US20010021817A1 - Methods, systems, and kits for the extracorporeal processing of blood - Google Patents

Methods, systems, and kits for the extracorporeal processing of blood Download PDF

Info

Publication number
US20010021817A1
US20010021817A1 US09862207 US86220701A US2001021817A1 US 20010021817 A1 US20010021817 A1 US 20010021817A1 US 09862207 US09862207 US 09862207 US 86220701 A US86220701 A US 86220701A US 2001021817 A1 US2001021817 A1 US 2001021817A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
blood
flow
pump
rate
line
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US09862207
Inventor
James Brugger
Charles Finch
Jeffrey Burbank
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Vasca Inc
Original Assignee
Vasca Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621Extra-corporeal blood circuits
    • A61M1/3626Gas bubble detectors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621Extra-corporeal blood circuits
    • A61M1/3663Flow rate transducers; Flow integrators
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1001General aspects of blood pumps irrespective of pump type
    • A61M1/1006Blood pumps incorporated within another functional device, e.g. an oxygenator, a dialyser or a blood chamber
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1037Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1037Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps
    • A61M1/1039Peristaltic pumps
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1086Regulating or controlling systems therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/33Controlling, regulating or measuring
    • A61M2205/3331Pressure; Flow
    • A61M2205/3334Measuring or controlling the flow rate

Abstract

Methods, systems, and kits for extracorporeally circulating and processing blood are described. The systems include a pump, a processing unit, and blood drawn return lines for accessing a patient's vasculature. Blood flow through the return line is measured and pump speed controlled to maintain a desired blood flow rate. Alarm conditions can be initiated when expected pump performance differs from that needed to maintain the control point flow rate. By using a ultrasonic flow detector, gas bubbles in the blood flow can be detected.

