aortic blood pump. Short-to-medium term (days to a month or so) counterpulsation efficacy has been clinically realized via intra-aortic balloon pump applications for over fifty years. This classic pneumatic energy transfer means for driving balloon inflation/deflation has been achieved using a thin catheter delivered percutaneously from remote peripheral arteries with lumen diameter in the range of 6-10 mm. Such delivery site arteries are largely blocked which often caused severe bleeding complication and downstream limb or arm ischemia, preventing percutaneous balloon counterpulsation from long-term use. Para-aortic placement is a new approach conceived, aiming to extend counterpulsatile therapy to a longer timeframe. However, long-term para-aortic counterpulsation demands a flow communicator be constructed to address the feature implant problems stated above. This flow cannula ought to be non-collapsible, easily implantable, bleeding free, and biocompatible without the concern of inducing pathological vascular maladaptation. The present invention is devoted to meet all the collective requirements by proposing an insertion type aortic adapter, which is to be disclosed in the following.
BRIEF SUMMARY OF INVENTIONTo address the deficiencies of conventional products, an embodiment of the invention provides an aortic adapter assembly, for an implantable ventricular assist device, including: a T-shaped flow connector, including: an inserted conduit portion, an extruded neck portion, both having a smooth blood-contacting surface, wherein the inserted conduit portion is joined with the extruded neck portion; and a truss, disposed in the inserted conduit portion; wherein the T-shaped flow connector has a polymeric elastomer reinforced by the truss having a Nitinol material; wherein the inserted conduit portion has a wall which is gradually thinning at two conduit ends of the inserted conduit portion, with a proper distance of a tip of the conduit end to the outmost boundary of the truss, and the conduit end possesses a compliance-matching effect to an implant site artery; wherein a proximal end of the extruded neck portion is configured to be joined with an inlet adapter of a blood pump..
In some embodiments, the truss is co-injected with a polymer substrate of the connector and embedded in the wall of the inserted conduit portion.
In some embodiments, the polymer substrate is made of a silicone material.
In some embodiments, the polymer substrate is a mold injectable polyurethane.
In some embodiments, a structural compliance of the embedded truss and a structural compliance of the polymer substrate are substantially equal to each other.
In some embodiments, the gradually thinning conduit ends are sharp-edged.
In some embodiments, the extruded neck portion has a shallow inclined surface to match with an inlet adapter of the blood pump, and an inner diameter of the extruded neck portion is slightly smaller than an inner diameter of the inlet adapter of the blood pump.
In some embodiments, the shallow inclined surface is inclined relative to an extending direction of the inserted conduit portion.
In some embodiments, the truss has a plurality of wavy structures.
In some embodiments, the extruded neck portion includes: a neck body; and a extension part, disposed on the neck body, wherein the extension part protrudes from the neck body, and the maximum inner diameter of the extension part is larger than the maximum inner diameter of the neck body.
In some embodiments, when the extruded neck portion is joined with the inlet adapter of a blood pump, the extension part snuggly embraces the inlet adapter, and the neck body is disposed around by the inlet adapter.
In some embodiments, the aortic adapter assembly further comprises a coupler, wherein the coupler includes: a flange base; a pair of collars, wherein the flange base mounted on the collars; and a latch, being able to lock the collars; wherein the collars have internal grooves which can clamp the T-shaped flow connector with a controlled compression to seal the T-shaped flow connector.
In some embodiments, each of the collars has a flange contour that enables a simultaneous engagement of the collars with respect to a rim of the flange base.
In some embodiments, the latch is made of a leaf spring that assures the coupler be locked without concern of incidental loosening.
In some embodiments, the coupler further includes a hinge joint disposed on the flange base, and the collars are pivotally connected to the hinge joint and rotatable to the hinge joint and the flange base.
In some embodiments, the hinge joint is located at the first side of the flange base, and the latch is located on a second side of the flange base, wherein the second side is opposite to the first side.
In some embodiments, the latch has is made of a leaf spring and has a slot in the middle that is able to lock with the ramp without the concern of disengagement.
In some embodiments, the flange base has a substantially circular-shaped structure, and each collar has an arc-shaped structure.
Another embodiment of the invention provides a blood pump device, for an implantable ventricular assist device, comprising the aforementioned aortic adapter assembly and a blood pump, wherein the blood pump has an inlet adapter, and the inlet adapter has a cone-shaped beak being able to fit with the proximal end of the extruded neck portion.
In some embodiments, the inner diameter of the inlet adapter of the blood bump is slightly larger than the inner diameter of the neck portion of the flow connector.
There are four embodiments that can be employed to realize the present para-aortic blood pump invention, as described below.
With reference to
The driver 18 comprises a battery power system 11 and a redundant battery power system (the battery power systems 21, 31, 41 in the
In
With reference to
The first embodiment has a cleaner driveline configuration and disposes electronic signal processor in the driver, hence minimizing the risk of environmental contamination (water ingress or moisture condensation) of the sensed pressure signal and the air leak incurred at the joint, both associated with the driveline interconnector 33. Nevertheless, this long driveline is more vulnerable to contact damage such as wear, kink, cut, abrasion arising from the contact with foreign objects in daily activities. Any major damage to the driveline 16 of the first or second embodiment, either electronically or mechanically, may warrant surgical blood pump replacement that is highly undesirable in view of surgical redo risk and the associated medical costs. The third or fourth embodiment, by employing a mid-way connector (driveline interconnector), mitigates such driveline damage-related blood pump replacement drawback. In general, the length of externalized distal driveline 37 is short and the interconnector 33 is protected better by the coverage of the skin dressing and/or the patient vest. In the extreme case of severe damage of the driveline beyond repairable, the most possibly damaged proximal driveline 39 can be easily exchanged without resorting to surgery. In addition, the third or fourth embodiment is more immune to electromagnetic interference because the analog-to-digital signal conversion is already accomplished in the circuitry in the interconnector 33. The fidelity of pressure signals can be better assured in the third or fourth embodiment because digital signal transmission in the proximal driveline 39 is less susceptible to the electromagnetic interferences.
