DIALYSIS SYSTEM AND METHODS
Dialysis systems and methods are described which can include a number of features. The dialysis systems described can be to provide dialysis therapy to a patient in the comfort of their own home. The dialysis system can be configured to prepare purified water from a tap water source in real-time that is used for creating a dialysate solution. The dialysis systems described also include features that make it easy for a patient to self-administer therapy. For example, the dialysis systems include disposable cartridge and patient tubing sets that are easily installed on the dialysis system and automatically align the tubing set, sensors, venous drip chamber, and other features with the corresponding components on the dialysis system. Methods of use are also provided, including automated priming sequences, blood return sequences, and dynamic balancing methods for controlling a rate of fluid transfer during different types of dialysis, including hemodialysis, ultrafiltration, and hemodiafiltration.
This application is a division of U.S. application Ser. No. 16/550,042, filed Aug. 23, 2019, which application claims the benefit of U.S. Provisional Appln. No. 62/722,119, filed Aug. 23, 2018, titled “Dialysis System and Methods”, incorporated herein by reference in their entirety. This application is related to U.S. Pat. No. 9,504,777, titled “Dialysis System and Methods”, which is incorporated herein by reference.
INCORPORATION BY REFERENCEAll 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.
FIELDThis disclosure generally relates to dialysis systems. More specifically, this disclosure relates to dialysis systems that include many features that reduce the need for technician involvement in the preparation and administration of dialysis treatment.
BACKGROUNDThere are, at present, hundreds of thousands of patients in the United States with end-stage renal disease. Most of those require dialysis to survive. Many patients receive dialysis treatment at a dialysis center, which can place a demanding, restrictive and tiring schedule on a patient. Patients who receive in-center dialysis typically must travel to the center at least three times a week and sit in a chair for 3 to 4 hours each time while toxins and excess fluids are filtered from their blood. After the treatment, the patient must wait for the needle site to stop bleeding and blood pressure to return to normal, which requires even more time taken away from other, more fulfilling activities in their daily lives. Moreover, in-center patients must follow an uncompromising schedule as a typical center treats three to five shifts of patients in the course of a day. As a result, many people who dialyze three times a week complain of feeling exhausted for at least a few hours after a session.
Many dialysis systems on the market require significant input and attention from technicians prior to, during, and after the dialysis therapy. Before therapy, the technicians are often required to manually install patient blood tubing sets onto the dialysis system, connect the tubing sets to the patient, and to the dialyzer, and manually prime the tubing sets to remove air from the tubing set before therapy. During therapy, the technicians are typically required to monitor venous pressure and fluid levels, and administer boluses of saline and/or heparin to the patient. After therapy, the technicians are often required to return blood in the tubing set to the patient and drain the dialysis system. The inefficiencies of most dialysis systems and the need for significant technician involvement in the process make it even more difficult for patients to receive dialysis therapy away from large treatment centers.
Given the demanding nature of in-center dialysis, many patients have turned to home dialysis as an option. Home dialysis provides the patient with scheduling flexibility as it permits the patient to choose treatment times to fit other activities, such as going to work or caring for a family member. Unfortunately, current dialysis systems are generally unsuitable for use in a patient's home. One reason for this is that current systems are too large and bulky to fit within a typical home. Current dialysis systems are also energy-inefficient in that they use large amounts of energy to heat large amounts of water for proper use. Although some home dialysis systems are available, they generally are difficult to set up and use. As a result, most dialysis treatments for chronic patients are performed at dialysis centers.
Hemodialysis is also performed in the acute hospital setting, either for current dialysis patients who have been hospitalized, or for patients suffering from acute kidney injury. In these care settings, typically a hospital room, water of sufficient purity to create dialysate is not readily available. Therefore, hemodialysis machines in the acute setting rely on large quantities of pre-mixed dialysate, which are typically provided in large bags and are cumbersome for staff to handle. Alternatively, hemodialysis machines may be connected to a portable RO (reverse osmosis) machine, or other similar water purification device. This introduces another independent piece of equipment that must be managed, transported and disinfected.
SUMMARYA method of priming a tubing set and a dialyzer of a dialysis system is provided, comprising the steps of connecting an arterial line of a tubing set to a venous line of the tubing set to form a continuous loop in the tubing set, pumping air out of the tubing set with an air pump, pulling a flow of fluid from a fluid source into the tubing set with the air pump, operating a blood pump of the dialysis system in a forward operating mode to flow fluid from the fluid source into the tubing set in a first direction, and operating the blood pump in a reverse operating mode to flow fluid through the tubing set in a second direction opposite to the first direction.
In some examples, the pulling step further comprises pulling the fluid into the tubing set with the air pump until the fluid is detected by a first level sensor in a venous drip chamber.
In one embodiment, operating the blood pump in the forward operating mode further comprises operating the blood pump in a forward operating mode to flow fluid from the fluid source into the tubing set until the fluid is detected by a second level sensor in the venous drip chamber.
In some examples the method can include, after the pulling step, allowing a fluid level in the venous drip chamber to fall below the first level sensor.
In one embodiment, operating the blood pump in the forward operating mode further comprises operating the blood pump in a forward operating mode to flow fluid from the fluid source into the tubing set until the fluid is detected by the first level sensor in the venous drip chamber.
In another example, the method can comprise pumping air out of the tubing set with an air pump during the operating steps.
A dialysis system is also provided, comprising a fluid source, a patient tubing set fluidly coupled to the fluid source, the patient tubing set including a venous drip chamber, an air pump coupled to the venous drip chamber, the air pump being configured to pump air into or out of the venous drip chamber, a blood pump coupled to the patient tubing set, the blood pump being configured to flow fluid through the patient tubing set, at least one sensor coupled to the venous drip chamber and being configured to monitor a fluid level in the venous drip chamber, and an electronic controller in communication with the at least one sensor, the blood pump, and the air pump, the electronic controller being configured to control the air pump to pump air out of the tubing set, control the air pump to pull a flow of fluid from the fluid source into the patient tubing set, control the blood pump in a forward direction to flow fluid from the fluid source into the tubing set, and control the blood pump in a reverse direction to flow fluid through the tubing set.
A method of testing for leaks in a tubing set of a dialysis system is provided, comprising pressurizing a first segment of the tubing set, measuring a baseline pressure of the first segment tubing set, exposing a second segment of the tubing set to the pressurized first segment, measuring a pressure of the second segment of the tubing set, and comparing the measured pressure of the second segment to the baseline pressure of the tubing set to identify a leak in the second segment.
In some embodiments, exposing the second segment further comprises opening one or more pinch valves of the tubing set.
