Patent Application
20190365979
The present application relates generally to the fields of medicine and biomedical engineering and more particularly to devices and methods for performing cardiopulmonary bypass in human or non-human animal subjects.
Pursuant to 37 CFR 1.71(e), this patent document contains material which is subject to copyright protection and the owner of this patent document reserves all copyright rights whatsoever.
In extracorporeal life support (ECLS), blood is removed from a subject's circulatory system and channeled through an ECLS system wherein the blood becomes oxygenated and carbon dioxide is removed. The oxygenated blood is then delivered back into the subject's circulatory system. Most ECLS systems include pumps which propel or circulate the blood through the subject's vasculature thereby assuming the function of both the heart and lungs, even if the subject's heart is stopped or beating inefficiently. Other ECLS systems (e.g., the Novalung System, Novalung GmbH, Heilbronn, Germany) provide pumpless extracorporeal lung assist by oxygenating and removing carbon dioxide from the blood while relying on the subject's beating heart to adequately circulate the blood through the device and through the subject's vasculature.
In general, ECLS techniques include extracorporeal membrane oxygenation (ECMO) as well as cardiopulmonary bypass (CPB). ECMO is essentially a form of partial CPB. ECMO is typically used for extended periods of time (e.g., days) while CPB is used for relatively short periods (e.g., hours). CPB has traditionally been used during cardiac and aortic surgical procedures wherein the heart is stopped. Generally, in ECMO vascular access is achieved by inserting cannulas into peripheral blood vessels using percutaneous technique or superficial surgical cut and then advancing the cannulas to locations in the central vasculature (e.g., vena cava, right atrium, aorta). In CPB vascular access is typically accomplished by intraoperative connection of cannulas to intrathoracic blood vessels.
ECMO can be performed either as venoarterial ECMO (VA-ECMO) or venovenous ECMO (VV-ECMO). In VA-ECMO, deoxygenated blood is removed from a vein and the oxygenated blood is returned into an artery. In VA-ECMO the system typically pumps the blood under pressure to partially support the subject's cardiac output while VV-ECMO generally provides extracorporeal lung assist but does not support cardiac function.
In the past, ECLS systems were typically available only at major medical centers where specialized personnel (e.g., cardiothoracic surgeons and/or perfusionists) could be called upon to set up and operate the ECLS systems. Patients in the field, or those who presented at smaller hospital emergency departments, after suffering severe cardiac events or lung injuries would typically have to undergo (and survive) transport by vehicle (e.g., ground ambulance, helicopter, etc.) to a major medical center before having any possibility of ECLS treatment.
In recent years, efforts have been made to develop small, automated, simplified, portable ECLS systems that could be used to deliver ECLS treatment to patients at smaller hospitals and during transport, without the need for specialized personnel. Examples of such devices include those described in U.S. Pat. Nos. 7,367,540; 7,597,546; 7,682,327; 7,846,122; 8,529,488: 8,529,488; 8,187,214; 8,568,347; 8,951,220; 8,834,399; 8,882,693; 8,721,579 and 8,844,336 _ as well as United States Patent Application Publication Nos. US2014/0142491; US2014/0326678 US2015/0056601; US2015/0141897; US2015/0073335 and US2015/0082863, the entire disclosure of each such patent and patent application being expressly incorporated herein by reference.
Various embodiments described herein provide certain advances and improvements for portable ECLS systems aimed at enhancing their automated set up and/or operation as well as their mobility and use in transport vehicles (e.g., ambulances, helicopters, watercraft, etc.)
An ECLS system which comprises an extracorporeal life support device having an inlet connectable to the vasculature of a human or animal subject or harvested organ(s), an outlet also connectable to the vasculature of the subject or organ(s) and gas exchange apparatus operable to a) receive deoxygenated blood from the vasculature of the subject or organ(s) via the inlet, b) oxygenate the blood and c) infuse the oxygenated blood into the vasculature of the subject or organ(s) via the outlet is described herein. One or more of the following components may be provided separately or in combination with an ECLS system:
Methods for preparing, testing and using ECLS systems of the foregoing character, including a method for using a transport vehicle to transport a subject or harvested organ(s) from a first location to a second location while the subject or organ(s) is/are receiving treatment from the extracorporeal life support system are described herein.