Description

  • [0001]
    This is a division of U.S. application Ser. No. 09/174,721, filed on Oct. 19, 1998, which is a continuation-in-part of Provisional Application No. 60/074,387, filed on Feb. 11, 1998, the full disclosures of which are incorporated herein by reference in their entirety.
  • BACKGROUND OF THE INVENTION
  • [0002]
    1. Field of the Invention
  • [0003]
    The present invention relates generally to medical methods, apparatus, and kits. More particularly, the present invention relates to methods, systems, and kits for pumping blood through extracorporeal processing units and returning the processed blood to patients.
  • [0004]
    A variety of extracorporeal blood therapies exist which require blood withdrawal, passage through processing equipment, and return of the processed blood to the patient. Examples of such extracorporeal blood therapies include hemodialysis, hemofiltration, hemodiafiltration, apheresis, and the like. Access to a patient's vasculature may be provided through implanted ports, transcutaneous catheters, direct needle access into blood vessels, and other approaches. Once blood withdrawal and blood return lines have been established, the blood is pumped through an appropriate processing unit, such as a dialysis unit, filtration unit, apheresis unit, or the like and the treated blood returned to the patient.
  • [0005]
    It is easy to appreciate that careful control and monitoring of the extracorporeal blood circulation is important to both successful blood treatment and patient safety. Important parameters and conditions to be monitored and controlled include blood flow rate, line pressures upstream and downstream of the pump, blockages in the blood draw line, blockages in the blood return line, air leakage into the recirculation blood stream, and the like. Previous extracorporeal blood circulation systems have often relied on setting the speed of a peristaltic pump to control the blood flow rate. Since peristaltic pumps operate by the positive displacement of blood, it has been assumed that the flow rate will be fixed by the pump speed.
  • [0006]
    As recognized by the inventors herein, however, that assumption is not warranted. Peristaltic pumps, also referred to tube or roller pumps, rely on moving rollers to progressively “pinch” a tube to advance a series of small blood volumes through the tube and out of the pump. So long as the inlet pressure to the pump tube is generally constant, the pump output will be a predictable function of pump speed. In the case of extracorporeal blood circulation, however, where blood is being drawn through a relatively small needle or other access tube, the inlet pressure of blood to the pump can vary significantly. Moreover, the flow characteristics of a peristaltic pump may vary over time so that the volumetric output will change even if the inlet pressure remains generally constant. While use of a peristaltic pump does have a number of advantages, e.g. there are much less likely to apply a deleterious negative pressure to the blood being circulated, calculating the flow rate based on pump speed alone is nonetheless problematic.
  • [0007]
    To help monitor whether the pump is starved of inlet blood flow (which can alter the flow rate as discussed above), some prior art systems have employed pressure monitors on the blood draw and/or return lines. A fall in pressure in the draw line indicates that a blockage or other failure has occurred in the draw line, that the access needle is too small and/or that the access vessel has undergone a partial or total collapse. In contrast, a rise in pressure in the return line indicates the occurrence of an occlusion or other problem in the return line and/or the occurrence of a blockage in the vessel, access device, or fistula. In order to help assure sterility, pressure measurement has usually been performed using drip chambers where the pressure is transmitted via an isolated air line and a transducer protector to the appropriate transducer. Such drip chambers, however, increase the cost of the catheters (blood lines) used for the draw and return lines and the air interface can cause clotting, air entrapment, and other flow problems in the blood recirculation.
  • [0008]
    For these reasons, it would be desirable to provide improved methods, systems, and kits for the extracorporeal recirculation and processing of blood. In particular, it would be desirable to provide extracorporeal blood flow systems having improved blood flow rate control as well as improved capability for monitoring proper operation of the blood circulation circuit. Such systems should permit monitoring with a reduced risk of contaminating the blood or causing clotting, air entrapment, or other degradation of the blood. Preferably, such improved systems and system components will permit relatively low cost operation, and specifically will permit implementation without the use of drip chambers as required by certain prior art systems. At least some of these objectives will be met by the invention described hereinafter.
  • [0009]
    2. Description of the Background Art
  • [0010]
    U.S. Pat. No. 5,562,617 assigned to the assignee of the present application, describes a system of implantable ports and catheters for accessing a patient's vasculature, which system could be used together with the extracorporeal blood recirculation systems of the present invention. U.S. Pat. No. 4,181,132, describing an extracorporeal processing and blood circulation unit which is attached to a patient's vasculature through an implanted port. Co-pending applications assigned to the assignee of the present invention and including related subject matter include: These patents and pending applications are incorporated herein by reference.
  • SUMMARY OF THE INVENTION
  • [0011]
    The present invention provides improved methods, systems, and kits for the extracorporeal circulation and processing of blood for a variety of purposes including but not limited to hemodialysis, hemofiltration, hemodifiltration, apheresis and the like. Particular improvements provided by the present invention include non-contact measurement of the actual blood flow rate in the circuit, preferably at a location close or adjacent to the return access site on the patient. Based on such actual blood flow measurement, the speed of the blood pump in the flow system can be adjusted to maintain the measured blood flow rate at a control point. Thus, operation of the of the system does not rely on an inferred flow rate based on the operational speed of the pump. Moreover, by monitoring the pump operation characteristics, system failures can be detected. For example, a measured blood flow rate which is significantly below an expected blood flow rate calculated from the speed at which the pump is being driven and known pump characteristics indicates a system failure, most likely loss of blood flow in the return line. Actual power consumption by the pump which is significantly above an expected power consumption based on the measured blood flow rate indicates a failure in the blood circulation system, most likely a blockage in the return line or elsewhere distal to the pump. The non-contact flow measurement is preferably performed using an ultrasonic flow detector. Output of the ultrasonic flow detector is also useful for indicating the presence of air in the blood flow which can result from a leak anywhere proximal to (upstream of) the flow detector. Air leaks may also be detected by an actual pump speed which is higher than expected for the measured blood rate. The methods and systems for implementing these safety and monitoring features are described in more detail below.
  • [0012]
    Methods according to the present invention for extracorporeally processing blood comprise pumping blood with a pump having a nominal relationship between pump speed and flow rate, i.e., pump output may be approximated based on pump speed but will be variable due to the factors discussed above. Such pumps will usually be positive displacement pumps, typically being peristaltic pumps which are often preferred since they permit complete isolation of the blood and reduced risk of blood contamination. It would be possible, however, to utilize centrifical and other nonpositive displacement pumps so long as the pumps permit monitoring of the pump speed and prediction of an expected flow rate based on the pump speed.
  • [0013]
    The blood flow rate delivered by the pump is measured, and the pump speed is controlled to maintain the measured blood flow at a control point, typically in the range from 100 ml/min to 1000 ml/min, preferably from 250 min to 500 m/min. Pumped blood is processed in any desired manner, including dialysis, hemofiltration, hemodifiltration, apheresis, and the like, and then returned to the patient. Usually, the blood will be withdrawn from an artery and returned to a vein or will be withdrawn from a vein and returned to a vein. It is also possible, although generally less preferred, to both draw the blood from and return the blood to an artery.
  • [0014]
    The blood flow measuring step is preferably performed with a non-contact flow sensing device, such as an ultrasonic flow sensor. By “non-contact,” it is meant that no component of the measuring device need be immersed in or otherwise in contact with the flowing blood. Preferably, the flow sensors will be mounted or attached over the blood return line or other conduit of the system. Suitable ultrasonic flow sensors are commercially available from suppliers, such as Transonics, Ithaca, N.Y. Other suitable non-contact flow sensing devices include magnetic flow meters, optical flow detectors, electrical conductance flow detectors, and the like. The ultrasonic or other non-contact flow measuring device is preferably mounted over an exterior surface of a blood return line to the patient, more preferably being close to the blood return site on the patient so that the blood is monitored immediately prior to its return to the patient. Use of the ultrasonic flow sensing device also permits the detection of entrained air or other gases in the blood since the ultrasonic signal generated by air passing through the sensor will be immediately detectable i.e. the air will disrupt reflectance of the ultrasound signal which can be readily detected.
  • [0015]
    In a preferred aspect of the methods of the present invention, a failure in the extracorporeal blood flood flow circuit will be detected by calculating or otherwise determining an expected blood flow rate value based on the pump speed. Usually, such a determination can be made by a microprocessor or other controller which is controlling operation of the system as described in more detail below. The expected blood flow rate value is compared with the measured blood flow rate value (i.e. the value measured by the blood flow measurement device), and a difference is determined. If the difference exceeds a threshold value, typically about 5% of the measured flow rate, usually about 10% of the measured flow rate, then an alarm condition will be initiated. An alarm condition may comprise an audible, visual, or other signal being initiated to alert the system user, and/or may include system shut down, or preferably both.