With reference to
With reference to
With reference to
The implant subsystem is described further below.
Implantation is achieved through a relatively small thoracic opening by using less invasive surgical techniques via a left thoracotomy. A thoracic incision is made, for example, at the 7th intercostal space as the primary opening to allow placement of the aortic adapter and the blood pump. Two other small incisions are made at the 6th and 8th intercostal spaces, respectively, to introduce proximal and distal aortic cross clamps. The cross-clamped segment of aorta allows aortic adapter be inserted into the implant site through an excess hole made in the aortic wall. The aortic adapter is flexible and is able to be crimped and constrained into a smaller delivery configuration prior to insertion. Upon completion of delivery into aorta, the crimped aortic adapter shall be released and restore back to its original form with predetermined oversize to the implant site lumen diameter. The material of the aortic adapter hence is important, which shall be flexible but possessing sufficient radial strength to make the delivered adapter conduit remain circular without wall buckling. Candidate aortic adapter construct may include that made by silicone or polyurethane elastomers, or those polymeric constructs reinforced with embedment.
The functional requirements of the aortic adapter of each of the aforementioned embodiments is further described below.
Hemodynamically, the aortic adapter plays a role of flow communication between the blood pump and human systemic circulation. Besides this role, the aortic adapter also serves as a mechanical base to hold the blood pump in place when connected to the aortic adapter. The structure of the aortic adapter has to be elastic but kink resistant, and strong enough to withstand the internal blood pressure and the external contact forces, exerted via contact with the surrounding lung tissue or diaphragm associated with respiratory and thoracic movement.
The aortic adapter 54 is implanted inside the aorta with its two conduit ends 545, 645 interfaced with the aortic lumen forming a host/graft boundary in the blood stream (see
The driver of each of the aforementioned embodiments is further described below.
Illustrated in
Critical information in operation and alarm warning of device malfunction and aortic pressure conditions will be displayed on the user interface panel 73 of the driver 78. The primary battery can be exchanged through the battery access door 71 when primary battery power is exhausted. An electric cable is used to power the driver 78 via a connection through the AC receptacle 77 when patient is bedridden and power from wall outlet can be utilized in a long-term manner. The proximal driveline 99, 993 end is connected to the driver 78 through the driveline receptacle 75, through which both electric sensor signal and pneumatic pressure pulse are communicated. A pair of ventilation windows 79 are installed on the opposite sides of the driver 78 to allow ambient air to flow through the interior of the driver 78 for cooling purpose.
The driver 78 can be coupled externally to a clinical monitor, wherein the clinical monitor is provided for collecting and displaying real-time clinical waveform data and stores patient data for long-term condition monitoring and diagnosis. Further, a clinical monitor unit provides a user interface to the clinician for displaying device monitoring/diagnostic information and for accessing to driver parameter settings in order to initiate and optimize a patient-specific operational mode.
The EMA is a pneumatic actuator consisting of a brushless servo motor, a ball screw unit, a piston and a cylinder assembly. Atmospheric air is used as a driving medium to reciprocally eject and fill the blood pump.
The EMA module is housed within the driver carried by the implant recipient. The EMA consists of a brushless servo motor, a piston and cylinder assembly and a ball screw unit which comprises a ball screw rod and a nut. The piston is firmly mounted on top of the ball screw rod which is in rotational coupling with the nut of the ball screw unit. The servo motor includes a stator and a rotor and the rotor is integrated with the nut of the ball screw unit. Through the electromagnetic coupling of the rotor/stator induction, the rotor can be rotated in both clockwise and counter-clockwise directions, thereby driving the ball screw rod back-and-forth in a rectilinear manner to result in a reciprocating piston stroke motion in a cylinder. The stroke motion of the piston drives air to and from the implanted blood pump via a driveline connecting the blood pump and the cylinder.
There are two air driving problems associated with the present EMA pneumatic actuator design; namely, the air leak and the condensation of water vapor permeated from the blood through the blood sac wall. The former will impair the pump eject and fill function and driver power consumption leading to degradation of support effectiveness, and the latter will cause bacteria invasion risk to the driveline interior. To solve these two problems, the present EMA incorporates a pressure equalization valve installed in the cylinder chamber wall for air replenishment and moisture reduction. The pressure equalization valve is opened periodically at a predetermined frequency, allowing air mass transport between the cylinder and the ambient until the air pressure in the cylinder chamber equals the atmospheric pressure. The EMA incorporates position and optical sensors to acquire reference trajectory signals for the electronic controller to generate coordinated control commands to drive the piston stroke motion as well as to operate the pressure equalization valve. Hence, the timing and frequency for pressure equalization valve to be activated for air exchange can be programmed in the controller. With such pressure equalization valve incorporated the driving air medium can be constantly maintained in full and dry in the pneumatic actuator to guarantee a long-term safe and effective pumping support of the blood pump.