In certain embodiments, a system or device comprising a conduit that is connectable to a subject's body, a controller, a pump and a sensor which senses pressure or flow within the conduit and transmits indicia of the sensed pressure or flow to the controller; wherein the pump creates negative pressure within the conduit to thereby withdraw a body fluid from the subject's body through the conduit, and the controller is programmed to determine when the sensed pressure or flow has fallen below a predetermined minimum and to thereafter issue control signals to the pump causing the pump to slow or stop until the sensed pressure or flow has risen above the predetermined minimum is provided. Such device or system may in some embodiments comprise an ECLS device or system in which the withdrawn body fluid is blood. However, this aspect or feature may be utilized in many other types of devices and systems including but not limited to apheresis systems and devices, autotransfusion systems and devices, hemodialysis systems and devices, hemofiltration systems and devices, plasmapheresis systems and devices and photopheresis systems and devices.
In other embodiments, there is provided an extracorporeal device having a conduit, a pump, a monitoring unit, a controller and a bubble sensor, wherein the pump circulates fluid through the conduit; the bubble sensor senses when a gas-liquid transition occurs within the conduit; the bubble sensor transmits a signal to at least the monitoring unit when a gas-liquid transition is sensed and the monitoring unit is programmed to issue an alarm or notification in response to the sensing of a gas-liquid transition by the bubble sensor; the controller is programmed to cause the system to take at least one remedial action in response to the sensing of a gas-liquid transition by the bubble sensor; and the controller is further programmed to perform a system test and a bubble sensor test while the conduit is initially being primed with fluid and/or during priming of the conduit with fluid and to provide a bubble sensor test failure indication and a system test failure indication; wherein the bubble sensor test failure indication is separate from the system test failure indication. In some embodiments a single gas-liquid transition occurs in the conduit during priming of the conduit and the bubble sensor test is timed to detect that single gas-liquid transition. In other embodiments, multiple gas liquid transitions may occur during priming of the conduit and the bubble sensor test is timed to detect at least one of those gas-liquid transitions. In some embodiments, gas may be volitionally introduced into the conduit (e.g., through a gas bubble injector) to create at least one gas-liquid transition for purposes of conducting the bubble sensor test. In at least some embodiments, the bubble sensor test and system test are performed sequentially as opposed to concurrently.
Still further aspects and details of the present invention will be understood upon reading of the detailed description and examples set forth herebelow.
The following detailed description and examples are provided for the purpose of non-exhaustively describing some, but not necessarily all, examples or embodiments, and shall not limit the scope of the invention in any way.
FIG. 2AAA is a top view of the transport accessory kit portion of the system of
The following detailed description and the accompanying drawings to which it refers are intended to describe some, but not necessarily all, examples or embodiments of the invention. The described embodiments are to be considered in all respects only as illustrative and not restrictive. The contents of this detailed description and the accompanying drawings do not limit the scope of the invention in any way.
The ECLS device 12 is useable for providing oxygenated blood to a human or animal subject or to vascularized organ(s) that have been explanted from a human or animal donor for subsequent transplantation (e.g., heart, lungs, heart & lungs, kidney, etc.). As described more fully below, the ECLS device includes, at minimum, an inlet which is connectable to vasculature of the subject or organ(s), an outlet which is also connectable to vasculature of the subject or organ(s) and gas exchange apparatus operable to oxygenate blood. In operation, the oxygenation apparatus receives deoxygenated blood from the subject or organ(s) via the inlet. The blood then becomes oxygenated by the oxygenation apparatus and the oxygenated blood then returns, via the outlet, into the vasculature of the subject or organ(s). In its most basic form, the ECLS device 12 is useable for VV-ECMO and other forms of extracorporeal lung assist. However, in many embodiments this ECLS device 10 may also include non-pulsatile or pulsatile blood pumping apparatus useable to propel or circulate the blood through the device 10 and through the vasculature of the subject or organ(s). The inclusion of such pumping apparatus will render the ECLS device 12 useable for full circulatory support procedures, such as VA-ECMO and CPB, as well. The ECLS device 12 may optionally include numerous other components, some examples of which are seen in the diagram of
In some embodiments, the system 10 may include a clinical accessory kit 16, an example of which is seen in
To facilitate its portability and transport, some embodiments of the system 10 may include a transport accessory kit 18, one example of which is seen in
As seen in
During transport it is usually important for the front of the ECLS device 12 to be facing the transport caregiver so that the caregiver when needed can easily access the controls. To avoid inadvertent placement of the ECLS device 12 in the inverted direction, the first belts or straps 40R, 40L may be color coded so as to be visually discernible from the second or rear belts or straps 41R, 41L. For example, the first belts 40R, 40L may be red and the second belts 41R, 41L may be black. In other embodiments, the first and/or second belts may include markings or other indicators to distinguish between the two types of belts. The ECLS device 12 itself may include markings or other indicators to ensure it is loaded into a transport vehicle in the proper orientation such that the front of the ECLS device 12 is facing the transport caregiver for ease of access to the controls.