  • [0016]
    In a still further preferred aspect of the method of the present invention, the blood flow status through the system may be monitored by measuring or otherwise determining the actual power being consumed by the pump while it is operating to establish extracorporeal blood flow. An expected value of the power consumption level can be determined by the system based on the pump speed and measured blood flow rate. Any differences between the actual power level being consumed and the expected power level can then be determined. If such a difference exceeds a threshold value, typically above 5% of the measured power consumption, usually above 10% of the measured power consumption, then an alarm condition can be initiated. The alarm conditions may be any of those set forth above.
  • [0017]
    As a further safety measure, pressure of the blood flow in the return line from the processor to the patient may also be detected and monitored. Preferably, the pressure is monitored externally on the blood return line, e.g. by placing a radially inward constriction on the return flow line. Radially outward forces on the constriction can then be monitored and will increase as the pressure within the flow line increases. Such a system can be calibrated to provide a rough estimation of pressure within the blood return line and alarm conditions can be initiated when threshold values are exceeded.
  • [0018]
    Optionally, a safety valve can be placed externally on the blood return line to positively stop blood flow from the system should an alarm condition occur.
  • [0019]
    Systems according to the present invention comprise a pump, a processing unit, a blood draw line, a blood return line, an external flow detector which may be positioned over an exterior surface of the blood return line, and a control unit. The pump is of a type generally described above, preferably being a positive displacement pump, and more preferably being a peristaltic pump. The processing unit may be a convention hemodialysis, hemofiltration, hemodifiltration, or apheresis unit. The blood draw and return lines will typically comprise catheters which are connectable in the system. In particular, the blood draw line will be connectable between the patient and the pump, while the blood return line will be connectable between the processing unit and the patient. The control unit is preferably a microprocessor and is connectable to both the pump and the flow detector so that the control unit can monitor flow and control pump speed according to the methods described above.
  • [0020]
    In particular aspects of the system, the control unit will be programmed to perform other functions as described in connection with the methods above. In particular, the control unit can monitor the actual pump speed and actual blood flow rate to determine if the expected blood flow rate based on pump speed is being achieved. Further, the control unit can monitor power consumption by the pump to determine if it is higher or lower than the expected value of power consumption based on the measured blood flow rate. Still further, the control unit can monitor the output of an ultrasonic flow detector to determine if there are air or other gas bubbles entrained in the flowing blood. Still further, the control unit may be programmed to monitor pressure in the blood return line from an external pressure detector.
  • [0021]
    The present invention will still further comprise kits including system components together with instructions for use. In a specific embodiment, the kit may comprise a blood draw catheter, a blood return catheter, and instructions for use setting forth any of the methods described above. System components will typically be packaged in a conventional medical device package, such as a pouch, tray, box, tube, or the like. Instructions may be printed on a separate sheet of paper or may be printed in whole or in part on part of the package materials. Usually, the system components will be maintained in a sterile condition within the packaging.
  • [0022]
    In an additional aspect of the present invention, a method for extracorporeally processing blood comprises drawing blood from the patient and pumping the drawn blood with a peristaltic pump at a predetermined stroke volume and rate corresponding to a theoretical pumped blood flow rate, i.e. a theoretical or expected value of blood flow rate that can be calculated based upon the known stroke volume and actual rate at which the peristaltic pump is being driven. An actual blood flow rate delivered by the pump is directly measured using any of the techniques described above, and the measured actual blood flow rate is compared with the theoretical or calculated blood flow rate. In a first instance, an alarm condition is signaled if the difference between the actual blood flow rate and the theoretical blood flow rate exceeds a predetermined minimum or threshold value. In a second instance, the rate at which the peristaltic pump is being driven is altered or varied in order to change the pumped blood flow rate to a desired value, e.g. one that more closely matches the theoretical pumped flow rate. It will be appreciated, of course, that the theoretical blood flow rate will vary over time as the pump speed is varied so that the theoretical flow rate and a target or control point flow rate will not always be precisely the same. It will further be appreciated that both the alarm and control aspects of this method may be employed or together.
  • [0023]
    In yet another aspect of the present invention, apparatus for extracorporeally processing blood comprises tubing having connectors for drawing blood from a patient and returning blood to the patient, where the tubing is connected to or comprises a section of peristaltic pump tubing. A controller operates the peristaltic pump at a desired stroke volume and rate which, at least at the outset, corresponds to a theoretical pumped blood flow rate. Apparatus directly measures the actual blood flow rate delivered by the pump through the tubing, and further apparatus compares the measured actual blood flow rate with the theoretical pumped blood flow rate. A signal is generated corresponding to a difference between the theoretical and actual blood flow rates. A signal may be used to initiate an alarm condition and/or control the actual pump speed in order to return the actual blood flow rate to a desired level or control point. Preferably, all tubing in the apparatus will be free of air-containing chambers, such as drip chambers.
  • [0024]
    In a still further aspect of the present invention, a blood processing system comprises a pump operable at different speeds to convey blood through a path. The system further includes a sensor which monitors blood flow rate and optionally detects the presence of air in the blood flow. A controller is coupled to both the sensor and the pump in order to control pump speed (and thus blood flow rate) as a function of monitored flow rate. Usually, the controller adjusts the flow rate as a function of deviation between the monitored blood flow rate and a desired (set point) flow rate. The control algorithm can be proportional, integral, derivative, or virtually any other known control algorithm. Usually, the sensor will be an ultrasonic sensor as described above.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0025]
    [0025]FIG. 1 is a schematic illustration of the system constructing in accordance with the principles of the present invention performing extracorporeal blood circulation and processing on a patient.
  • [0026]
    [0026]FIG. 2 illustrates an exemplary kit constructed in accordance with the principles of the present invention.
  • DESCRIPTION OF THE PREFERRED EMBODIMENT
  • [0027]
    An exemplary system 10 for performing the methods of the present invention is illustrated in FIG. 1. The system 10 comprises a pump 12 coupled to a pump driver 14, a processing unit 16, a blood inlet line 18, and a blood return line 20. The pump 12 is illustrated as a peristaltic pump having a pair of opposed rollers 22 which are rotatably driven on an armature 24 to engage a resilient flow tube 26 (which may optionally be part of the replaceable inlet line 18). The driver 14 causes the armature 24 to rotate at a preselected rotational rate, typically comprising a digitally or servo controlled drive motor. The volumetric flow rate through the pump 12 may thus be approximated in the first instance by the internal diameter of the flow tube 26, stroke length of the pump (i.e., the length of tubing between the engagements points of the rollers 22), and the rotational rate of the armature 24. For the purposes of the present invention, it is important that there be a theoretical relationship between the pump speed, i.e. rotational rate of the armature 24, and the flow rate. In the case of the peristaltic pump, the theoretical relationship is linear. It will be appreciate that other types of pumps could also be utilized. Preferred pumps include other positive displacement pumps such as piston pumps, and the like, where the flow rate will have a linear relationship with the speed at which the pump is driven. It will also be possible to use centrifical pumps which have a non-linear, but predictable relationship between the pump speed and flow rate. The use of peristaltic pumps, however, is most preferred since in addition to providing a known, theoretically linear relationship between pump speed and flow, they also provide for complete isolation of the blood passing thorough the pump.
  • [0028]
    The processing unit 16 may be any device or apparatus intended for the extracorporeal treatment of blood. Most commonly, the processing unit 16 will be a hemodialysis unit, a hemofiltration, a hemodifiltration, a apheresis, or the like. Such processing units will typically have other associated components which are not shown in FIG. 1. For example, hemodialysis units will have the components necessary for continuously flowing a dialysate solution past an internal membrane to perform the desired dialysis function. Hemofiltration and diafiltration may have components for regenerating and controlling the filtering operation.
  • [0029]
    The blood draw line 18 will typically comprise a flexible tube or catheter having a distal end 30 adapted to access a patient's vasculature, e.g. a percutaneous access device adapted to connect to a subcutaneous port, and a proximal end 32 adapted to connect to an inlet port 34 of the pump 12. The distal end 30 can be adapted in a variety of ways. As illustrated, an access needle 36 is provided for percutaneous access to an implanted port, as generally described in a co-pending application Ser. No. 08/942,990, filed on Oct. 2, 1997, assigned to the assignee of the present application, the full disclosure of which is incorporated herein by reference. The access port will be subcutaneously connected to an artery or a vein to provide a source of blood for processing as more completely described in the co-pending application. The blood draw line could also be configured for connection to transcutaneous catheters, other implanted ports, or other blood access systems as described in the medical and patent literature. For use in the present invention, tubes or catheters comprising the blood draw line will typically have inner lumen diameters in the range from 2 mm to 8 mm, preferably from 4 mm to 6 mm, and lengths in the range from 50 cm to 300 cm, typically from 120 cm to 180 cm. The tubes or catheters may be composed of conventional materials, such as polyvinylchloride, silicone elastomer, polyurethane, and the like.