As illustrated in
The blood pump pressure sensor is built into the proximal blood pump shell and immersed in a small pressure sensing chamber filled with sensing medium, allowing a continuous monitoring of the blood pump pressure. A distal driveline is attached to the pump housing and provides timed air pressure pulses to command ejection and filling of the blood sac. The distal and proximal drivelines provide a pneumatically driven pressure pulse, generated by the EMA inside the driver, to the blood pump; and transmits an electrical blood pressure signal, generated by the pressure blood pump pressure sensor, to the driver. A driving air path (indicated by a dotted arrow line) and an electrical signal path (indicated by a solid-line) is illustrated in
With reference to
The driver receives blood pump pressure signal (electric signal) and processes the signal using trigger detection algorithm to generate trigger signal that commands the EMA actuation in synchronization with the heart rhythm. Upon receiving the assigned trigger timing, the micro controller unit sends commands to the motor controller unit to drive the piston, from eject-to-fill or from fill-to-eject courses, to provide counter-pulsatile circulatory support.
The architecture of the electronic controller incorporates three functional blocks, namely, a micro controller unit (MCU), a motor control block (motor controller unit), and a power management unit. The following Table provides descriptive outlines for each functional block of the driver 78.
The signal acquisition, transmission, processing, and the control logic and command generation and EMA actuation to produce pressure pulse to drive the blood pump is illustrated in
When the MCU loses the BPP signal (electrical signal) sent from the blood pump, a washout mode is launched automatically by MCU to drive the EMA, operating at a predetermined pumping rate and driver stroke volume. The washout mode is used to prevent the formation of thrombus in the blood sac, which is a device protection mode instead of providing synchronous circulatory support.
The para-aortic blood pump device of the present invention, with its non-occlusive para-aortic feature, in principle, has a better counter-pulsatile support efficacy as compared to the intra-aortic balloon pump (IABP). Unlike the bedridden or ambulatory IABP patients who have to stay in hospital, the portable para-aortic blood pump device allows the patients to leave the hospital and have ambulatory capability to live a better life at home. Hence, the para-aortic blood pump device of the present invention may further improve patient’s disease conditions and quality of life, in addition to the economic benefits gained from a shorter hospital stay.
The trend of LVAD use has been plateaued in recent years, mainly because its application is only indicated to the terminal-stage heart failure patient cohort. Applying early intervention LVAD therapy to the less-sick heart failure patients has long been a clinical objective, which is expected to imposing substantial impact on the future cardiac medicine advancement provided by the broadened use of LVAD therapy. Clinical evidences have shown that certain non-ischemic cardiomyopathy patients supported by LVAD, administered in moderate-to-severe heart failure stage, can be improved with myocardial reverse remodeling toward functional upgrade or sustained myocardial recovery. Nevertheless, this intention of early intervention must be ushered by two enabling factors: an easy and safe surgical procedure, and an effective and adaptive support scheme accompanying disease development. Continuous-flow VAD support is non-physiologic, which deranges the supported heart away from a normal course of recovery. The counter-pulsatile support, however, is physiologic and meets the therapeutic requirement by providing systolic contraction unloading and diastolic perfusion augmentation to promote myocyte reverse remodeling. In summary, the treatment strategy provided by this para-aortic blood pump invention aligns with the early intervention trend development in cardiac medicine. Salutary attributes provided by the para-aortic blood pump device, such as adaptive partial-support, less invasive surgery and counter-pulsatile therapeutics will collectively make the present invention a prospective candidate to contribute to the future advancement of heart failure treatment.
The blood pump of each of the aforementioned embodiments is further described below.
With reference to
With reference to
Referring to
A miniaturized pressure sensor 527 is built into the pump shell 523 and fluid communicated to the enclosed pressure sensing chamber 528. This arrangement allows a continuous monitoring of the blood pressure contained in the blood sac 529. Since the pressure sensor 527 is not blood-contacting, the long-term sensor reliability and fidelity is assured by the protection of the pump housing 52h that isolates the sensor 527 and its electric circuit from the influence of chemical corrosion and protein adherence arising from the direct blood contact.
A driveline 57 end is attached to the pump shell 525 to provide timed air pressure pulses for actuating the eject or fill stroke of blood out of or into the blood pump 52. The driveline design can be multi-luminal or multi-layered so as to accommodate the electrical wires for pressure signal transmission. Metallic coil or fabric mesh can be adopted as the wall reinforcement to enhance the anti-kink capability of the driveline 57. The overall geometry of the blood flow passage in the present blood pump is wide, along with the valveless aortic adapter design and pulsatile pumping operation, constituting a superior blood handling property that avoids high shear-induced hemolysis as well as low flow speed generated thrombus formation or thromboembolism.
The blood sac 529 of the blood pump 52 includes an innovative design to make the sac membrane 526 durable. The blood sac 529 is an oval-shaped membrane body of revolution to the centerline of the blood pump 52. There are two polymeric stems (proximal stem 530, distal stem 540) bonded at both housing 52h ends, configured respectively to be in a circular disc or an annulus shape, and working as a flexing/stretching relief mechanism to alleviate stress concentration when attached to the rigid housing 52h. During pump ejection, the sac membrane 526 will be compressed or folded into a tri-lobe shape where the highest strain often occurs at the creased folding line near the rim of the stem attachment (proximal stem 530, distal stem 540). This local high membrane stress/strain arising from large membrane deformation is substantially reduced or absorbed by the deformation of the flexible stem rim as a bendable suspension. Notice that the tri-lobe folding pattern is non-stationary, with creases changing from place to place as influenced by the gravitational direction. In fact, a patient’s body posture and orientation including the positions of standing, sleeping, sitting, exercising, etc. may change from time to time in daily activities. The gravitational effect or the body force acting on the stored blood volume in the blood pump 52 is hence constantly changing, resulting in a non-stationary crease line initiation and formation. Such running membrane folding line constitutes a unique fatigue resistance feature of the present invention. It is anticipated that the present blood pump 52 will possess a much longer durability than that of the conventional fixed folding line membrane design.