In one example, the method can include monitoring the pressure of the second segment for a pressure decay rate that exceeds a pressure decay threshold to identify a leak in the second segment.
A method of priming a tubing set of a dialysis system is provided, comprising removing the tubing set from a sterile shipping receptacle, attaching the tubing set to the dialysis system, priming the tubing set with a flow of fluid from the dialysis system to remove air from the tubing set, and draining the fluid from the tubing set into the shipping receptacle.
In some examples, the method further comprises attaching the shipping receptacle to the dialysis system.
In one embodiment, attaching the shipping receptacle further comprises engaging attachment features of the shipping receptacle with corresponding mechanical features on the dialysis system.
In some examples, the mechanical features on the dialysis system are angled with respect to another so as to impose a curvature on one or more surfaces of the shipping receptacle to enlarge an opening of the shipping receptacle.
In another embodiment, the method includes draining the fluid from the tubing set into the shipping receptacle through a junction fitting that connects an arterial line of the tubing set to a venous line of the tubing set.
A method of improving durability and operation of one or more displacement pumps is provided, comprising connecting one or more displacement pumps to a pump burn-in fixture to form a closed-loop fluidic path between the one or more displacement pumps and the pump burn-in fixture, increasing a temperature and pressure of fluid within the closed-loop fluidic path, operating the one or more displacement pumps to flow the fluid through the closed-loop fluidic path for a predetermined period of time to reduce surface imperfections internal to the one or more displacement pumps.
In one embodiment, the increasing step further comprises increasing the temperature and pressure of the fluid to levels that are above what the one or more displacement pumps encounter during normal operation.
In another embodiment, the method comprises increasing the temperature of the fluid above 25 deg C.
In another embodiment, the method comprises increasing the pressure of the fluid above 100 psi.
A pump burn-in fixture is provided, comprising a housing, a fluid source, one or more connection ports in or on the housing, one or more displacement pumps coupled to the one or more connection ports so as to form a closed-loop fluidic path between the fluid source, the one or more displacement pumps, and the one or more connection ports, a heating element configured to heat a fluid within the closed-loop fluidic path to an elevated temperature above a normal operating temperature of the one or more displacement pumps, and an electronic controller configured to control operation of the one or more displacement pumps with the elevated temperature fluid for a predetermined time to reduce surface imperfections internal to the one or more displacement pumps.
In some examples, a method of providing dialysis therapy to a patient is provided, comprising combining a dialysate concentrate and water with a dialysate system to produce a dialysate in real-time, providing a first flow of the dialysate through the dialysis system at a first dialysate flow rate, monitoring consumption of the dialysate concentrate by the dialysis system, determining if enough dialysate concentrate remains to complete the dialysis therapy at the first dialysate flow rate, and if there is not enough dialysate concentrate to complete the dialysis therapy at the first dialysate flow rate providing a second flow of the dialysate through the dialysis system at a second dialysate flow rate that allows for completion of the dialysis therapy.
In one embodiment, the method includes, before providing the second flow, calculating the second dialysate flow rate that allows for completion of the dialysis therapy.
In some embodiments, the dialysis system houses a finite supply of dialysate concentrate.
In one embodiment, the second dialysate flow rate is lower than the first dialysate flow rate.
In one example, the first dialysis flow rate is approximately 300 ml/min, and the second dialysis flow rate is approximately 100 ml/min.
In another embodiment, the determining step further comprises determining if enough dialysate concentrate remains based on the first dialysate flow rate, an amount of dialysate concentrate remaining, and a total treatment time.
In one example, the method further comprises maintaining a pressure within the dialysis system when the second flow of dialysate is provided.
The novel features of the invention are set forth with particularity in the claims that follow. A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description that sets forth illustrative embodiments, in which the principles of the invention are utilized, and the accompanying drawings of which:
This disclosure describes systems, devices, and methods related to dialysis therapy, including a dialysis system that is simple to use and includes automated features that eliminate or reduce the need for technician involvement during dialysis therapy. In some embodiments, the dialysis system can be a home dialysis system. Embodiments of the dialysis system can include various features that automate and improve the performance, efficiency, and safety of dialysis therapy.
In some embodiments, a dialysis system is described that can provide acute and chronic dialysis therapy to users. The system can include a water purification system configured to prepare water for use in dialysis therapy in real-time using available water sources, and a dialysis delivery system configured to prepare the dialysate for dialysis therapy. The dialysis system can include a disposable cartridge and tubing set for connecting to the user during dialysis therapy to retrieve and deliver blood from the user.
Dialysis system 100 can also include a cartridge 120 which can be removably coupled to the housing 106 of the system. The cartridge can include a patient tubing set attached to an organizer, which will be described in more detail below. The cartridge and tubing set, which can be sterile, disposable, one-time use components, are configured to connect to the dialysis system prior to therapy. This connection correctly aligns corresponding components between the cartridge, tubing set, and dialysis system prior to dialysis therapy. For example, the tubing set is automatically associated with one or more pumps (e.g., peristaltic pumps), clamps and sensors for drawing and pumping the user's blood through the tubing set when the cartridge is coupled to the dialysis system. The tubing set can also be associated with a saline source of the dialysis system for automated priming and air removal prior to therapy. In some embodiments, the cartridge and tubing set can be connected to a dialyzer 126 of the dialysis system. In other embodiments, the cartridge and tubing set can include a built-in dialyzer that is pre-attached to the tubing set. A user or patient can interact with the dialysis system via a user interface 113 including a display.
In
In some embodiments, the dialysis system 100 can also include a blood pressure cuff to provide for real-time monitoring of user blood pressure. The system (i.e., the electronic controller of the system) can be configured to monitor the blood pressure of the user during dialysis therapy. If the blood pressure of the user drops below a threshold value (e.g., a blood pressure threshold that indicates the user is hypotonic), the system can alert the user with a low blood pressure alarm and the dialysis therapy can be stopped. In the event that the user ignores a configurable number of low blood pressure alarms from the system, the system can be configured to automatically stop the dialysis therapy, at which point the system can inform the user that return of the user's blood (the blood that remains in the tubing set and dialyzer) back to the user's body is necessary. For example, the system can be pre-programmed to automatically stop therapy if the user ignores three low blood pressure alarms. In other embodiments, the system can give the user a bolus of saline to bring user fluid levels back up before resuming dialysis therapy. The amount of saline delivered to the patient can be tracked and accounted for during ultrafiltration fluid removal.
The dialysis delivery system 104 of
Dialysis can be performed in the dialysis delivery system 104 of the dialysis system 100 by passing a user's blood and dialysate through dialyzer 126. The dialysis system 100 can include an electronic controller configured to manage various flow control devices and features for regulating the flow of dialysate and blood to and from the dialyzer in order to achieve different types of dialysis, including hemodialysis, ultrafiltration, and hemodiafiltration.