  • [0030]
    The processing unit 16 will receive blood from an outlet port 40 of the pump 12 via a connector 43. After passing through the processing unit 16 (typically a dialysis membrane or hemofiltration filter), the blood will flow outwardly through the port 42 and into the blood return line 20. The blood return line 20 usually comprises a tube or catheter having a distal end 44 adapted for accessing the patient vasculature typically through an implanted port or other conventional access device as described above. The proximal end 46 of the tube or catheter is preferably connectable directly to the outlet 42 of the processing unit 16. Thus, the extracorporeal circuit which is established comprises the blood draw line 18, the flow tube 26 of the pump 12, the processing unit 16, and the return line 20. Preferably, at least the draw line 18, flow tube 26, and return line 20 will be disposable and replaceable with new, sterile components to lower the risk of patient infection. Usually, at least the internal components of the processing unit 16 will also be disposable and replaceable for the same reason. In this way, all system components which contact the circulating blood will be initially sterile and used only once.
  • [0031]
    As described thus far, the extracorporeal circuit is generally conventional. One significant difference, however, with many previous systems is that neither the blood draw line nor the blood return line 20 need include drip chamber(s) to facilitate pressure monitoring (although the present invention does not preclude the use of drip chambers). It is a particular advantage of the present system that the use of such drip chambers is not necessary.
  • [0032]
    The system 10 is monitored and controlled by a control unit 50 which is typically a microprocessor based programmable controller integrated with the processing unit 16 but which may also be a separate personal computer or work station. The control unit 50 will have appropriate input/output devices 52, such as knobs, dials, a display screen, keyboard, hardisk, floppy disk, CD drive, and the like, for permitting control, monitoring, and data acquisition in a generally conventional manner.
  • [0033]
    In particular, the control unit 50 will be connected to the pump driver 14 in order to permit the user to set the desired blood flow rate, typically in the ranges set forth above. The user will usually input a value of flow rate, typically in ml/min, and the control unit 50 will determine the corresponding pump speed which is expected to provide such a full rate based on the known pump characteristics. This selected flow rate will be the “expected” flow rate which is considered in a number of contexts below in connection with operation of the system. This user-selected “expected” flow rate will typically be a fixed value throughout the entire treatment protocol. The flow rate, however, could also be varied over time in which case the “expected” value for the flow rate will also vary as the treatment protocol progresses.
  • [0034]
    The actual blood flow rate is measured by a flow sensor 60 which is positioned to measure the output of the pump 12 after it passes through the processing unit 16. The sensor 60 is preferably a “non-contact” sensor which can be placed over an exterior surface of the blood return line 20 to measure the blood flow without any contact between the sensor and the blood itself. In this way, the flow sensor 60 can be reused without contamination from any individual patient. Preferably, the flow sensor 60 will be an ultrasonic flow sensor, such as model HT109, available from Transonics, Ithaca, N.Y. The ultrasonic sensor is particularly preferred, however, since it also permits monitoring of gas bubbles within the return line 20, as described in more detail below. Output of the flow sensor 60 is directed back to the control unit 50 where it is used for several purposes.
  • [0035]
    In particular, real-time determination of the blood flow rate through the return line 20 can be used for feedback control of the blood flow rate. While the blood flow rate may be nominally selected based on the pump speed, feedback of the actual flow from flow sensor 60 to the control unit 50 permits the control unit to adjust the 20 pump speed to more precisely achieve the actual blood flow rate. The control unit 50 can be programmed to implement a variety of suitable control algorithms, including proportional control, derivative control, integral control, and combinations thereof.
  • [0036]
    In addition to real-time control of the blood flow rate, monitoring of the actual blood flow rate with flow sensor 60 permits the system 10 to monitoring for malfunctions. In the first instance, the control unit 50 can compare the actual flow rate as measured by the sensor 60 with the flow rate which would be expected for the pump 12 based on its known relationship between pump speed and flow output. If the pump speed is significantly higher than the speed which would be expected for achieving the actual flow rate, it is likely that the system is malfunctioning. For example, there may be a blockage between the patient and the pump 12 which starves the pump of blood. The pump 12 will then turn faster in response to the control algorithm which is attempting to maintain the flow control point.
  • [0037]
    Alternatively, there may be a leak between the output of the pump 12 and the flow detector 60, e.g. in the processing unit 16, which may also cause the pump to turn faster in an attempt to achieve the control point flow through the flow sensor. In either case, the control unit 50 can initiate an alarm condition when the pump speed is greater than the expected speed or the control point flow rate by some threshold amount, usually at least 1%, more usually at least 5%, and often 10%, or more, based on the preselect flow rate. The alarm condition may comprise shutting down the pump 12, initiating a visual or audible alarm and/or closing a safety valve 70 on the blood return line 20. Usually, all three actions will be taken.
  • [0038]
    When using an ultrasonic flow sensor 60, the system 10 can also detect the presence of air or other gas bubbles in the return line 20 to the patient. The ultrasonic reflective characteristics of blood and gas vary considerably, permitting the control unit 50 to detect the presence of the gas based on a very significant disruption in the detected ultrasonic signal. The presence of air or other gases in the blood return in the patient can result from a leak in the system anywhere upstream of the flow sensor 60. Regardless of the cause, the system 10 will initiate an alarm condition generally as described above in the case of pump overspeed. Since the controller 50 will know the cause, the alarm condition can indicate that it results from the presence of gas bubbles in the blood return line.
  • [0039]
    Knowledge of the actual flow rate provided by flow sensor 60 to the control unit 50 can also be used to detect a blockage in the downstream of the pump 12, usually in the return line 20. Any blockage downstream or distal from the pump 12 discharge port 40 will cause a greater pressure drop across the pump in order to maintain a given flow rate. Thus, by monitoring the power or current being consumed by the pump driver 14 through signal line 80, the actual power needed to drive the pump 12 can be compared with the expected power based on the actual flow rate. When the actual power consumed by the pump 12 exceeds the expected value by a threshold amount, typically at least 1%, usually at least 5%, and often 10% or more, based on the expected power consumption, then an alarm condition can be initiated generally as described above. An alarm condition can particularly indicated that there is a blockage in that portion of the system which is downstream or proximal from the pump 12.
  • [0040]
    Optionally, an external pressure sensor 90 can also be provided on the blood return line 20. The pressure sensor 90 can be a collar or other restriction which applies a small radially inward force on the resilient body of the return line 20. As blood flows through the return line, the corresponding radially outward pressure will be applied against the collar or other constriction. By monitoring this radially outward force, excess pressures through the return line 20 can be detected. Such secondary pressure monitoring is desirable for detecting significant overpressures, typically above 400 mmHg, and can be used to immediately shut down the system and initiate an alarm condition as described above.
  • [0041]
    In operation, the vasculature of a patient P is accessed by connecting the blood draw line 18 to an arterial or venous source within the patient. The blood draw line is then connected to the inlet port 34 of the pump 12. The blood return line 20 is then connected to a venous return location within the patient P and, at its other end, to an output port 42 of the processing unit 16. The flow sensor 60 will then be connected typically about the exterior of the blood return line 20. Optionally, the stop valve 70 and the overpressure detector 90 will also be connected to the exterior of the blood return line 20. The operation in the pump 12 will then be initiated to begin blood circulation through the draw line 18, pump 12, processing unit 16, and back to the patient to the return line 20. The blood flow rate will be controlled using the active control scheme described above, while system operation and malfunction will be monitored, also as described above.
  • [0042]
    The present invention will also provide kits 100 including some or all of the disposable components which can be used with the system 10 for performing the methods of the present invention. For example, the kit 100 can include tubes or catheters comprising the draw line 18 and return line 20 as well as instructions for use 102 setting forth methods for extracorporeally circulating blood as described above. The catheters 18 and 20 and instructions for use 102 will typically be sterilely packaged within a conventional medical device package 104, such as a pouch, tray, tube, box, or the line. Instructions for use 102 will usually be printed on a separate sheet of paper, but may also be printed in whole or in part on a portion of the packing materials.
  • [0043]
    While the above is a complete description of the preferred embodiments of the invention, various alternatives, modifications, and equivalents may be used. Therefore, the above description should not be taken as limiting the scope of the invention which is defined by the appended claims.