Membrane folding and expansion are intimately related to the vortex flow pattern contained in the blood sac 529. The aforementioned sac design features a running folding line formation that makes the vortex structure pattern alternatingly change in response to the folded membrane pattern. The washout effect in the blood pump 52 is thus strong and non-stationary, characterized by a random walk-like vortical flow movement. Such randomness in the pump vortex flow structure helps washout the entire blood-contacting surface without creating any fixed low-speed zone near the membrane wall or in the crease area. It has been observed in animal trails that the present blood pump is very thromboresistant.
The (distal) driveline of each of the aforementioned embodiments is further described below.
Referring to
The (distal) driveline 991, 971 and its connector are designed to withstand the tensile loads applied during surgical externalization. Post-operatively, the (distal) driveline 991, 971 is constantly influenced by muscular motion-induced loads, and the (distal) driveline 991, 971 is designed to withstand these loads for their intended service life. The externalized portion of (distal) driveline 991, 971 is also designed to be biocompatible and chemically resistant to cleaning agents and disinfectant in clinical use.
The (proximal) driveline of each of the aforementioned embodiments is further described below.
The (proximal) driveline 993, 99 is used to connect the (distal) driveline 991, 97 to the driver 98. The (proximal) driveline 99 has a driveline interconnector 93 at one end and a driver connector at the other end. The said driveline interconnector 93 encloses a circuit board, which converts analog blood pump pressure signal into digital signal, and a vibrator that provides a tactile feedback in addition to the audible alarms. The driveline interconnector 93 comes with a flat shape to prevent torsion from being generated to the (distal) driveline 973 when the driveline interconnector 93 is anchored against the patient’s skin. Further, the driveline interconnector 93 and the driveline outer cover are designed to be sealed and protected against water or moisture ingression. Since the (proximal) driveline 99 is installed externally, it can be replaced and/or maintained when deemed necessary, hence eliminating the surgical blood pump replacement required when the (proximal) driveline 99 is damaged beyond repairable.
Valveless blood pump has two advantages in blood handling characteristics: 1) having no annoying valve sound and valve-induced blood cell damage, thrombus formation and thromboembolism; 2) being more thromboresistant because the two-way pulsatile flow has better surface cleaning effect to minimize protein adhesion and avert interface discontinuity-related clot formation over the blood-contacting artificial surfaces. The flow passage in the valveless pulsatile pump is uniformly much wider that those in the valved pulsatile or continuous-flow rotary pumps. Hemolysis (rupture of red blood cell membrane) generally takes place at narrow flow passages with high flow velocity gradient, such as the gaps between the valve ring and leaflet of a valved pulsatile pump. In addition, low-speed recirculation or stasis zone often exists in the back side of the opened valve which may encourage thrombus to be generated. In a sharp contrast, in a valveless pulsatile blood pump, the shear stress applied on blood cells is literally order of magnitude smaller, and the low-speed stasis zone associated with valve geometry and motion is substantially eliminated, which leads to less blood cell damage or platelet activation, less clot formation and aggregation and translates to lower dose of anticoagulant use and easier and safer post-operative care.
As shown in
In this embodiment, the feedthrough 63 is disposed in the distal shell 625 of the pump housing 62h for coupling the driveline 67 to the pump housing 62h. Further, the feedthrough 63 is configured in a body-fitted shape adjacent to the distal shell 625, making driveline connection in a tangential direction to the pump outer surface. Such body-fitted feedthrough design renders pump housing 62h design adaptive to the anatomic space available for blood pump placement. The blood pump 62 can be rotatably connected to the interface adapter 501 and allow the driveline 67 be routed with best suited orientation to enable a smooth subcutaneous tunneling and skin exit. In this way, it favors to anatomic adaptivity to the implant site geometry.
In this embodiment, the feedthrough 63 is remotely suited in the distal shell 625 while the pressure sensor 6271 (see
As illustrated in
The embodiment of the present invention innovates a running folding line attribute which makes the high-strain location appearing non-stationarily in the membrane to prolong sac fatigue life. The detrimental stress concentration phenomenon frequently associated with the flexing blood sac is hence improved. Based on this fundamental change in flexing pattern behavior, the fatigue life of membrane will significantly increase attributable to this non-stationary folding line formation characteristic that disperses the high strain areas all over the sac. Further, a salutary outcome accompanying this non-stationary sac deformation pattern resides on the vortex washout effect enhanced within the blood sac. The sac surface will be washed more thoroughly with a random walk-like vortex formation and traversing. The probability of producing constant low-speed recirculation zone dwelling in the near-wall region or creases of the folding lines, hence, will be greatly reduced, resulting in a long-duration, thrombo-resistant blood pump design.