The cartridge can be pressed into place on the front panel using these locator pegs 260 to ensure that all the features of the cartridge and tubing set line up and are installed properly with the corresponding features of the front panel 210. In some embodiments, the cartridge can be easily installed with a single hand, and closing the door of the system can seat the cartridge onto the system. As shown in
The pinch valves can be used for a number of functions before, during, and after dialysis therapy. The pinch valves 180a-d can be controlled by the electronic controller of the dialysis delivery system. Pinch valves 180a and 180b can be configured to control the flow of saline from a saline source (such as a saline bag) to the tubing set. In some embodiments, the pinch valves can be opened and the blood pump 213 can be operated to draw saline into the tubing set to remove air during a priming sequence, to flush impurities from the dialyzer before treatment, and to displace blood back to the user at the end of a treatment. The pinch valves 180a and 180b can also be used to deliver therapeutic boluses of saline to the user during therapy to maintain blood pressure or adjust electrolytes or fluid levels of the patient. In other embodiments, pumps such as peristaltic pumps may be configured to deliver therapeutic boluses of saline to the user.
Pinch valves 180c and 180d can be configured to close the arterial and venous lines of the tubing set that connect to the user. They can also be opened and closed multiple times before, during, and after treatment to facilitate actions such as tubing set pre-conditioning tubing to achieve proper compliance, priming, discarding of priming saline, blood return to the patient, and/or draining the dialyzer after treatment. In one embodiment, the system can incorporate information from venous air sensor 2161, arterial air sensor 216, or other air sensors in the system to close pinch valves 180c and 180d in the event that air bubbles are found in the lines, particularly in the venous line. In a further embodiment, the system can be configured to remove the detected air bubble(s) by reversing the operation of the blood pump to attempt to clear the air bubble(s) through the venous drip chamber.
Pinch valves 180a-d can also be actuated to perform a series of self-tests on the tubing set prior to each treatment. The tubing set can be pressurized with the blood pump, and the pressure can be held in the tubing set by closing the pinch valves. The arterial and venous pressure sensors can then be used to look for pressure decay in the tubing set.
In other embodiments, the system may comprise algorithmic features to protect itself from the failure of one or more of the venous level sensors 181a or 181b and still allow automatic level control. During treatment, the venous drip chamber 361 will be filled with blood. Detecting blood level in a drip chamber can be hindered by the tendency of blood to clot. These conditions can cause venous level sensors to not accurately sense the true level of the blood, causing the system to raise or lower the level incorrectly. This could lead to the fluid level to drop excessively, resulting in the air detector creating an alarm, or for the fluid level to raise excessively, which can cause blood to enter line 363 and foul venous transducer protector 371, hindering pressure readings.
In these embodiments, algorithmically improved automatic level control within the venous drip chamber can be maintained under the adverse conditions of clots and foam. The algorithmically improved automatic level control may utilize the ideal gas law to determine a set amount (“air budget”) of air for air pump 250 to either inject or remove to lower or raise the level, based on pressure detected within the chamber by venous pressure sensor 182a. This is possible because the geometric gas volumes of drip chamber and tubing connections are known. At high pressure, air is volumetrically compressed, and therefore the linear distance that a level within a substantially straight-walled chamber is raised or lowered will be smaller, for a given amount of air injected or removed. If the lower level sensor 181b detects air (or a clot forms that is sensed as air), the algorithm will begin raising the level. For a given venous pressure, the pump removes air up until the budget of air has been reached. The budget is determined to place the fluid level between the two level sensors, and is dynamically calculated using the ideal gas law as described above. In the event that the system is actually detecting air as opposed to a clot, the fluid rises and as a result the lower level 181b sensor will again detect fluid. At this point the algorithm resets the air budget available to be used the next time lower level sensor 181b detects air. If, however, lower level sensor 181b incorrectly detects air because it is confounded by a clot or other phenomena, it will still not detect air after the air pump removes air and raises the level. At this point, the algorithm begins controlling the level dynamically based on the pressure in the drip chamber. If the pressure increases, the gas space above the fluid compresses, causing the fluid level to rise. Conversely, if the pressure decreases, the gas space above the fluid expands, causing the fluid level to drop. A pressure increase or decrease will be detected by venous pressure sensor 182a. If a pressure change of sufficient magnitude is detected, the control algorithm uses the pressure/volume relationship of the ideal gas law and calculates an amount of air to add or remove using the air pump 250 to counteract the rise or drop in level. In some embodiments, the pressure change threshold is 20 mmHg. In some embodiments, the pressure change threshold is 50 mmHg. In some embodiments, the pressure change threshold is 100 mmHg. The amount of air to be removed or injected is calculated dynamically using the both the magnitude and change in venous pressure. In further embodiments, if pressure in the chamber is not changed, and the upper level sensor 181a senses fluid, the control algorithm will cause air pump 250 to inject a calculated budget of air into the chamber to drive the level down.
Referring to step 3010 again, in some instances the lower level sensor will still detect air, even after removing the budgeted air in step 3008. This could be caused, for example, by a clot or other phenomena in the venous drip chamber. In this event, at step 3014, a fault is detected and the dialysis system can switch to controlling the fluid level in the venous drip chamber based on measured pressure. At step 3016, the system will continuously measure the pressure within the venous drip chamber. If a pressure change above a pressure threshold is detected (e.g., a pressure change greater than 20-50 mmHg) then at steps 3018/3022, the system can determine an “air budget” based on the pressure change and pressure magnitude. At step 3020, the fluid level can be lowered by adding the budgeted air, and at step 3024, the fluid level can be raised by adding the budgeted air.
In other embodiments, the system may comprise a single analog or non-binary digital level sensor in the place of the two venous level sensors to detect the actual level within the drip chamber. The dialysis delivery system can then be configured to perform analogous adjustments as described above based on the level detected by this single sensor. The single sensor can comprise, for example, an ultrasonic, optical, or capacitive level sensor.
Still referring to
The tubing set can further include saline connections 353a and 353b to a saline solution, such as a saline bag, via a saline line 233. As shown in
Flow of fluid, such as blood, through the tubing set 122 will now be described. As described above, the blood pump that interacts with blood pump portion 2167 of tubing set 122 can be a peristaltic pump. The blood pump can operate in two modes of operation. One mode of operation can be a “forward” operating mode of the blood pump that can be used during dialysis therapy to move blood from the patient into the tubing set and back to the patient. Another mode of operation can be a “reverse” operating mode of the blood pump that can be used during a priming sequence to move saline through the tubing set. Fluid flows through the tubing set in the “forward” operating mode in a direction opposite to fluid flowing through the tubing set in the “reverse” operating mode. During dialysis therapy, blood can be drawn from the patient into the tubing set 122 through arterial line 230, due to the blood pump 213 interacting with the tubing set in the “forward” operating mode. Arterial pressure pod 355 can mate with a pressure sensor (arterial pressure sensor 182b of
As shown in
Priming and Prime Discard
Before treatment, the tubing set can be primed with saline to remove air from the line and prepare the system for dialysis therapy. During a priming sequence, the arterial and venous lines of the tubing set can be connected together to form a continuous loop in the tubing set.