Claims (8)

    What is claimed is:
  1. 1. A method for extracorporeally processing blood, said method comprising:
    drawing blood from a patient;
    pumping the blood with a pump at a predetermined blood flow rate;
    measuring an actual blood flow rate delivered by the pump;
    comparing the actual blood flow rate with the predetermined blood flow rate; and
    adjusting the blood flow rate delivered by the pump.
  2. 2. The method of
    claim 1
    , further comprising the step of signaling an alarm condition if a difference of a predetermined minimum value exists.
  3. 3. The method of
    claim 1
    , wherein the actual blood flow rate is directly measured.
  4. 4. The method of
    claim 1
    , wherein the step of pumping the drawn blood with a pump at a predetermined blood flow rate includes pumping the drawn blood with a pump at a predetermined stroke volume and blood flow rate.
  5. 5. The method of
    claim 1
    , wherein the drawn blood is pumped at a blood flow rate that corresponds to a theoretical pumped blood flow rate.
  6. 6. The method of
    claim 1
    , wherein the pump is a peristaltic pump.
  7. 7. The method of
    claim 1
    , further comprising the step of slowing or stopping pump operation when said difference has said predetermined minimum value.
  8. 8. The method of
    claim 1
    wherein the measuring step comprises ultrasonically measuring the flow rate using a sensor disposed externally to the blood flow.
US09862207 1998-02-11 2001-05-21 Methods, systems, and kits for the extracorporeal processing of blood Abandoned US20010021817A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US7438798 true 1998-02-11 1998-02-11
US09174721 US7004924B1 (en) 1998-02-11 1998-10-19 Methods, systems, and kits for the extracorporeal processing of blood
US09862207 US20010021817A1 (en) 1998-02-11 2001-05-21 Methods, systems, and kits for the extracorporeal processing of blood

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US09862207 US20010021817A1 (en) 1998-02-11 2001-05-21 Methods, systems, and kits for the extracorporeal processing of blood

Publications (1)

Publication Number Publication Date
US20010021817A1 true true US20010021817A1 (en) 2001-09-13

Family

ID=21742376

Family Applications (2)

Application Number Title Priority Date Filing Date
US09174721 Active US7004924B1 (en) 1998-02-11 1998-10-19 Methods, systems, and kits for the extracorporeal processing of blood
US09862207 Abandoned US20010021817A1 (en) 1998-02-11 2001-05-21 Methods, systems, and kits for the extracorporeal processing of blood

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US09174721 Active US7004924B1 (en) 1998-02-11 1998-10-19 Methods, systems, and kits for the extracorporeal processing of blood

Country Status (2)

Country Link
US (2) US7004924B1 (en)
WO (1) WO2002070042B1 (en)