The blood sac 629 is anchored onto the pump housing 62h, which includes a proximal shell 623 and a distal shell 625, to facilitate pump fill and ejection actions. In general, the flexural properties of the sac 629 and the housing 62h are vastly different. To accomplish a long-duration sac design, it requires an intermediate suspension to be installed to render the pump assembly continuous in structural property transition, in particular the membrane flexural deformation. A pair of flexible stems 630 and 640 is adopted as the suspension that integrates the blood sac 629 with the housing 62h. As shown in
As shown in the bottom of
During surgical operation, the closed-end sac design of the valveless blood pump 62 would attract air and agglomerate air bubbles in the sac top due to buoyancy force. As shown in
As illustrated in
The pressure sensing mechanism 627, as detailed in
An embodiment of the present invention innovates a pressure-based blood pump control method and sensor design. A miniature MEMS pressure sensor is adopted with electronic circuit packaged and embedded in the pump housing wall. In principle, MEMS sensor die is very durable owing to its intrinsic micro-scaled structure. Sensor durability, in fact, depends on the packaging design. The present pressure sensing system 627 is non-blood contacting and isolated from the corrosive biochemical effects associated with blood, thus providing long-duration signal acquisition and transmission that is required for long-term implantable assist devices.
The driveline 67 works as a communicator for electric signal transduction and pneumatic pulse pressure transfer between the blood pump 62 and the driver 98. A representative multi-layered driveline 67 in the present invention is shown in
The central portion of the driveline 67 accommodates the pneumatic lumen 6701 (or air passage, inner tubing) with a lumen diameter around 2-5 mm, depending on the preference of choice between lower energy consumption or low-profile for easiness of surgery. The electric wires 6702 for signal transmission are embedded in the wall of the driveline 67. There are variants of driveline design that may be adopted. Aside from the multi-layered driveline design shown in
The inner tubing, or pneumatic lumen 6701, is received by the middle tubing 673 with reinforcement being sandwiched in between. Between the inner and middle tubing 6701 and 673, the coil 674 (or fabric thread or mesh) can be reflowed (thermally co-molded using heat shrink) as a reinforcement to the driveline wall, making the driveline 67 flexible but kink resistant. The outer layer tubing 675 covers the inner and middle pneumatic tubing 6701 and 673, and can be employed to cover the spirally wrapped electric wires 6702 as a protective sheath. In some embodiments, a non-distensible tether 676 can be disposed between the outer tubing 675 and the silicone jacket 677 of the driveline 67, to strengthen the tensile resilience required during externalization of the driveline 67. Clinically it has been demonstrated that silicone jacket 677 is least irritative to the subcutaneous tissues and has the lowest driveline infection rate.
In this embodiment, the pneumatic lumen 6701, the metal coil 674, the middle tubing 673, the spiral electric wires 6702, the outer tubing 675, the tether 676, and the silicone jacket 677 are packaged into a body of the driveline 67. The proximal end 671 of the driveline 67 is to be plugged into a receptacle housed in the driver 98. The rigid driveline connector 678 of the driveline 67 is configured to be received by the receptacle of the proximal driveline interconnector 93 or the driver 98. The rigid driver connector 678 is flush mounted with a plurality of electrodes 6781 (for example, four electrodes 6781 in
The connection of the driveline 67 onto the blood pump 62 is accomplished via a feedthrough 63, as illustrated in
As shown in
The modular design pertaining to the first embodiment of the present blood pump invention has been disclosed in
As shown in
In counterpulsatile support, pump fill and ejection are alternatingly actuated in synchronization with cardiac rhythm, which generates a special T-juncture flow as shown in
The aortic adapter 14 is mold injected with its internal blood-contacting surface 141 being manufactured ultra-smooth and continuous without any parting lines. Silicone or other polymeric elastomers can be used as the material. The aortic adapter 14 comprises a conduit (or an inserted conduit portion) 142 which is to be inserted in the aorta 95 (see
The entire aortic adapter 14 is thin-walled to maximize the flow efficiency. To strengthen the thin-walled structure, a pair of Nitinol truss (or truss rings) 144 is embedded around the two ends of the conduit portion 142 of the aortic adapter 14.
One of the complications that plagued the large stent graft implantation is the endo-leak problem. Type-I endo-leak means the seal of the graft end to the endothelial lumen of the implanted artery is not complete, causing gap created between the graft leading-edge and the arterial lumen. Leaked blood will be trapped and jammed in the gaps and solidified into clot and finally becomes fibrous pseudo-intima which will grow uncontrollably in time. Not only the pseudo-intima will obstruct the grafted artery, but also it may signal and stimulate coagulation mechanism to attract platelet adhesion and leads to thrombotic adverse events to occur. The solution to resolve such endo-leak problem is to have a tight seal of the aortic adapter 14 with respect to the attached lumen surface. The present aortic adapter 14 comes up with a compliance-matching design concept that enables the semi-rigid conduit ends 145 seamlessly attach to the arterial lumen when subject to pulsatile blood pressurization. The outside diameter 146 of the aortic adapter conduit 142 is slightly larger than the luminal diameter with an oversize ratio (defined as percentage increment in conduit diameter 146 relative to luminal diameter) in the range of 3-10 % conditioned at certain nominal blood pressure (say 120 mmHg). As blood pressure fluctuates between systole and diastole, or under the pulse pressure generated by counterpulsatile support, the compliance-matching conduit ends 145 will dynamically expand and contract in response to the pressure pulsation without creating interfacial gaps.