During a priming sequence to remove air from the tubing set and prepare the system for therapy, saline can be drawn into the tubing set through saline connections 353a and/or 353b by activating the blood pump in the “forward” and “reverse” operating modes to cause the blood pump to interact with the tubing set and move saline into the tubing set from the saline source. When the pump operates in this “reverse” operating mode, the saline moves from the saline source into the tubing set and the blood-side of the dialyzer to fill the tubing set and the dialyzer with fluid and remove air from the tubing set via the venous drip chamber. In this “reverse” operating mode, saline flows through the tubing set in the opposite direction of blood flow during dialysis therapy. Thus, the saline flows through the venous drip chamber before flowing through the blood-side of the dialyzer. Air in the venous drip chamber can be monitored with the venous level sensors. Any air in the system can be pushed by the saline into the venous drip chamber.
When the venous level sensors no longer detect any changes to the fluid level in the venous drip chamber, or when air sensors no longer detect air circulating through the tubing set, then the tubing set is primed and ready for treatment. The blood pump can then be operated in the “forward” operating mode to move the saline in the other direction than described above and out of the tubing set. In the “forward” operating mode, the saline travels through the blood-side of the dialyzer before passing through the venous drip chamber and into the patient through venous line 232. In some embodiments, the saline used during the priming sequence is delivered into the patient at the start of dialysis therapy. The amount of saline delivered is tracked and accounted for during dialysis therapy depending on the patient's individual fluid removal requirements. In another embodiment, some or all of the saline is pumped or drained out of the tubing set prior to therapy.
To complete the priming sequence, dialysate can be pumped or moved through the dialysate-side of the dialyzer with a dialysate pump (described below). The dialysate is pumped through the dialysate-side of the dialyzer in the same direction that saline is pumped through the blood-side of the dialyzer. The direction of the saline and dialysate through the dialyzer can be in the direction of bottom to top through the dialyzer, which allows the bubbles to naturally purge through the top of the dialyzer. Thus, the priming sequence of the present disclosure can remove air from both the blood-side and dialysate-sides of the dialyzer without physically manipulating or “flipping” an orientation of the dialyzer, as is required by other conventional systems, since the priming sequence moves fluid through both sides of the dialyzer in the same direction.
During therapy, blood in the tubing set normally passes through the blood-side of the dialyzer in the top down direction. However, during priming, the blood pump can be operated in the “reverse” direction to push saline through the dialyzer in the bottom to top direction to more effectively remove air from the dialyzer. The unique configuration of the tubing set and venous drip chamber allows for the flow of saline in the “reverse” direction through the tubing set because fluid both enters and exits the venous drip chamber at connections on the bottom of the venous drip chamber. Conventional venous drip chambers, in which tubing connections are made at the top and bottom of the venous drip chamber, only allow for fluid flow through the venous drip chamber in one direction. The unique configuration of this disclosure allows for priming of both the blood and dialysate sides of the dialyzer without having to physically flip the dialyzer. Any air generated in the venous drip chamber during priming can be removed by either venting out of the system, or pumping out of the system. In one embodiment, the pinch valves of the system can be periodically actuated to open and close the saline lines of the tubing set depending on the timing of the priming sequence to “bang” bubbles loose in the dialyzer. For example, the pinch valves can be opened and closed every 4-8 seconds to create a pulsing effect of the saline in the lines.
Next, as shown in
Next, as shown in
Referring now to
Next, as shown in
After a priming sequence when saline is in the tubing set, the system can further run self-tests to check for leaks in the tubing set. In one embodiment, the pinch valve on the venous line can be closed with the blood pump running, and air can be pumped into the venous drip chamber. Next, the arterial pinch valve can be closed, and the venous pinch valve can be opened, and the system can check for pressure stabilization. If there is no pressure decay, it can be confirmed that there are no leaks in the system.
In one embodiment, the dialyzer can be flushed prior to beginning dialysis therapy with a patient. The system can be configured to flush the dialyzer with up to 500 ml of saline. Upon completion of the priming procedure, the used priming fluid may be discarded. Typically there have been two different types of destinations for the used priming fluid: 1) a receptacle or fluidic connection that leads to the inside the dialysis machine itself, which routes to a drain, or 2) an external receptacle, which is typically reusable and manually dumped into a sink and cleaned. Both of these approaches present challenges in terms of maintaining cleanliness and disinfection of surfaces, either internal or external. Additionally, often times the open end(s) of the tubing set that are used to interface with the disposal receptacle are the same ends which will later be connected to the patient during treatment. Infection control is of critical importance while performing hemodialysis treatments and setups, and exposing the open ends of the tubing set during the prime discard procedure presents an infection risk, especially since the tubing set must be handled by a user to position it correctly for discarding the fluid.
As described above, the tubing set is filled with saline during the priming sequence. During this priming, the arterial and venous lines are attached to each other with union joint 256 as illustrated in
In another prime discard embodiment, the sterile packaging for the cartridge and tubing set can also be used as a discard receptacle after priming. The cartridge and tubing set is supplied sterile, and is typically packaged in a disposable pouch which serves as a sterile barrier. In a first configuration, shown in
The sterile receptacle 1900 can include mounting features 1902, shown in
Additionally, the dialysis system can include mounting features to hold the union joint in place on the dialysis system relative to the mounted receptacle. The mounting features on the dialysis system may include snap fit features, spring grip features, semicircular cup features, hole and shaft features, or any other similar mounting features. For example, the receptacle may include linear slits cut into one of the sheets which interface with linear extrusions which are hook-shaped in cross section located on the dialysis system. In one specific example, these hook-shaped features may be mounted on surfaces which are not co-planar with one another but meet at a slight angle, such that the hook-shaped features impose a slight curvature on of the sheets on the pouch. This would force the other sheet that is welded to the first sheet at its edges into an opposite curvature, enlarging the opening between the sheets at the top of the pouch.
In some embodiments, the sterile receptacle may be constructed of two thin sheets welded together at the edges, which may be opened by de-laminating the weld at one edge of the pouch. If a user were to completely delaminate both sheets, the pouch could not be used as a prime discard receptacle because it would not be able to hold any liquid volume.