In operation, as shown in
The ECLS device 12, with its attached belt assemblies 42R, 42L, may be loaded into the transport vehicle along with the subject (or the harvested organ(s)) receiving treatment from the ECLS device 12. The color coding of the anchoring belts 40R, 40L, 41R, 41L may be observed and referenced to ensure that the ECLS device 12 is loaded into the vehicle in the right direction (i.e., with its front side facing in the direction of the caregiver's seat or usual location within the vehicle). This typically will require the first belts 40R, 40L to be directed toward the front of the vehicle and the second belts 41R, 41L to be directed toward the rear of the vehicle. Alternatively, the ECLS device may be loaded into the transport vehicle in the proper direction and the belt assemblies 42R, 42L, may subsequently be attached to the ECLS device.
After the ECLS device has been loaded into the transport vehicle, the free ends of the fixed-length first belts 40R, 40L are attached to desired first anchoring locations which are adjacent to one another at a first region of the floor or other surface(s) of the vehicle and the free ends of the variable-length second anchoring belts 41R, 41L are anchored to desired second anchoring locations which are adjacent to one another at a second region of the floor or other surface(s) of the vehicle. Thereafter, the adjustment mechanisms 52R, 52L are used to cinch or shorten the variable-length second anchoring belts 41R, 41L thereby causing the belts to be sufficiently taught to firmly hold the ECLS device 12 in position within the vehicle. In many instances, the floor of the transport vehicle will be equipped with recessed tracks and the free ends of the belts 40R, 40L, 41R, 41L will be equipped with hardware that allows them to be inserted into and affixed to desired locations within those recessed tracks, thereby establishing the appropriate anchoring locations for holding the ECLS device 12 in its intended position. In certain embodiments, one or more first belts may be a variable-length belt and one or more second or rear belts may be a fixed-length belt. In other embodiments, any combination of fixed-length and variable-length belts may be utilized for the first and/or the second or rear belts.
Additionally, to facilitate use of the ECLS device 12 during transport the securement belt 19 may be removed from the transport accessory kit 18 and used to attach the remainder of the transport accessory kit 18 to a transport position on top of the ECLS device 12, as seen in
The appropriate power cord 38 is selected for use and removed from the transport kit case or bag 28 along with the DC power supply 36. One end of the selected power cord 38 is plugged into an electrical power outlet of the vehicle and the other end is plugged into an input jack of the DC power supply 36. The case or bag 28 may then be closed and the DC power supply placed on top of the case or bag 28 and held in place by straps 37 as shown in FIG. 2AAA. The power supply cord 35 of the DC power supply 36 is plugged into power input jack 39 of the ECLS device 12. Thus, the electrical current from an outlet in the transport vehicle is carried to the DC power supply 36 by a selected cord 38. The DC power supply then adjusts the voltage of the received power, as needed, and delivers the desired voltage of DC current through the power supply cord 35 to the ECLS device 12. The ECLS device 12 may be equipped with a battery backup to supply short term power to the device 12 during periods when it, is not receiving externally sourced power through either the AC power supply 21 (typically used in hospital) or DC power supply (typically used in the transport vehicle).
As explained above, ECLS devices 12 of varying type and complexity may be used in conjunction with the transport facilitating kits, belt assemblies and other components/methods described herein.