Generally speaking, a thin-walled tubing made of elastomer is flexible and tends to be compliance-matching, but it is often not strong enough to withstand the compression force exerted due to device oversizing, causing wall buckling of the inserted adapter and the resultant massive bleeding. Hence, the combined use of Nitinol truss structure 144 and the elastomeric substrate with appropriate hardness is important. As shown in
Illustrated in
A convenient measure of conduit rigidity (inverse of compliance) can be represented by the so-called lateral stiffness (LS) whose measurement method is illustrated in
The aortic adapter 14 is configured to be connected to the blood pump 62 to facilitate circulatory support. A quick-connector type coupler is invented herein. Illustrated in
In particular, quick-connection type locking can easily be carried out by closing the collars 253 that will be latched without a concern of unintentional unlocking, as depicted in
A butt joint design is not feasible for connecting two smooth-surfaced tubing adapters in a blood stream. In most clinical applications, the connected graft is with rough surface to promote endothelialization so that tiny interface discontinuity in the blood stream will be “smoothed out” by the ingrown cells and proteins. The present aortic adapter 14 adopts smooth surface approach to avoid thrombotic adverse events to occur. The blood flow in the aortic adapter is bi-directional in response to the ejection and filling action of the counterpulsatile pumping, as depicted in
In practice, tolerance inevitably exists in matching two separate bodies even if the machining of each body is perfectly performed.
As shown in
The inner diameter 84 of the beak 82 is slightly greater than the inner diameter 148 (see
The clamping force generation mechanism is graphically shown in
The present design of interface connection between the blood pump 62 and the aortic adapter 14 has two hemodynamic merits for reducing thrombus formation in-situ. First, there will be literally no step or gap type joint discontinuities generated as observed in the conventional butt joint connection. Second, stasis flow located in the interface of the beak leading-edge 85 can be minimized. Hence, blood stream flowing over the connected interface will be maintained with high-speed, substantially improving the butt connection drawback, namely the forward-facing or backward-facing steps 101,102 or the gap 103 created at the interface.
The present cone surface 149 is ramped with an inclination angle to the stream direction. Such ramp interface design averts step or gap be generated at joint due to limited manufacturing precision or matching eccentricity associated with conventional butt connection. Nevertheless, this shallow, cone-shaped ramp 149 has an intrinsic shortcoming in fulfilling a concentric centerline alignment of the joined counterparts. The present coupling of the aortic adapter 14 with the inlet beak 82 has no strict lateral constraint to assure coupling alignment. To connect a rigid beak 82 with a semi-rigid aortic adapter flange ramp 149 concentrically, a simultaneous catching of the collars around the entire peripheral rim of flange base 252 is critical. When a simultaneous catching/locking engagement fails to be accomplished, the initially caught adapter flange ramp 149 will be strained more than other free portion, creating a tendency to tilt or disposition the rest contact surface leading to an eccentric pump connection. Such an eccentric connection often is the causal factor that generates step or gap at the interface that induces thrombus formation. This drawback is remedied by having the flange contour 259 (
Structural deformability and method of delivery involved in the present aortic adapter confers a special design feature of the present invention. Material elasticity consideration, in fact, need to be carefully incorporated in the present design. Surgically deliver an insertion type graft into aorta via incised aortic wall is challenging in the sense of peri-operative safety and long-term reliability. The material chosen for the present aortic adapter 14 should have a preset memorized shape. During device delivery, the adapter 14 is first crimped into a smaller delivery configuration, and such delivery configuration guarantees a quick and safe device implantation. After the crimped aortic adapter 14 is placed at the intended implant site, the delivery configuration shall be released to self-expand to its original memorized shape.
Prior to aortic adapter insertion a hole of diameter 12-14 mm ought to be made in the aortic wall. In making such an access hole, care must be taken to avoid making any cut edges that may become a crack initiation point when wall distension is required for device insertion. A side-biting aortic punch, as disclosed in U.S. Pat. Appl. No. 17/034036, is an ideal tool for making a large hole in the aorta. With one bite of punch a sound hole without any fractured edges can be made successfully.
The aortic adapter 14 morphologically includes two circular tubes joined together into a T-shaped flow communicator for para-aortic circulatory support enforcement. The conduit wall is typically 1-2 mm in thickness and the material used is polymer such as silicone or polyurethane with appropriate hardness, for example, of Shore A 80-90. The crimped delivery configuration differs substantially from the commercially available large stent graft covered by Dacron or PTFE (Polytetrafluoroethylene) fabric. In
This folded adapter can be held fixed by string tightening. For example, as shown in
Additional safety measures can be applied to enhance the hemostasis and stability of the implanted para-aortic blood pump system. Para-aortic placement of blood pump inevitably involves lateral force (perpendicular to the longitudinal direction of the aorta) and torque exerted on the aortic adapter 14 due to the weight of blood pump 62 and the pumping forces generated by counterpulsatile support. Such device related external forcing may affect the long-term remodeling of the implant site vascular structure. A purse-string suture can be placed in the adventitial layer around the access hole. The purse-string suture can additionally tighten the aortic wall against the inserted adapter 14 and works as a protective measure to prevent the enlargement of the access hole. Moreover, surgical tapes can be looped and tightened around the two ends of the conduit 142, strengthening the integration of the inserted aortic adapter 14 and aorta as a whole. Freedom from endo-leak can be doubly assured by the compliance-matching design and the banding of the looped tapes. Sometimes, blood pressure may elevate beyond the upper bound that endo-leak free can be assured by compliance-matching. Under such extreme condition, surgical tapes come into play working as a hard limiter that seals the detached adapter ends and assures hemostasis be maintained.