An alternative embodiment, as shown in
In yet another example as shown in
In another embodiment, the pre-attached receptacle interfaces with a prime discard valve that is controlled by the dialysis system. In this embodiment, priming is performed as described above, and upon completion of priming the dialysis system can control the prime discard valve to route the priming saline into the pre-attached receptacle. Alternatively, the dialysis system itself could include a discard receptacle, and the tubing set could be configured to automatically discard into the discard receptacle via the prime discard valve at the completion of a priming sequence. In some embodiments, the connection between the discard receptacle on the dialysis system and the blood tubing set is automatically made when the blood tubing set is mounted onto the system, as is enabled by the organizer configuration described above. In these embodiments, flow from the blood tubing set into the discard receptacle can be controlled automatically by a pinch valve that engages the tubing of the blood tubing set connector. In further embodiments, the discard receptacle of the dialysis system is disinfected by the system's automatic disinfection sequences.
At the completion of a dialysis treatment, blood still remains inside the tubing set. The blood pump 213 can be controlled to draw saline into the tubing set to push the remaining blood back into the patient. This blood return mechanism can be highly controlled by the controller and blood pump of the system. For example, during dialysis therapy and blood return, the controller of the system can monitor and track the exact number of revolutions made by the blood pump when the pinch valves that control saline administration are open to know exactly how much saline has been pushed into the tubing set. The blood pump can then be stopped or de-activated when the desired volume of saline is drawn into the tubing set. This allows the system to know exactly how much saline has been used, and how much remains in the saline source or bag. At the end of the dialysis therapy, the amount of blood in the tubing set is known (typically around 250 ml), so the system can precisely meter the correct amount of saline into the tubing set to push the blood back into the user. The anticipated amount of saline to use for blood return (typically 300-600 ml depending on the varying degree of thoroughness of the blood return) can be integrated into the overall fluid removal target for ultrafiltration so that after the blood return the patient target weight is attained. If the needed amount of saline does not remain in the saline source prior to blood return, the system can alert the user that the saline source needs to be refilled or replaced.
In one embodiment, the dialyzer can be flushed prior to beginning dialysis therapy with a patient. In some cases, clinics ignore this labeling and do not flush the dialyzer. The system can be configured to flush the dialyzer with up to 1000 ml of saline.
The system can also automatically drain any fluid out of the dialyzer after a dialysis treatment. In one embodiment, the blood pump can be run in the reverse direction with the venous line clamped to pull fluid from the dialysate chamber of the dialyzer through the dialyzer microtube walls against gravity through the dialyzer and into the saline source or bag.
Referring to
The water can then flow through one or more carbon filters 110 (shown as CF-1 and CF-2) configured to filter materials such as organic chemicals, chlorine, and chloramines from the water. For example, the carbon filters 110 can include granulated carbon block cartridges having 10-micron filters. The carbon filters can be connected in series with a chlorine sample port 195 positioned in the flow path between the carbon filters. The chlorine sample port can provide a user with access (such as through the front panel of the system) to the flowing water such as for quality control purposes to ensure the total chlorine concentration level of the water is below a certain threshold (e.g., below 0.1 ppm). Additionally, a post-carbon pressure sensor 2179 can be placed after the carbon filter(s) to monitor the fluid pressure in the line after the sediment and carbon filtration. As is also shown in
As shown in
The pressure created by the RO feed pump and a RO concentrate flow restrictor 2181 can control the flow rate of waste to the drain. To ensure that the restriction does not become fouled or plugged, the flow through the RO concentrate flow restrictor can be periodically reversed by actuating valves 180. In addition, to improve filter life and performance, recirculation pumps can be used to increase fluid flow rate in the RO filter housings. This increase in flow rate can serve to reduce a boundary layer effect that can occur near the surface of RO filters where water near the filter membrane may not flow. The boundary layer can create an area with a higher concentration of total dissolved solids that can build up over the surface of the RO filter and may collect and foul the RO filter.
The RO filtration subsystem can include on or more conductivity sensors 196 configured to measure the conductivity of water flowing through the subsystem to measure solute clearance, or per, pressure sensors 198 configured to monitor fluid pressures, and air separators 187 configured to separate and remove air and air bubbles from the fluid. Additionally, the RO filtration subsystem can include a variety of valves 180, including check valves, and fluid pumps for controlling flow through the RO filters and on to the pasteurization subsystem, back through the RO filtration subsystem for further filtration, or to the drain. Water can flow from the RO filtration subsystem to the pasteurization subsystem, described next.
In some embodiments, the HEX 145 can heat water received by the pasteurization subsystem to a temperature of approximately 148 degrees Celsius. The heated water can be held in a dwell chamber of the HEX for a time period sufficient to eliminate and kill bacteria and denature endotoxins. Endotoxins can be described as the carcasses of dead bacteria, characterized by long lipid chains. During water and dialysate preparation, endotoxins can be monitored along with bacteria to judge the purity of the dialysate. Endotoxins in dialysate can cause an undesirable inflammatory response in users. Therefore, it is desirable to minimize the levels of endotoxin in the dialysate. Endotoxins are not readily trapped by the pore size of typical ultrafilters. Instead, the endotoxins are stopped by ultrafilters through surface adsorption which can become saturated with endotoxins to the point that additional endotoxin will start to pass through. Heating endotoxins in superheated water to temperatures as low as 130 degrees C. have been demonstrated to denature endotoxins but the required dwell time is very long (many minutes). At these elevated temperatures, where the water remains in the liquid phase, water which is typically considered a polar solvent and begins to behave like a non-polar solvent to denature the lipid chains of the endotoxin. As the temperature increases to 220 degrees C. or higher, the denaturing of endotoxins occurs in seconds. The HEX of the present disclosure can run at 220 degrees C. or higher while maintaining a pressure (approximately 340 psi for 220 degrees C., but the HEX can withstand pressures of over 1000 psi) that keeps the water in liquid form. In one embodiment, a preferred temperature and pressure range of the HEX is 180-220 degrees C. and 145-340 psi. The water can then be cooled as it exits the dwell chamber. The HEX 145 is a self-contained counterflow heat exchanger that simultaneously heats incoming water and cools outgoing water to reduce energy consumption.