In typical operation, the components 60 are initially filled with a priming fluid. Priming line clamp 74 may be opened and a suitable priming fluid, such as sterile 0.9% NaCl solution (saline), may be introduced through the priming line 66 while the controller C operates the pumps 72, 86 in a manner that fills all components with the priming fluid. As discussed in more detail below, during or after the priming process the controller C may cycle through certain pre-treatment tests, such as a system or performance test and a bubble detector test. A critical aspect of the operation of the system is to avoid inadvertent introduction of clinically significant gas emboli (e.g., bubbles) through the outlet line and into the patient's vasculature.
When it is desired to commence the ECLS treatment, the inlet line 64 is connected to the patient's vasculature, typically via a cannula that has been advanced to a central venous location such as the patient's vena cava or right atrium. The outlet line 100 is also connected to the patient's vasculature, typically via a cannula that has been advanced to a central arterial location such as the patient's aorta. The controller C causes the blood pump 86 to circulate blood through the system components 60 and, in at least cases where the patient is in cardiac arrest or has clinically insufficient cardiac output, the blood pump 86 creates sufficient flow and pressure to also circulate blood through the patient's vasculature. Incoming de-oxygenated blood fills the reservoir 62 and any gas that collects at the top of the reservoir due to degassing of the blood or other causes is removed through vent line 71 with or without active pumping by the vent pump 72. Deoxygenated blood from the reservoir 62 then flows though lines 80 and 88 into oxygenator 92. In the oxygenator, gas exchange occurs through membranes such that carbon dioxide is removed from the blood and oxygen is added to the blood. The resultant oxygenated blood then flows through line 94, through filter 98 and though the outlet line 100. The filter 98 captures any solid embolic material, such as small or microscopic blood clots, that may be present in the blood. In routine operation, the oxygenated blood flows though the outlet line, the bubble detector detects no bubbles, the fast clamp 104 remains open and the oxygenated blood flows into the patient's vasculature as intended. However, if the bubble detector 102 senses a bubble, it immediately sends a bubble detection signal to the monitoring unit MU and the controller C. In response to that bubble detection signal, the monitoring unit MU causes a bubble detection error signal to appear at the top of the display screen of user interface 24 and the controller C promptly issues control signals to the fast clamp 104 and shunt clamp 108 causing the fast clamp 104 to close before the detected bubble has flowed past it and causing shunt clamp 108 to open. As a result, the flow of blood into the patient ceases and the blood (including the detected air bubble) is shunted through recirculation line 107, through inlet line 64 and back into the reservoir 62. This recirculation continues until the detected bubble 9 (and any others) have been separated from the blood in reservoir 62 and ultimately removed through vent line 71. After the recirculation has proceeded for a desired period of time with no further bubbles being detected by the bubble detector 102, the controller C causes shunt clamp 108 to close and fast clamp 104 to open, thereby returning the system to its normal mode of operation with deoxygenated blood being removed from the patient's vasculature and oxygenated blood being returned into the patient's vasculature. It is important that the fast clamp 104 comprise a clamping or valving device that closes rapidly enough after a bubble is sensed, by the bubble detector 10 to prevent, the detected bubble from passing into the subject's vasculature. One example of a fast closing clamp useable in this application is that described in U.S. Pat. No. 7,367,540 (Brieske) entitled Fast Closing Clamp, the entire disclosure of which is expressly incorporated herein by reference.
During operation, running of the blood pump 86 and/or vent pump 72 causes negative pressure in the inlet line 64 and positive pressure in the outlet line 100. Occasionally, the negative pressure in the inlet line 64 may become excessive, especially if the overall amount of fluid in the extracorporeal circuit is low and the blood pump 86 is running at high speed. Excessive negative pressure in the inlet line 64 can have adverse consequences. For example, it may cause the tip of the inlet blood cannula to become suction-attached to the wall of the blood vessel in which it is positioned, potentially causing damage to the blood vessel. Also, the blood reservoir 62 could run dry or damages (e.g., leaks) could occur in system components 60. To deal with this potential problem, an additional pressure sensor (not shown) could optionally be present on the inlet line 64 and the Controller C could optionally be programmed to receive and process signals from that inlet line pressure sensor and, if the negative pressure in the inlet line exceeds a predetermined maximum, to issue control signals to the blood pump 86 and/or vent pump 72 causing the pump(s) 86 and/or 72 to reduce speed. This controlled reduction in pump speed will cause the venous pressure to rise in the inlet line until it reaches a desired pressure. This may be accomplished by any suitable programming of the controller C. One manner in which the controller C may be programmed to accomplish this is by Pressure Feedback Control with the following parameters:
The derivative gain Kd has two values because the speed of the blood pump should decrease very fast if the venous line gets kinked but the speed should increase only slowly if the operator changes the set point. In this example, the pressure feedback control is only active if the set limit of the blood pump is higher than 1500 rpm. A warning message is displayed, such as via a user interface 24, if the pressure feedback control does momentarily reduce the speed of the blood pump 86. Also, in this example, the pressure feedback control can be switched on/off, such as via a sensor settings menu on a user interface 24 but the default setting will be with the pressure feedback control switched on.