The step-by-step demonstration of implanting the aortic adapter 14 is detailed in
In summary, an embodiment of the present invention provides a ventricular assist device, including a blood pump, a driveline and a feedthrough. The blood pump includes an axi-symmetric oval-shaped blood sac and stem assembly, including a flexible membrane sac, proximal stem, and a distal stem, wherein the flexible membrane sac is attached with the proximal stem and the distal stem as a stress-relief suspension mechanism; a pump housing, including a proximal shell and a distal shell, wherein the stress-relief suspension mechanism is coupled to the pump housing; and a pressure sensing system, embedded in the proximal shell, wherein the pressure sensing system includes a pressure sensor and a pressure sensing chamber which is filled with an incompressible fluid for pressure transmission. The driveline includes a pneumatic lumen, at least one electric wire and a tether, wherein the electric wires and the tether are disposed in the driveline wall. The feedthrough connects the driveline to the pump housing.
An embodiment of the present displacement pump invention discloses a pulsatile blood pump design that incorporates a non-stationary folding line concept in the construct of a long-duration blood sac that may substantially prolong the durability of a displacement type blood pump. Also, a miniature pressure sensing system is disclosed, which can be used to serve as reference waveform for real-time pump control as well as for long-term trending analysis, disease monitoring and diagnosis, based on evidence-based mega data. Further, the embedded pressure sensing system is non-blood contacting, which, hence, greatly improves the reliability requirements in building an implantable sensor system.
The embodiment of the present blood pump invention has at least one of the following advantages or effects. By the feedthrough connection of the driveline to the pump housing, a compact feedthrough design is provided to make the electric wiring and signal transduction more robust and fault tolerant. Further, a compact feedthrough design integrates the sensory electric wires and the pneumatic tubing with the blood pump. This compactness attribute is particularly essential for implant devices. It not only simplifies surgical operation and mitigates peri-operative implantation risks, but also contributes to the reduction of post-operative morbidity associated with driveline infection.
In some blood pump embodiments, the feedthrough is integrated with a distal shell of the pump housing and the feedthrough has a first portion as an extension of the distal shell in which the pneumatic lumen, the tether and the electric wire of the driveline are coupled, and a second portion being interlocked with the first portion working as a bend relief of the driveline, to the advantage of anatomic adaptivity and fitness to the implant site geometry.
An embodiment of the present flow communication invention provides an aortic adapter assembly, for an implantable ventricular assist device, comprising: a T-shaped aortic adapter, including: an inserted conduit portion, an extruded neck portion, wherein the inserted conduit portion is joined with the extruded neck portion, both having a blood-contacting surface which is smooth; and a truss, disposed in the inserted conduit portion; wherein the T-shaped aortic adapter has a polymeric elastomer reinforced by the truss having a Nitinol material; wherein the inserted conduit portion has a wall which is gradually thinning at two conduit ends of the inserted conduit portion, with a proper distance of a tip of the conduit end to the outmost boundary of the truss, and the conduit end possesses a compliance-matching effect to an implant site artery; wherein a proximal end of the extruded neck portion is configured to be joined with an inlet adapter of a blood pump.
The embodiment of the present flow communication invention has at least one of the following advantages or effects. The present invention discloses a flow communicator assembly that enables blood flow transport into and out of a para-aortic ventricular assist device 10, in particular, a counterpulsatile blood pump. Unlike many existing flow communicators that employ rough surface approach to promote endothelialization so as to avert thrombotic adverse events to occur, the present aortic adapter invention adopts a smooth surface, insertion type prosthetic graft concept to construct the flow communicator. Further, a compliance-matching design is embodied around the inserted conduit ends, which combines the gradually thinning wall characteristic with a super-elastic Nitinol supported thin-walled polymer to accomplish the endo-leak free requirement. Abnormal high pressure, high shear, and low-speed recirculation flow phenomena associated with para-aortic counterpulsatile pumping are contained within the artificial surface of the inserted conduit. Hence, the pathologic device-induced hemodynamic influences and risk factors are substantially eliminated and long-term vascular maladaptation related adverse events such as endothelial cell erosion, lipid infiltration, smooth muscle cell proliferation, vascular stenosis, arterial wall dissection, etc. are significantly reduced. To accomplish a sound connection of the semi-rigid flow adapter to a blood pump, a quick connector type coupler is invented. This coupler has a self-alignment interface design that minimizes the step and gap discontinuity and hence reduces the possibility of thrombotic adverse events to occur at interface joint. Accompanying this aortic adapter invention is a specially designed delivery method that assures a quick and safe delivery procedure. The crimped aortic adapter is made into a prepack delivery configuration whose overall size is reduced into half of its deployed configuration. This prepacked adapter can be inserted into the implant site aorta easily and self -expands into its original deployed configuration, resulting in a snuggly fitted flow communicator without the concern of endo-leak. It is not only beneficial for surgical operations that mitigate peri-operative implantation risks, but also contributes to the reduction of post-operative morbidity associated with device-induced flow and implant site vascular maladaptation.
Use of ordinal terms such as “first”, “second”, “third”, etc., in the claims to modify a claim element does not by itself connote any priority, precedence, or order of one claim element over another or the temporal order in which acts of a method are performed, but are used merely as labels to distinguish one claim element having a certain name from another element having the same name (but for use of the ordinal term) to distinguish the claim elements.
Embodiments of this invention are described, and variations of those embodiments may become apparent to those of ordinary skill in the art upon reading the foregoing description. Accordingly, this invention includes all modifications and equivalents of the subject matter recited in the claims.