The pasteurization subsystem can include a HEX pump 193 configured to maintain a fluid pressure in the fluid line, to prevent the water from boiling. After the water passes through the HEX 145, a water regulator 197 can reduce the pressure of the water for use in the dialysis delivery system. One or more pressure sensors 182 or temperature sensors 184 can be included for measuring pressure and temperature, respectively, of the water flowing through the pasteurization subsystem. Furthermore, an air separator 187 can further remove air and air bubbles from the water. In one embodiment, a flow restrictor 189 and valve 180 can be used to limit water dumped to the drain when the HEX 145 is heating up. Once the water has passed through the pasteurization subsystem, it has traveled through the entire water purification system and is clean and pure enough to be used in dialysate preparation and delivery by the dialysis delivery system.
After de-aeration and subsequent cooling with the heater 220 to approximately body temperature, acid and bicarbonate concentrates can be volumetrically proportioned into the fluid path by way of concentrate pumps 223 in order to reach the desired dialysate composition. The water and concentrates can be mixed in a series of mixing chambers 224 that utilize a time delay or volumetric mixing instead of in-line mixing to smooth the introduction of fluids.
Smart Flow
During dialysis therapy, the user has the ability to change the dialysate flow rate from the dialysis system to suit the patient's prescription. Oftentimes, this setting is toggled once at the beginning of the treatment, and the flow rate is held throughout the entire treatment. Dialysis providers typically set the maximum dialysate flow rate to maximize the waste clearances, although studies show that clearance rates witness diminishing returns at higher flow rates. As most dialysis machines run on a central water loop, with central dialysis concentrates, there is typically little incentive to conserve dialysate during treatment.
The dialysis system of the present disclosure is unique as it uses a finite volume of concentrates to proportion dialysate on-the-fly, as described above. In one embodiment, the dialysis system of the present disclosure can conserve dialysate concentrate by actively monitoring the amount of dialysate used during therapy and modulating the dialysate flow rate to lower the consumption of acid and bicarbonate concentrates. The ratio of pressures across the dialyzer (e.g., patient venous pressure, dialysate pressure, etc.) can be automatically maintained by the dialysis system while the dialysate flow is lowered, ensuring the appropriate ultrafiltration profile.
Depending on treatment goal, running at a lower dialysate flow rate may be appropriate. For example, running a longer treatment at lower dialysate and blood flow rates has a gentler physiological effect on the body, and may be appropriate for patients dialyzing at night or who have compromised physiology. The onboard monitoring of dialysate consumption, and real-time dialysate flow rate control, allows for laissez faire dialysis treatments while retaining appropriate device efficiency.
If, however, the “smartflow” option is enabled at step 2004, then at step 2008 of flowchart 2000 the treatment can initially begin at a selected dialysate flow rate (e.g., 300 ml/min). The dialysis system can monitor dialysate consumption in real-time, and at step 2010 of flowchart 2000, the dialysis system can calculate and determine if the amount of remaining dialysate (or dialysate concentrates) are enough to complete the scheduled treatment. Step 2010 can be performed constantly during treatment, or can be performed and repeated at scheduled intervals during the therapy (e.g., every 30 seconds, every minute, every 5 minutes, etc.).
If there is enough dialysate remaining to complete the treatment at step 2010, then at step 2012 the dialysis system can complete the treatment at the original dialysate flow rate (e.g., 300 ml/min). If, however, there is not enough dialysate to complete the treatment, then at step 2014 of flowchart 2000, the dialysate flow rate can be reduced to a flow rate that permits completion of treatment with the amount of dialysate on hand (e.g., a flow rate of 100 ml/min). The dialysis system can be configured to maintain a pressure within the dialysis system when the flow rate is reduced. The therapy can continue at the flow rates of steps 2006, 2012, or 2014 until completion of the treatment at step 2016.
The smartflow calculations of the dialysis system are determined by comparing the potential dialysate remaining in the concentrate bottles to the dialysate consumed by a single dialysis treatment. As the dialysis system operates from dialysate concentrates of fixed volume, the dialysis system can, in real-time, calculate the amount of concentrates consumed and adjust the dialysate flow rate accordingly to conserve concentrate fluids. The calculation of dialysate used versus dialysate remaining is determined as following:
The total dialysate needed for a treatment is calculated by multiplying the sum of the concentrate and water flow rates by the total treatment time.
Total Dialysate Needed=(Acid Flow Rate+Bicarb Flow Rate+Water Flow Rate)*Total Treatment Time (eq. 1)
Typically, bicarbonate concentrate is the limiting factor, as it has a higher consumption rate than acid concentrate. As such, the total dialysate available in any given treatment is dependent on bicarbonate volume and flow rate:
Amount of Available Time For Bicarbonate=Total Bicarb Volume/Bicarb Flow Rate (eq. 2)
Dialysate Available=Dialysate Flow Rate*Amount of Available Time For Bicarbonate (eq. 3)
The amount of dialysate consumed during a treatment is calculated real-time.
Dialysate Used=Dialysate Flow Rate*Elapsed Time in Treatment (eq. 4)
From here, the dialysis system actively calculates the dialysate flow rate necessary to completely deplete the concentrates, thus completing the treatment without user intervention.
Time Remaining in Treatment=Total Treatment Time−Elapsed Time in Treatment (eq. 5)
Dialysate Flow Rate Necessary=(Dialysate Available−Dialysate Used)/Time Remaining in Treatment (eq. 6)
The Dialysate Flow Rate Necessary (eq. 6) for treatment completion will drop from the initial flow rate over the course of a treatment. If the calculated Dialysate Flow Rate Necessary falls to a predetermined set point, the system will immediately modulate the flow rate to the appropriate, lower, dialysate flow rate in order to complete the treatment.
In one embodiment, the concentrate pumps can run at an elevated rate to push out any air bubbles in the pumping mechanism (e.g., can run at upwards of 30 ml/min compared to −7 ml/min during normal operation). Once the dialysate is mixed, a dialysate pump 226 can control the flow of dialysate through the dialysis delivery system. The mixing subsystem 162 can include various pressure sensors 182, temperature sensors 184, and conductivity sensors 196 to monitor the fluid during the dialysate preparation. The conductivity sensors can be used to measure the fluid ionic properties to confirm that the composition is correct.
The flow path within the dialysate delivery system can include one or more bypass or circulation routes that permit circulation of cleaning and/or sterilization fluid through the flow path. The circulation route may be an open flow loop wherein fluid flowing through the circulation route can be dischargeable from the system after use. In another embodiment, the circulation route may be a closed flow loop wherein fluid flowing through the circulation route is not dischargeable from the system.
A method of providing dialysis therapy to a patient is provided, comprising combining a dialysate concentrate and water with a dialysate system to produce a dialysate on-demand, providing a first flow of the dialysate through the dialysis system at a first dialysate flow rate, monitoring consumption of the dialysate concentrate by the dialysis system, determining if enough dialysate concentrate remains to complete the dialysis therapy at the first dialysate flow rate, and if there is not enough dialysate concentrate to complete the dialysis therapy at the first dialysate flow rate, calculating a second dialysate flow rate that allows for completion of the dialysis therapy, and providing a second flow of the dialysate through the dialysis system at the second dialysate flow rate.