Cited By (64)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030152482A1 (en) * 2002-02-14 2003-08-14 O'mahony John J. Method and apparatus for an extracorporeal treatment device to control blood withdrawal and infusion
WO2003072942A1 (en) * 2002-02-21 2003-09-04 Terumo Cardiovascular Systems Corporation Method and apparatus for controlling fluid pumps
US20030210390A1 (en) * 2002-05-07 2003-11-13 O'mahony John J. Blood leak detector for extracorporeal treatment system
US20040030277A1 (en) * 2000-11-02 2004-02-12 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US20040039324A1 (en) * 2000-11-27 2004-02-26 Chf Solutions, Inc. Controller for ultrafiltration blood circuit which prevents hypotension by monitoring osmotic pressure in blood
US20040084358A1 (en) * 2001-04-13 2004-05-06 Chf Solutions, Inc. User interface for blood treatment device
US20040195165A1 (en) * 2003-04-04 2004-10-07 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US20050094127A1 (en) * 2003-10-29 2005-05-05 Chf Solutions Inc. Cuvette apparatus and system for measuring optical properties of a liquid such as blood
US20050131332A1 (en) * 2003-11-05 2005-06-16 Thomas Kelly High convection home hemodialysis/hemofiltration and sorbent system
US20050256444A1 (en) * 2004-04-26 2005-11-17 Chf Solutions Inc. User interface for blood treatment device
US20060095021A1 (en) * 2004-11-02 2006-05-04 Casas-Bejar Jesus W Introduction of agent with medical device
US20070100272A1 (en) * 2002-03-04 2007-05-03 Dennis Briggs Method for collecting a desired blood component and performing a photopheresis treatment
US7311689B2 (en) 2000-05-23 2007-12-25 Chf Solutions, Inc. Method and apparatus for peripheral vein fluid removal in heart failure
US20080086042A1 (en) * 2006-10-04 2008-04-10 Dexcom, Inc. Analyte sensor
US20080200788A1 (en) * 2006-10-04 2008-08-21 Dexcorn, Inc. Analyte sensor
US20080203023A1 (en) * 2002-06-06 2008-08-28 Nxstage Medical, Inc. Last-chance quality check and/or air/pathogen filtger for infusion systems
US20080230450A1 (en) * 2005-01-07 2008-09-25 Burbank Jeffrey H Filtration System for Preparation of Fluids for Medical Applications
US20090012456A1 (en) * 2007-07-05 2009-01-08 Baxter International Inc. Dialysis system having disposable cassette
WO2008148506A3 (en) * 2007-06-04 2009-04-30 Fresenius Medical Care De Gmbh Device for controlling a system for transporting blood, and method for transporting blood in a blood line of an extracorporeal blood circuit of an extracorporeal blood treatment device
US20090124963A1 (en) * 2007-11-09 2009-05-14 Baxter International Inc. Balanced flow dialysis machine
US20090182263A1 (en) * 2006-04-07 2009-07-16 Burbank Jeffrey H Filtration system for preparation of fluids for medical applications
US20090211975A1 (en) * 2003-01-07 2009-08-27 Brugger James M Batch Filtration System for Preparation of Sterile Fluid for Renal Replacement Therapy
WO2010020380A1 (en) * 2008-08-21 2010-02-25 Fresenius Medical Care Deutschland Gmbh Method and apparatus for monitoring a peristaltic hose pump for conducting a fluid in a tubing
WO2010065398A1 (en) 2008-12-04 2010-06-10 Therox, Inc. Method and device for combined detection of bubbles and flow rate in a system for enriching a bodily fluid with a gas
US7744553B2 (en) 2003-12-16 2010-06-29 Baxter International Inc. Medical fluid therapy flow control systems and methods
US7857760B2 (en) 2004-07-13 2010-12-28 Dexcom, Inc. Analyte sensor
US20110160637A1 (en) * 2009-12-31 2011-06-30 Fresenius Medical Care Holdings, Inc. Detecting Blood Flow Degradation
WO2011079941A1 (en) * 2009-12-28 2011-07-07 Fresenius Medical Care Deutschland Gmbh Device and method for monitoring an extracorporeal blood treatment
US20110196282A1 (en) * 2008-12-19 2011-08-11 Cvdevices, Llc (A California Limited Liability Company) Devices, systems, and methods for autoretroperfusion
US8038639B2 (en) 2004-11-04 2011-10-18 Baxter International Inc. Medical fluid system with flexible sheeting disposable unit
US8114276B2 (en) 2007-10-24 2012-02-14 Baxter International Inc. Personal hemodialysis system
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US20120310205A1 (en) * 2011-06-06 2012-12-06 Chaoyoung Lee Medical Pump Providing Customizable Programming Permissions
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US20130030345A1 (en) * 2011-07-29 2013-01-31 Fresenius Medical Care Deutschland Gmbh Method as well as apparatuses for detecting a permeability or patency in a tube which is inserted in a tube pump
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
CN103170024A (en) * 2012-10-18 2013-06-26 郝兴海 Normovolemic dilution autoblood collection and reinfusion system and normovolemic dilution autoblood collection and reinfusion device
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
US8517968B2 (en) 2011-02-25 2013-08-27 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US8562558B2 (en) 2007-06-08 2013-10-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
US8676288B2 (en) 1997-03-04 2014-03-18 Dexcom, Inc. Device and method for determining analyte levels
US8743354B2 (en) 2010-09-07 2014-06-03 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US20140194817A1 (en) * 2012-06-06 2014-07-10 Zyno Medical, LLC. Medical pump with operator-authorization awareness
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
USD725261S1 (en) 2012-02-24 2015-03-24 Fresenius Medical Care Holdings, Inc. Blood flow chamber
US9173988B2 (en) 2010-11-17 2015-11-03 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
US9194792B2 (en) 2010-09-07 2015-11-24 Fresenius Medical Care Holdings, Inc. Blood chamber for an optical blood monitoring system
CN105597178A (en) * 2015-12-22 2016-05-25 济南市儿童医院 Remote monitoring method, device and equipment of blood purification system
US9370324B2 (en) 2008-11-05 2016-06-21 Fresenius Medical Care Holdings, Inc. Hemodialysis patient data acquisition, management and analysis system
US9375526B2 (en) 2013-06-25 2016-06-28 Fresenius Medical Care Holdings, Inc. Vial spiking assemblies and related methods
US9439589B2 (en) 1997-03-04 2016-09-13 Dexcom, Inc. Device and method for determining analyte levels
US9504781B2 (en) 2008-12-19 2016-11-29 Cvdevices, Llc Peripheral arterialization devices and methods of using the same
US9764074B1 (en) 2002-07-19 2017-09-19 Baxter International Inc. Systems and methods for performing dialysis
USD799031S1 (en) 2015-09-09 2017-10-03 Fresenius Medical Care Holdings, Inc. Blood flow chamber with directional arrow
US9801993B2 (en) 2010-11-17 2017-10-31 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
US9968727B2 (en) 2013-08-13 2018-05-15 Cvdevices, Llc Systems, devices, and methods for organ retroperfusion along with regional mild hypothermia