Any suitable pressure limits may be used. For example, the default value for the set limit of the deoxygenated blood pressure in inlet line 64 may be −120 mmHg. An indicator, such as a bar indicator on a user interface 24, may change appearance (e.g., change from green/red to grey) if the pressure feedback control is switched off. Neither the controller C nor monitoring unit MU supervise the venous pressure if the pressure feedback control is switched off.
The optional pressure feedback control described herein is not only useable in ECLS systems, but may be incorporated into any extracorporeal device or system that draws a body fluid (e.g., blood) from the body of a patient and is equipped with a pump and a controller. Examples of non-ECLS types of devices in which this pressure feedback control feature may be incorporated include but are not limited to devises used for apheresis, autotransfusion, hemodialysis, hemofiltration, plasmapheresis, photopheresis, etc.
ECLS devices 12 may also include modifications to the controller software aimed at streamlining the initial start-up and testing of the ECLS device. Specifically, as mentioned above, the ECLS device may include a controller C, which may be programmed to perform self-tests of the overall system performance and bubble detector and to display information and error signals in ways that facilitate rapid location and correction of any detected problems.
In the example shown, the system also performs a pre-test of the bubble sensor 102. The bubble sensor 102 has two independent channels. Two analog signals are transmitted from the bubble sensor 102 and are converted to square root signals. One square root signal gets evaluated by the controller C and the other square root signal gets evaluated by the monitoring unit MU. During filling of the patient module air in line 100 is displaced by liquid being pumped through the system by the blood pump 86. For certain types of blood pumps, this may occur as a single air to liquid transition. For other types of blood pumps, multiple air-liquid transitions may occur (i.e., air-liquid-air-liquid-, etc.) before a constant flow of liquid is achieved through line 100. Both square root signals may transit from permanent high (air) to a periodic square root signal (liquid). Every conceivable single fault error, like sensor errors or a cable break, may prevent this transition from happening on at least one evaluation unit. Therefore the result of the bubble sensor activation is very reliable and the patient module can be regarded as bubble free,
In certain embodiments, the ECLS devices described herein may run for extended periods of time, e.g., up to 14 days, or longer than 14 days.
It is to be appreciated that, although the invention has been described hereabove with reference to certain examples or embodiments of the invention, various additions, deletions, alterations and modifications may be made to those described examples and embodiments without departing from the intended spirit and scope of the invention. For example, any elements, steps, members, components, compositions, reactants, parts or portions of one embodiment or example may be incorporated into or used with another embodiment or example, unless otherwise specified or unless doing so would render that embodiment or example unsuitable for its intended use. Also, where the steps of a method or process have been described or listed in a particular order, the order of such steps may be changed unless otherwise specified or unless doing so would render the method or process unsuitable for its intended purpose. Additionally, the elements, steps, members, components, compositions, reactants, parts or portions of any invention or example described herein may optionally exist or be utilized in the absence or substantial absence of any other element, step, member, component, composition, reactant, part or portion unless otherwise noted. All reasonable additions, deletions, modifications and alterations are to be considered equivalents of the described examples and embodiments and are to be included within the scope of the following claims.
This is a continuation of copending U.S. patent application Ser. No. 14/807,732 entitled Mobile Extracorporeal Life Support Systems and Related Methods filed Jul. 23, 2015, the entire disclosure of which is expressly incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| Parent | 14807732 | Jul 2015 | US |
| Child | 16375578 | US |