In some examples, the dialysis system houses a finite supply of dialysate concentrate. In another example, the second dialysate flow rate is lower than the first dialysate flow rate. In one example, the first dialysis flow rate is approximately 300 ml/min, and the second dialysis flow rate is approximately 100 ml/min.
In one example, the determining step further comprises determining if enough dialysate concentrate remains based on the first dialysate flow rate, an amount of dialysate concentrate remaining, and a total treatment time. In one example, the method further includes maintaining a pressure within the dialysis system when the second flow of dialysate is provided.
The blood circuit subsystem can also include a venting circuit 248 adapted to automatically control the fluid level in venous level chamber 361, as described above. The venting circuit can include a bi-directional peristaltic pump 250. The venous pressure sensor 182a of the system can also be located in the venting circuit 248. During dialysis therapy, the venous level sensor(s) 181 can monitor a fluid level of blood in the venous drip chamber 361. The electronic controller can receive the fluid level information from the sensor(s) and automatically maintaining the fluid level of the blood in the venous drip chamber by pumping or venting air out of the venous drip chamber with bi-directional peristaltic pump 250 and/or venting valves 252 if sensor(s) detect the fluid level dropping below a lower threshold, and by pumping air into the venous drip chamber with bi-directional peristaltic pump 250 if the sensor(s) detect the fluid level rising above an upper threshold.
Still referring to
The dialysate pump and used dialysate pump described above can be part of an electronic circuit in communication with the electronic controller of the dialysis system to achieve a controlled ultrafiltration rate, and can also be adjusted to precisely control the addition or removal of fluid to or from the patient.
The dialysate pump and used dialysate pump can be controlled with a high degree of precision to achieve dynamic balancing, periodic balancing, and continuous correction. Referring to
To calibrate the flow of the system, the system can be controlled to enter a bypass mode in which valves 177 are actuated to prevent dialysate flow through the dialyzer. This isolates the patient tubing set on the blood side of the dialyzer from the dialysate flow and creates a closed system for dialysate flow that will not allow ultrafiltration. Whenever the system is in bypass the used dialysate pump can be servoed to maintain constant pressure as measured by pressure sensor 182c, which is positioned between the dialysate pump 226 and used dialysate pump 227. The pump speed of the used dialysate can be adjusted while the pump speed of the dialysate pump is maintained at a constant speed until the pressure measured by pressure sensor 182c stabilizes. Once the pressure is stabilized, the pump speed of the used dialysate pump vs the pump speed of the dialysate pump can be recorded as the pump speed ratio that results in zero ultrafiltration. When the systems exits bypass and returns to dialysis therapy, the used dialysate pump speed can be adjusted based on the desired ultrafiltration rate.
When dialyzer is bypassed, pressure measurements of the dialysate can be made independent of influences or pressures from the blood-side of the dialyzer (e.g., isolated from the blood tubing set). When the dialysate and used dialysate pumps operate at the same rate there is no pressure change at pressure sensor 182c positioned between the two pumps, so there is no flow imbalance between the pumps. However, if the dialysate and used dialysate pumps operate at different rates then a flow imbalance is created between the pumps, and a pressure change representing this flow imbalance can be measured at pressure sensor 182c. In some embodiments, the flow imbalance can be controlled based on the pump strokes of the respective pumps. In other embodiments, the flow imbalance can be controlled based on lookup tables that determine the optimal pump speeds based on the measured venous pressure. The electronic controller of the system can be configured to automatically control the flow of fluid across the dialyzer (i.e., ultrafiltration) by adjusting a pump speed of the used dialysate pump 227 with respect to dialysate pump 226 (or alternatively, of the dialysate pump 226 with respect to used dialysate pump 227) to create a flow imbalance between the dialysate-side and blood-side of the dialyzer. When a flow imbalance is created on the dialysate-side of the dialyzer by operating the pumps 226 and 227 at different speeds, then fluid can flow across the dialyzer membranes from the blood-side to the dialysate-side, and vice versa, to equalize that flow imbalance.
The pump speeds of the dialysate pump 226 and used dialysate pump 227 can be locked in by the system based on a desired rate of ultrafiltration, and valve 180 can be opened for normal operation during dialysis therapy. During therapy, the system can continue to monitor venous pressure on user side at pressure sensor 182a. If the venous pressure changes (e.g., greater than 30 mm-Hg mercury in change), the system can be configured to automatically rebalance the pumps with the same technique described above. This allows the pumps to be balanced to achieve the desired amount of fluid transfer through the dialyzer, or alternatively, to achieve no fluid transfer through the dialyzer. In one specific embodiment, the system can detect changes in the venous pressure of the user and automatically adjust the speed of the used dialysate pump 227 based on a look-up table of speeds against venous pressure to maintain ultrafiltration balance in the user. Once the system has been calibrated, the used dialysate pump speed can be modulated to adjust the rate of fluid removal from the patient. In some embodiments, a pump speed of the used dialysate pump can be alternatively increased or decreased relative to the dialysate pump to enable hemodiafiltration (e.g., pushing/pulling fluid onto the patient).
In some embodiments, there are two phases of operation of the dialysate pump and the used dialysate pump. In the first phase of operation, the speed of the used dialysate pump is greater than the speed of the dialysate pump, resulting in net fluid flux from the blood side of the dialyzer and into the dialysate side of the dialyzer. The speed differential may be set such that fluid is removed from the patient's blood at a rate that is physiologically tolerable over a short duration, perhaps up to a rate of 100 mL/min. To achieve this, for example, the dialysate pump may be set to run at 300 mL/min, and the used dialysate pump may be set to run at 400 mL/min. In this phase, convective clearance of solutes is increased. However, because of a limited volume of fluid in the patient's circulation, indefinite application of this first phase of operation is not sustainable, as it would hemo-concentrate the blood in the dialyzer. In the second phase of operation, the speed of the dialysate pump is greater than the speed of the used dialysate pump, resulting in net fluid flux from the dialysate side of the dialyzer into the blood side of the dialyzer. In this second phase, at least some of the fluid removed from the patient's circulation during the first phase is replaced, allowing the first phase to be repeated. Convective clearance of solutes is reduced during the second phase, although diffusive clearance would still take place. Current systems that are used for hemodiafiltration typically inject replacement fluid into the patient's extracorporeal circuit directly, which requires extremely high standards for microbiological purity. These replacement fluids are typically pre-manufactured and provided in large bags, which are cumbersome to handle and add considerable cost. In the disclosed invention, the replacement fluid is produced on-line and is additionally filtered by the dialyzer before coming into contact with the patient's blood, obviating the need for pre-manufactured fluids and direct connections into the patient's extracorporeal circuit. In some embodiments, the duration and/or net fluid flux of the first phase of the second phase are equal. In some embodiments, the duration and/or net fluid flux of the first phase and the second phase are not equal. In further embodiments, the net fluid flux produced by the two phases sum up to equal the total fluid removal goal during the treatment. In further embodiments, the invention comprises a plurality of any number of operating phases with varying durations and/or net fluid fluxes, or a continuum thereof.