Families Citing this family (71)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6554791B1 (en) 1999-09-29 2003-04-29 Smisson-Cartledge Biomedical, Llc Rapid infusion system
US6497676B1 (en) * 2000-02-10 2002-12-24 Baxter International Method and apparatus for monitoring and controlling peritoneal dialysis therapy
US7645225B2 (en) * 2000-03-27 2010-01-12 Alexander Medvedev Chronic performance control system for rotodynamic blood pumps
US20050131305A1 (en) * 2002-05-17 2005-06-16 Danielson Bo G. Sensor unit and method for sensing a blood related parameter and system including such a sensor unit
US7153286B2 (en) * 2002-05-24 2006-12-26 Baxter International Inc. Automated dialysis system
US7175606B2 (en) 2002-05-24 2007-02-13 Baxter International Inc. Disposable medical fluid unit having rigid frame
JP2005533560A (en) 2002-07-19 2005-11-10 バクスター インターナショナル インコーポレイテッド System and method for performing peritoneal dialysis
US7238164B2 (en) 2002-07-19 2007-07-03 Baxter International Inc. Systems, methods and apparatuses for pumping cassette-based therapies
DE20307256U1 (en) * 2003-05-09 2003-10-02 Lifebridge Medizintechnik Gmbh Portable heart-lung machine
US7029456B2 (en) * 2003-10-15 2006-04-18 Baxter International Inc. Medical fluid therapy flow balancing and synchronization system
JP4691503B2 (en) * 2003-10-28 2011-06-01 バクスター・インターナショナル・インコーポレイテッドBaxter International Incorp0Rated For medical fluid system, improved priming method and apparatus integrity and hydraulic head height
EP1696806B1 (en) 2003-11-21 2012-08-29 Silk Road Medical, Inc. Apparatus for treating a carotid artery
US7160243B2 (en) * 2004-03-25 2007-01-09 Terumo Corporation Method and system for controlling blood pump flow
US20060173396A1 (en) * 2004-12-09 2006-08-03 Mehdi Hatamian Systems and methods for temperature adjustment using bodily fluids as a thermic medium
US7935070B2 (en) * 2005-01-28 2011-05-03 Fresenius Medical Care North America Systems and methods for dextrose containing peritoneal dialysis (PD) solutions with neutral pH and reduced glucose degradation product
US7563248B2 (en) 2005-03-17 2009-07-21 Smisson-Cartledge Biomedical Llc Infusion fluid heat exchanger and cartridge
US7975491B2 (en) * 2005-03-17 2011-07-12 Smisson-Cartledge Biomedical Llc Heat exchange system for a pump device
US8211060B2 (en) 2005-05-10 2012-07-03 Palyon Medical (Bvi) Limited Reduced size implantable pump
US7637892B2 (en) * 2005-05-10 2009-12-29 Palyon Medical (Bvi) Limited Variable flow infusion pump system
US8915893B2 (en) 2005-05-10 2014-12-23 Palyon Medical (Bvi) Limited Variable flow infusion pump system
CN101678160A (en) * 2007-04-05 2010-03-24 麦克罗美德技术公司 Blood pump system
US7901376B2 (en) * 2007-07-05 2011-03-08 Baxter International Inc. Dialysis cassette having multiple outlet valve
US8512553B2 (en) 2007-07-05 2013-08-20 Baxter International Inc. Extracorporeal dialysis ready peritoneal dialysis machine
US8157760B2 (en) * 2007-07-18 2012-04-17 Silk Road Medical, Inc. Methods and systems for establishing retrograde carotid arterial blood flow
US8858490B2 (en) 2007-07-18 2014-10-14 Silk Road Medical, Inc. Systems and methods for treating a carotid artery
WO2009029677A1 (en) * 2007-08-27 2009-03-05 Quest Medical, Inc. Self-adaptive piston blood pump
US8597505B2 (en) 2007-09-13 2013-12-03 Fresenius Medical Care Holdings, Inc. Portable dialysis machine
US9199022B2 (en) 2008-09-12 2015-12-01 Fresenius Medical Care Holdings, Inc. Modular reservoir assembly for a hemodialysis and hemofiltration system
US9358331B2 (en) 2007-09-13 2016-06-07 Fresenius Medical Care Holdings, Inc. Portable dialysis machine with improved reservoir heating system
US20090076434A1 (en) * 2007-09-13 2009-03-19 Mischelevich David J Method and System for Achieving Volumetric Accuracy in Hemodialysis Systems
US9308307B2 (en) 2007-09-13 2016-04-12 Fresenius Medical Care Holdings, Inc. Manifold diaphragms
US8105487B2 (en) * 2007-09-25 2012-01-31 Fresenius Medical Care Holdings, Inc. Manifolds for use in conducting dialysis
US20090101577A1 (en) * 2007-09-28 2009-04-23 Fulkerson Barry N Methods and Systems for Controlling Ultrafiltration Using Central Venous Pressure Measurements
US20090114037A1 (en) * 2007-10-11 2009-05-07 Mark Forrest Smith Photo-Acoustic Flow Meter
US8040493B2 (en) * 2007-10-11 2011-10-18 Fresenius Medical Care Holdings, Inc. Thermal flow meter
WO2009073567A1 (en) 2007-11-29 2009-06-11 Xcorporeal. Inc. System and method for conducting hemodialysis and hemofiltration
JP2011510796A (en) * 2008-02-05 2011-04-07 シルク・ロード・メディカル・インコーポレイテッドSilk Road Medical, Inc. Interventional catheter system and method
US20090198172A1 (en) * 2008-02-05 2009-08-06 Garrison Michi E Interventional sheath with retention features
US8092416B2 (en) 2008-03-28 2012-01-10 Vitalmex Internacional S.A. De C.V. Device and method for connecting a blood pump without trapping air bubbles
US8062513B2 (en) 2008-07-09 2011-11-22 Baxter International Inc. Dialysis system and machine having therapy prescription recall
US9011467B2 (en) 2008-08-13 2015-04-21 Silk Road Medical, Inc. Suture delivery device
US8574245B2 (en) * 2008-08-13 2013-11-05 Silk Road Medical, Inc. Suture delivery device
CN105148344A (en) 2008-10-07 2015-12-16 弗雷塞尼斯医疗保健控股公司 Priming system and method for dialysis systems
CA2928208A1 (en) * 2008-10-30 2010-06-03 Fresenius Medical Care Holdings, Inc. Modular, portable dialysis system
EP2379129B1 (en) * 2008-12-23 2017-09-13 Silk Road Medical, Inc. Methods and systems for treatment of acute ischemic stroke
US8240636B2 (en) 2009-01-12 2012-08-14 Fresenius Medical Care Holdings, Inc. Valve system
WO2010083167A3 (en) * 2009-01-13 2010-09-23 Silk Road Medical, Inc. Methods and systems for performing neurointerventional procedures
US9370664B2 (en) * 2009-01-15 2016-06-21 Boston Scientific Neuromodulation Corporation Signaling error conditions in an implantable medical device system using simple charging coil telemetry
US20100184198A1 (en) * 2009-01-16 2010-07-22 Joseph Russell T Systems and Methods of Urea Processing to Reduce Sorbent Load
US8535522B2 (en) * 2009-02-12 2013-09-17 Fresenius Medical Care Holdings, Inc. System and method for detection of disconnection in an extracorporeal blood circuit
US8475399B2 (en) * 2009-02-26 2013-07-02 Fresenius Medical Care Holdings, Inc. Methods and systems for measuring and verifying additives for use in a dialysis machine
US20100228269A1 (en) * 2009-02-27 2010-09-09 Garrison Michi E Vessel closure clip device
WO2010141752A1 (en) * 2009-06-03 2010-12-09 Silk Road Medical, Inc. System and methods for controlling retrograde carotid arterial blood flow
US9943236B2 (en) * 2009-09-30 2018-04-17 Medtronic, Inc. Methods for guiding heart failure decompensation therapy
US8753515B2 (en) 2009-12-05 2014-06-17 Home Dialysis Plus, Ltd. Dialysis system with ultrafiltration control
US9585810B2 (en) 2010-10-14 2017-03-07 Fresenius Medical Care Holdings, Inc. Systems and methods for delivery of peritoneal dialysis (PD) solutions with integrated inter-chamber diffuser
WO2013052680A3 (en) 2011-10-07 2013-07-11 Home Dialysis Plus, Ltd. Heat exchange fluid purification for dialysis system
US8568360B2 (en) 2011-12-28 2013-10-29 Palyon Medical (Bvi) Limited Programmable implantable pump design
JP5587958B2 (en) * 2012-10-19 2014-09-10 日機装株式会社 Peristaltic pump
JP5469728B1 (en) 2012-10-19 2014-04-16 日機装株式会社 The pressure sensing device of the liquid flow path
US9157786B2 (en) 2012-12-24 2015-10-13 Fresenius Medical Care Holdings, Inc. Load suspension and weighing system for a dialysis machine reservoir
US9440017B2 (en) 2013-03-14 2016-09-13 Baxter International Inc. System and method for performing alternative and sequential blood and peritoneal dialysis modalities
US9433720B2 (en) 2013-03-14 2016-09-06 Fresenius Medical Care Holdings, Inc. Universal portable artificial kidney for hemodialysis and peritoneal dialysis
CN103520786B (en) * 2013-10-16 2015-10-14 上海工程技术大学 A method of controlling the flow of blood purification peristaltic pump
US9354640B2 (en) 2013-11-11 2016-05-31 Fresenius Medical Care Holdings, Inc. Smart actuator for valve
US9265512B2 (en) 2013-12-23 2016-02-23 Silk Road Medical, Inc. Transcarotid neurovascular catheter
JP2015205056A (en) * 2014-04-21 2015-11-19 テルモ株式会社 Extracorporeal circulation apparatus and control method thereof
EP3137128A4 (en) 2014-04-29 2018-01-03 Outset Medical Inc Dialysis system and methods
US9241699B1 (en) 2014-09-04 2016-01-26 Silk Road Medical, Inc. Methods and devices for transcarotid access
US9486590B2 (en) 2014-09-29 2016-11-08 Fenwal, Inc. Automatic purging of air from a fluid processing system
US9498567B2 (en) 2014-09-29 2016-11-22 Fenwal, Inc. Systems and methods for controlling the return phase of a blood separation procedure

Family Cites Families (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS52132175A (en) * 1976-04-26 1977-11-05 Santo Tekkosho Kk Method of preventing curling knitted cloth
US4108574A (en) * 1977-01-21 1978-08-22 International Paper Company Apparatus and method for the indirect measurement and control of the flow rate of a liquid in a piping system
US4181132A (en) 1977-05-31 1980-01-01 Parks Leon C Method and apparatus for effecting hyperthermic treatment
US4173144A (en) * 1978-04-03 1979-11-06 Transdynamics Low flow rate transducer construction
US4401431A (en) 1981-06-26 1983-08-30 Arp Leon J Blood pump and oxygenator monitor-controller and display device
CA1201999A (en) * 1982-08-03 1986-03-18 Peter G. Wheeldon Fluid flow control process and apparatus
US4828543A (en) 1986-04-03 1989-05-09 Weiss Paul I Extracorporeal circulation apparatus
US4690002A (en) * 1986-05-14 1987-09-01 Minnesota Minning And Manufacturing Company Doppler system for measurement of blood flow during cardiopulmonary bypass and ventricular assist
FR2599496B1 (en) * 1986-05-28 1992-02-14 Mms bubble detector in a liquid circuit
US4902276A (en) * 1986-06-09 1990-02-20 The Regents Of The University Of California Apparatus and method for removing obstructions in bodily organs or cavities
DE3720667A1 (en) 1987-06-23 1989-01-05 Schael Wilfried Haemodialysis and haemofiltration unit
US5814004A (en) * 1989-09-22 1998-09-29 Tamari; Yehuda System for regulating pressure within an extracorporeal circuit
US5391142A (en) * 1992-07-29 1995-02-21 Organetics, Ltd. Apparatus and method for the extracorporeal treatment of the blood of a patient having a medical condition
DE4232130A1 (en) * 1992-09-25 1994-03-31 Teves Gmbh Alfred Method and circuit arrangement for controlling the delivery rate of a hydraulic pump
US5562617A (en) 1994-01-18 1996-10-08 Finch, Jr.; Charles D. Implantable vascular device
US5597377A (en) * 1994-05-06 1997-01-28 Trustees Of Boston University Coronary sinus reperfusion catheter
US5618441A (en) * 1995-06-07 1997-04-08 Rosa; Jim Single microcontroller execution of control and safety system functions in a dialysis machine
US5820579A (en) * 1996-04-30 1998-10-13 Medtronic, Inc. Method and apparatus for creating pulsatile flow in a cardiopulmonary bypass circuit
US5779721A (en) * 1996-07-26 1998-07-14 Kensey Nash Corporation System and method of use for revascularizing stenotic bypass grafts and other blood vessels
JPH10103286A (en) * 1996-09-30 1998-04-21 Kubota Corp Operation control method of pump
US20010016699A1 (en) * 1997-02-14 2001-08-23 Jeffrey H. Burbank Hemofiltration system
US6135943A (en) 1998-08-07 2000-10-24 Cardiac Assist Technologies, Inc. Non-invasive flow indicator for a rotary blood pump
US20050209547A1 (en) 2002-06-06 2005-09-22 Burbank Jeffrey H Last-chance quality check and/or air/pathogen filter for infusion systems