Claims
1. An aortic adapter assembly, for an implantable ventricular assist device, comprising:
- a T-shaped flow connector, including: an inserted conduit portion and an extruded neck portion; wherein the inserted conduit portion is joined with the extruded neck portion; both having a blood-contacting surface which is smooth; and a truss, disposed in the inserted conduit portion; wherein the T-shaped flow connector has a polymeric elastomer reinforced by the truss having a Nitinol material; wherein the inserted conduit portion has a wall which is gradually thinning at two conduit ends of the inserted conduit portion, with a proper distance of a tip of the conduit end to the outmost boundary of the truss, and the conduit end possesses a compliance-matching effect to an implant site artery; wherein a proximal end of the extruded neck portion is configured to be joined with an inlet adapter of a blood pump.
2. The aortic adapter assembly as claimed in claim 1, wherein the truss is co-injected and embedded in the wall of the inserted conduit portion of the flow connector.
3. The aortic adapter assembly as claimed in claim 2, wherein the polymer substrate is a silicone material.
4. The aortic adapter assembly as claimed in claim 2, wherein the polymer substrate is a mold injectable polyurethane.
5. The aortic adapter assembly as claimed in claim 2, wherein a structural compliance of the embedded truss and a structural compliance of the polymer substrate are substantially equal to each other.
6. The aortic adapter assembly as claimed in claim 1, wherein the gradually thinning conduit ends are sharp-edged.
7. The aortic adapter assembly as claimed in claim 1, wherein the extruded neck portion has a shallow inclined surface to match with an inlet adapter of the blood pump, and an inner diameter of the extruded neck portion is slightly smaller than an inner diameter of the inlet adapter of the blood pump.
8. The aortic adapter assembly as claimed in claim 7, wherein the shallow inclined surface is inclined relative to an extending direction of the inserted conduit portion.
9. The aortic adapter assembly as claimed in claim 1, wherein the truss has a plurality of wavy structures.
10. The aortic adapter assembly as claimed in claim 1, wherein the extruded neck portion includes:
- a neck body; and
- an extension part, disposed on the neck body, wherein the extension part protrudes from the neck body, and the maximum inner diameter of the extension part is larger than the maximum inner diameter of the neck body.
11. The aortic adapter assembly as claimed in claim 10, wherein when the extruded neck portion is joined with the inlet adapter of a blood pump, the extension part snuggly embraces the inlet adapter, and the neck body is disposed around by the inlet adapter.
12. The aortic adapter assembly as claimed in claim 1, further comprising a coupler, wherein the coupler includes:
- a flange base;
- a pair of collars, mounted rotatably on the flange base; and
- a latch, being able to lock the collars;
- wherein the collars have internal grooves which can clamp the T-shaped flow connector with a controlled compression to seal the T-shaped flow connector.
13. The aortic adapter assembly as claimed in claim 12, wherein each of the collars has a flange contour that enables a simultaneous engagement of the collars with respect to a rim of the flange base.
14. The aortic adapter assembly as claimed in claim 12, wherein the latch is made of a leaf spring that assures the coupler be locked without concern of incidental disengagement.
15. The aortic adapter assembly as claimed in claim 12, wherein the coupler further includes a hinge joint disposed on the flange base, and the collars are pivotally connected to the hinge joint and rotatable to the hinge joint and the flange base.
16. The aortic adapter assembly as claimed in claim 15, wherein the hinge joint is located at the first side of the flange base, and the latch is located on a second side of the flange base, wherein the second side is opposite to the first side.
17. The aortic adapter assembly as claimed in claim 16, wherein the latch has a slot which can be engaged with a ramp on the opposite collar.
18. The aortic adapter assembly as claimed in claim 12, wherein the flange base has a substantially circular-shaped structure, and each collar has an arc-shaped structure.
19. A blood pump device, for an implantable ventricular assist device, comprising:
- a blood pump, having an inlet adapter, wherein the inlet adapter has a cone-shaped beak;
- an aortic adapter assembly, for an implantable ventricular assist device, comprising: a T-shaped flow connector, including: an inserted conduit portion and an extruded neck portion; wherein the inserted conduit portion is joined with the extruded neck portion; both having a blood-contacting surface which is smooth; and a truss, disposed in the inserted conduit portion;
- wherein the T-shaped flow connector has a polymeric elastomer reinforced by the truss having a Nitinol material;
- wherein the inserted conduit portion has an inner wall which is gradually thinning at two conduit ends of the inserted conduit portion, with a proper distance of a tip of the conduit end to the outmost boundary of the truss, and the conduit end possesses a compliance-matching effect to an implant site artery;
- wherein a proximal end of the extruded neck portion is configured to be joined with the inlet adapter of a blood pump;
- wherein the cone-shaped beak is able to fit with the proximal end of the extruded neck portion.
20. The blood pump device as claimed in claim 19, wherein the inner diameter of the inlet adapter is slightly larger than the inner diameter of the neck portion of the flow connector.
21. A method of implanting a flow connector assembly as claimed in claim 1, with an artery, the method comprising:
- crimping the flow connector into a delivery configuration; wherein the size of the delivery configuration is at least half of the diameter of the original flow connector; and
- inserting the delivery configuration of the flow connector into an artery having an access hole punched in the arterial wall;
- releasing the inserted delivery configuration of the flow connector; wherein the released flow connector is self-expandable to its original deployed form; and
- coupling the deployed flow connector with a ventricular assist device to assist circulation in the patient.
Type: Application
Filed: Dec 2, 2022
Publication Date: Aug 24, 2023
Applicant: 3R Life Sciences Corporation (Campbell, CA)
Inventors: Pong-Jeu LU (Kaohsiung City), Hsiao-Chien LIN (Kaohsiung City)
Application Number: 18/074,201