Pump Burn-in
The dialysis system described herein includes a number of pumps, including pumps that may interact directly with fluids such as dialysate, saline, or blood that are delivered to the patient. A vane pump can include internal graphite components whereas the gear pump can include of PEEK materials which shed off during normal pump operations. These particles may enter components such as filters or regulators of the dialysis system which may result in premature failures. By design, vane pumps and gear pumps operate under a positive displacement principle, where internal pump components will grind against one another to move fluid. As such, surface imperfections on the internal pump components will continue to shed over use. Under high temperature and/or pressure conditions, the stress on the internal pump components will increase, thereby increasing the amount of shedding observed. This disclosure provides a vane and gear pump burn in process designed to reduce particulate shedding amounts during dialysis system operation.
The intent of a burn-in process is to remove loose particulates present in the pumps by running the pumps at elevated temperatures and/or elevated pressures during the first few hours of the pumps lifetime. For example, the process can include running the pumps at temperatures and/or pressures that are higher than the temperatures and pressures that the pumps will encounter during normal operation. In running these pumps in an extreme condition, the surface imperfections on the internal pump will be sanded down, thus making a more flush interface between components. Smooth to smooth surface contact on internal vanes and gears yields fewer particulates shed, thereby preventing premature failure of other components in the system. In one example, running these pumps at 70 deg C. and 100 psi for 8 hours maximizes the amount of infant shedding, thus leading to reduced shedding during normal operation modes (25 deg C. and 100 psi).
A method of improving durability and operation of one or more displacement pumps, can comprise connecting one or more displacement pumps to a pump burn-in fixture to form a closed-loop fluidic path between the one or more displacement pumps and the pump burn-in fixture, increasing a temperature and pressure of fluid within the closed-loop fluidic path, and operating the one or more displacement pumps to flow the fluid through the closed-loop fluidic path for a predetermined period of time to reduce surface imperfections internal to the one or more displacement pumps.
In some embodiments, the increasing step further comprises increasing the temperature and pressure of the fluid to levels that are above what the one or more displacement pumps encounter during normal operation. For example, this can include increasing the temperature of the fluid above 25 deg C. In another example, the method can include increasing the pressure of the fluid above 100 psi.
As described above, the water purification system and the dialysate delivery system can both include a variety of pumps, valves, sensors, air separators, air sensors, heat exchangers, and other safety features. All of these features can be controlled electronically and automatically by the electronic controller of the dialysis system.
Automated Conductivity Calibration
The dialysis system described herein includes a number of conductivity sensors to monitor the quality of the incoming water, the effectiveness of the water purification system and to ensure proper proportioning of the dialysate fluid generated. As with many sensors, it can necessary to perform periodic re-calibration of these sensors to ensure accuracy. Typically, each conductivity sensor is calibrated in isolation, where the fluid connections to the rest of the system on either side of the sensor are broken, and then re-connected to a source of conductivity calibration fluid and a calibrated external conductivity meter. This conductivity calibration fluid which has a known conductivity, is passed through the sensor, and additionally verified by the external conductivity meter, which verifies that the sensor under test is properly calibrated, or allows for adjustment of its calibration constants if it is out of calibration. The type of calibration fluid used may be different for each sensor, as the conductivity range it is meant to read could be different from other conductivity sensors in the system. Disclosed herein is a method to perform automated calibration of all the conductivity sensors within the system that does not require breaking the fluidic path. In some embodiments, the automatic conductivity calibration method comprises connecting a calibration fluid concentrate to the acid or bicarbonate pumps. Optionally, an external conductivity meter may be connected to the fluidic circuit of the system, for example using the inlet and outlet connectors that are used to connect to a dialyzer. Using the proportioning pumps, the system will mix the calibration fluid concentrate and purified water produced by the water purification module to produce a calibration fluid of a nominally known conductivity. In this state, the fluidic path of the system is a single-pass flow through, where the mixed fluid is sent to drain. Once the conductivity of the mixed calibration fluid has stabilized, the proportioning pump(s) can be stopped, and the fluidic path of the system is automatically reconfigured to recirculate the fluid instead of sending it to drain. The recirculation path of the system can be configured to include all the conductivity sensors within the system, including the optional external conductivity meter, which will now all be exposed to the same recirculating fluid. Measurements from any or all of the conductivity sensors can then be compared with other sensors, including the optional external conductivity sensor, and calibration constants may be adjusted as needed. In some embodiments, the this process can be automatically repeated multiple times, with different mixing ratios of calibration fluid producing final mixed fluids of different conductivities. As such a multi-point calibration curve can be generated. Furthermore, conductivity sensors in different portions of the fluid path typically sense fluids of different conductivity ranges. The calibration fluid can be sequentially proportioned to cover the different typical operating ranges of the different conductivity sensors. Calibration of the each of the conductivity sensors can be more heavily weighted, or done exclusively, with calibration fluid representative of its native operating range.
Claims
1. A method of testing for leaks in a tubing set of a dialysis system, comprising:
- pressurizing a first segment of the tubing set;
- measuring a baseline pressure of the first segment tubing set;
- exposing a second segment of the tubing set to the pressurized first segment;
- measuring a pressure of the second segment of the tubing set; and
- comparing the measured pressure of the second segment to the baseline pressure of the tubing set to identify a leak in the second segment.
2. The method of claim 1, wherein exposing the second segment further comprises opening one or more pinch valves of the tubing set.
3. The method of claim 1, further comprising monitoring the pressure of the second segment for a pressure decay rate that exceeds a pressure decay threshold to identify a leak in the second segment.
Type: Application
Filed: Apr 29, 2021
Publication Date: Aug 12, 2021
Inventors: Michael Edward HOGARD (Odessa, FL), Dean HU (San Leandro, CA), Shih-Paul CHEN (Los Altos, CA), James RITSON (San Jose, CA), Gopi K. LINGAM (San Jose, CA), Peter Velasco OBICO (Santa Clara, CA), James R. CURTIS (Portland, OR), Steven M. MILLER (Palo Alto, CA)
Application Number: 17/244,672