Cited By (178)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6783328B2 (en) 1996-09-30 2004-08-31 Terumo Cardiovascular Systems Corporation Method and apparatus for controlling fluid pumps
US9439589B2 (en) 1997-03-04 2016-09-13 Dexcom, Inc. Device and method for determining analyte levels
US8676288B2 (en) 1997-03-04 2014-03-18 Dexcom, Inc. Device and method for determining analyte levels
US9931067B2 (en) 1997-03-04 2018-04-03 Dexcom, Inc. Device and method for determining analyte levels
US9339223B2 (en) 1997-03-04 2016-05-17 Dexcom, Inc. Device and method for determining analyte levels
US20110208106A1 (en) * 2000-05-23 2011-08-25 Chf Solutions, Inc. Method and apparatus for ultrafiltration of blood
US8603021B2 (en) 2000-05-23 2013-12-10 Gambro Uf Solutions, Inc. Method and apparatus for ultrafiltration of blood
US7935071B2 (en) 2000-05-23 2011-05-03 Chf Solutions, Inc. Method and apparatus for peripheral vein fluid removal in heart failure
US9440018B2 (en) 2000-05-23 2016-09-13 Gambro Lundia Ab Method for ultrafiltration of blood
US20080097273A1 (en) * 2000-05-23 2008-04-24 Chf Solutions, Inc. Method and apparatus for peripheral vein fluid removal in heart failure
US7311689B2 (en) 2000-05-23 2007-12-25 Chf Solutions, Inc. Method and apparatus for peripheral vein fluid removal in heart failure
US8702638B2 (en) 2000-11-02 2014-04-22 Gambro Uf Solutions, Inc. Method for blood withdrawal and infusion using a pressure controller
US7462161B2 (en) 2000-11-02 2008-12-09 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US7955289B2 (en) 2000-11-02 2011-06-07 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US20050230313A1 (en) * 2000-11-02 2005-10-20 Chf Solutions Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US20040030277A1 (en) * 2000-11-02 2004-02-12 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US7674237B2 (en) 2000-11-02 2010-03-09 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US20090149795A1 (en) * 2000-11-02 2009-06-11 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US20040039324A1 (en) * 2000-11-27 2004-02-26 Chf Solutions, Inc. Controller for ultrafiltration blood circuit which prevents hypotension by monitoring osmotic pressure in blood
US7399289B2 (en) 2000-11-27 2008-07-15 Chf Solutions, Inc. Controller for ultrafiltration blood circuit which prevents hypotension by monitoring osmotic pressure in blood
US6923782B2 (en) 2001-04-13 2005-08-02 Chf Solutions, Inc. User interface for blood treatment device
US20070185429A1 (en) * 2001-04-13 2007-08-09 Chf Solutions Inc. Pressure sensor disconnect detection for a blood treatment device
US7647834B2 (en) 2001-04-13 2010-01-19 Chf Solutions Inc. Pressure sensor disconnect detection for a blood treatment device
US20040084358A1 (en) * 2001-04-13 2004-05-06 Chf Solutions, Inc. User interface for blood treatment device
US20100175483A1 (en) * 2001-04-13 2010-07-15 Chf Solutions Inc. Pressure sensor disconnect detection for a blood treatment device
US7886611B2 (en) 2001-04-13 2011-02-15 Chf Solutions Inc. Pressure sensor disconnect detection for a blood treatment device
US20050004502A1 (en) * 2002-02-14 2005-01-06 Chf Solutions, Inc. Method to control blood and filtrate flowing through an extracorporeal device
US6796955B2 (en) 2002-02-14 2004-09-28 Chf Solutions, Inc. Method to control blood and filtrate flowing through an extracorporeal device
US20030152482A1 (en) * 2002-02-14 2003-08-14 O'mahony John J. Method and apparatus for an extracorporeal treatment device to control blood withdrawal and infusion
US7540851B2 (en) 2002-02-14 2009-06-02 Chf Solutions, Inc. Method to control blood and filtrate flowing through an extracorporeal device
WO2003072942A1 (en) * 2002-02-21 2003-09-04 Terumo Cardiovascular Systems Corporation Method and apparatus for controlling fluid pumps
US20070100272A1 (en) * 2002-03-04 2007-05-03 Dennis Briggs Method for collecting a desired blood component and performing a photopheresis treatment
US20100298752A1 (en) * 2002-03-04 2010-11-25 Dennis Briggs Method for collecting a desired blood component and performing a photopheresis treatment
US7850634B2 (en) * 2002-03-04 2010-12-14 Therakos, Inc. Method for collecting a desired blood component and performing a photopheresis treatment
US9238097B2 (en) * 2002-03-04 2016-01-19 Therakos, Inc. Method for collecting a desired blood component and performing a photopheresis treatment
US20060012774A1 (en) * 2002-05-07 2006-01-19 Chf Solutions Inc. Blood leak detector for extracorporeal treatment system
US7230687B2 (en) 2002-05-07 2007-06-12 Chf Solutions Inc. Blood leak detector for extracorporeal treatment system
US6947131B2 (en) 2002-05-07 2005-09-20 Chf Solutions, Inc. Blood leak detector for extracorporeal treatment system
US20030210390A1 (en) * 2002-05-07 2003-11-13 O'mahony John J. Blood leak detector for extracorporeal treatment system
US20080203023A1 (en) * 2002-06-06 2008-08-28 Nxstage Medical, Inc. Last-chance quality check and/or air/pathogen filtger for infusion systems
US8192387B2 (en) 2002-06-06 2012-06-05 Nxstage Medical, Inc. Last-chance quality check and/or air/pathogen filter for infusion systems
US9764074B1 (en) 2002-07-19 2017-09-19 Baxter International Inc. Systems and methods for performing dialysis
US8202420B2 (en) 2003-01-07 2012-06-19 Nxstage Medical, Inc. Batch filtration system for preparation of sterile fluid for renal replacement therapy
US20100228177A1 (en) * 2003-01-07 2010-09-09 Brugger James M Batch filtration system for preparation of sterile fluid for renal replacement therapy
US20090211975A1 (en) * 2003-01-07 2009-08-27 Brugger James M Batch Filtration System for Preparation of Sterile Fluid for Renal Replacement Therapy
US7749393B2 (en) 2003-01-07 2010-07-06 Nxstage Medical, Inc. Batch filtration system for preparation of sterile fluid for renal replacement therapy
US7976711B2 (en) 2003-01-07 2011-07-12 Nxstage Medical, Inc. Batch filtration system for preparation of sterile fluid for renal replacement therapy
US20110186521A1 (en) * 2003-01-07 2011-08-04 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US8679348B2 (en) 2003-01-07 2014-03-25 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US8545428B2 (en) 2003-01-07 2013-10-01 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US9388059B2 (en) 2003-01-07 2016-07-12 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US8460558B2 (en) 2003-01-07 2013-06-11 Nxstage Medical, Inc. Batch filtration system for preparation of sterile fluid for renal replacement therapy
US7410582B2 (en) 2003-04-04 2008-08-12 Chf Solutions Inc. Hollow fiber filter for extracorporeal blood circuit
US20040195165A1 (en) * 2003-04-04 2004-10-07 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US20080060990A1 (en) * 2003-04-04 2008-03-13 Chf Solutions Inc. Hollow fiber filter for extracorporeal blood circuit
US7297270B2 (en) 2003-04-04 2007-11-20 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US7671974B2 (en) 2003-10-29 2010-03-02 Chf Solutions Inc. Cuvette apparatus and system for measuring optical properties of a liquid such as blood
US20050094127A1 (en) * 2003-10-29 2005-05-05 Chf Solutions Inc. Cuvette apparatus and system for measuring optical properties of a liquid such as blood
US9039648B2 (en) 2003-11-05 2015-05-26 Baxter International Inc. Dialysis system with enhanced features
US9072830B2 (en) 2003-11-05 2015-07-07 Baxter International Inc. Systems and methods for priming sorbent-based hemodialysis
US9572919B2 (en) 2003-11-05 2017-02-21 Baxter International Inc. Dialysis system with cassette based balance chambers and volumetric pumps
US9144641B2 (en) 2003-11-05 2015-09-29 Baxter International Inc. Dialysis system with balance chamber prime and rinseback
US9072831B2 (en) 2003-11-05 2015-07-07 Baxter International Inc. Medical fluid pump valve integrity test methods and systems
US8894600B2 (en) 2003-11-05 2014-11-25 Baxter International Inc. Hemodialysis system including on-line dialysate generation
US9072843B2 (en) 2003-11-05 2015-07-07 Baxter International Inc. Renal therapy system having pump reversing fluid control
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
US9050411B2 (en) 2003-11-05 2015-06-09 Baxter International Inc. Dialysis system including downloaded prescription entry
US9480784B2 (en) 2003-11-05 2016-11-01 Baxter International Inc. Dialysis system with balance chamber prime and rinseback
US9028436B2 (en) 2003-11-05 2015-05-12 Baxter International Inc. Hemodialysis system with cassette-based blood and dialyste pumping
US9005152B2 (en) 2003-11-05 2015-04-14 Baxter International Inc. Dialysis system with cassette based balance chambers and volumetric pumps
US9642961B2 (en) 2003-11-05 2017-05-09 Baxter International Inc. Renal failure therapy machines and methods including convective and diffusive clearance
US8926540B2 (en) 2003-11-05 2015-01-06 Baxter Healthcare Inc. Hemodialysis system with separate dialysate cassette
US9421313B2 (en) 2003-11-05 2016-08-23 Baxter International Inc. Hemodialysis system with horizontal cassette roller pumps
US9872950B2 (en) 2003-11-05 2018-01-23 Baxter International Inc. Renal therapy system having pump reversing fluid control
US9387286B2 (en) 2003-11-05 2016-07-12 Baxter International Inc. Dialysis system including peristaltic tubing pumping cassette
US8882692B2 (en) 2003-11-05 2014-11-11 Baxter International Inc. Hemodialysis system with multiple cassette interference
US8858488B2 (en) 2003-11-05 2014-10-14 Baxter International Inc. Dialysis system including blood and dialysate cassette
US9168333B2 (en) 2003-11-05 2015-10-27 Baxter International Inc. Dialysis system including disposable cassette
US9884144B2 (en) 2003-11-05 2018-02-06 Baxter International Inc. Hemodialysis system with cassette-based blood and dialysate pumping
US9889243B2 (en) 2003-11-05 2018-02-13 Baxter International Inc. Dialysis system including automatic priming
US9302039B2 (en) 2003-11-05 2016-04-05 Baxter International Inc. Hemodialysis system including a disposable cassette
US20050131332A1 (en) * 2003-11-05 2005-06-16 Thomas Kelly High convection home hemodialysis/hemofiltration and sorbent system
US9550020B2 (en) 2003-11-05 2017-01-24 Baxter International Inc. Dialysis system with a varying rate ultrafiltration profile
US9216246B2 (en) 2003-11-05 2015-12-22 Baxter International Inc. Renal failure therapy machines and methods including conductive and convective clearance
US9155825B2 (en) 2003-11-05 2015-10-13 Baxter International Inc. Hemodialysis system using sorbent and reservoir
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US8430835B2 (en) 2003-12-16 2013-04-30 Baxter International Inc. Renal therapy blood cleansing system with balance chamber and bolus, rinseback or prime volume feature
US9211370B2 (en) 2003-12-16 2015-12-15 Baxter International Inc. Renal therapy blood cleansing system with isolation feature
US7744553B2 (en) 2003-12-16 2010-06-29 Baxter International Inc. Medical fluid therapy flow control systems and methods
US20100076364A1 (en) * 2004-04-26 2010-03-25 Chf Solutions, Inc. User interface for blood treatment device
US20050256444A1 (en) * 2004-04-26 2005-11-17 Chf Solutions Inc. User interface for blood treatment device
US7585286B2 (en) 2004-04-26 2009-09-08 Chf Solutions, Inc. User interface for blood treatment device
US8197432B2 (en) 2004-04-26 2012-06-12 Gambro Uf Solutions, Inc. User interface for blood treatment device
US7303540B2 (en) 2004-04-26 2007-12-04 Chf Solutions, Inc. User interface for blood treatment device
US7857760B2 (en) 2004-07-13 2010-12-28 Dexcom, Inc. Analyte sensor
US20060095021A1 (en) * 2004-11-02 2006-05-04 Casas-Bejar Jesus W Introduction of agent with medical device
US20060095020A1 (en) * 2004-11-02 2006-05-04 Medtronic, Inc. Introduction of agent with medical device
US8038639B2 (en) 2004-11-04 2011-10-18 Baxter International Inc. Medical fluid system with flexible sheeting disposable unit
US20080230450A1 (en) * 2005-01-07 2008-09-25 Burbank Jeffrey H Filtration System for Preparation of Fluids for Medical Applications
US9700663B2 (en) 2005-01-07 2017-07-11 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US20090182263A1 (en) * 2006-04-07 2009-07-16 Burbank Jeffrey H Filtration system for preparation of fluids for medical applications
US8469331B2 (en) 2006-04-07 2013-06-25 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US9636444B2 (en) 2006-04-07 2017-05-02 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US8774886B2 (en) 2006-10-04 2014-07-08 Dexcom, Inc. Analyte sensor
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US20080086044A1 (en) * 2006-10-04 2008-04-10 Dexcom, Inc. Analyte sensor
US20080086042A1 (en) * 2006-10-04 2008-04-10 Dexcom, Inc. Analyte sensor
US20080200788A1 (en) * 2006-10-04 2008-08-21 Dexcorn, Inc. Analyte sensor
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US9451908B2 (en) 2006-10-04 2016-09-27 Dexcom, Inc. Analyte sensor
US8532730B2 (en) 2006-10-04 2013-09-10 Dexcom, Inc. Analyte sensor
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US8911367B2 (en) * 2006-10-04 2014-12-16 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US7775975B2 (en) 2006-10-04 2010-08-17 Dexcom, Inc. Analyte sensor
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8632487B2 (en) 2007-06-04 2014-01-21 Fresenius Medical Care Deutchland Gmbh Device for controlling a system for transporting blood, and method for transporting blood in a blood line of an extracorporeal blood circuit of an extracorporeal blood treatment device
EP2431064A1 (en) * 2007-06-04 2012-03-21 Fresenius Medical Care Deutschland GmbH Device for controlling a device for conveying blood and method for conveying blood to a blood vessel of an extracorporeal blood circuit of an extracorporeal blood treatment device
WO2008148506A3 (en) * 2007-06-04 2009-04-30 Fresenius Medical Care De Gmbh Device for controlling a system for transporting blood, and method for transporting blood in a blood line of an extracorporeal blood circuit of an extracorporeal blood treatment device
US8562558B2 (en) 2007-06-08 2013-10-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US9741139B2 (en) 2007-06-08 2017-08-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8057423B2 (en) 2007-07-05 2011-11-15 Baxter International Inc. Dialysis system having disposable cassette
US8920362B2 (en) 2007-07-05 2014-12-30 Baxter International Inc. Dialysis system having disposable cassette
US8337449B2 (en) 2007-07-05 2012-12-25 Baxter International Inc. Dialysis system having disposable cassette
US20090012456A1 (en) * 2007-07-05 2009-01-08 Baxter International Inc. Dialysis system having disposable cassette
US9925320B2 (en) 2007-10-24 2018-03-27 Baxter International Inc. Renal therapy machine and system including a priming sequence
US9855377B2 (en) 2007-10-24 2018-01-02 Baxter International Inc. Dialysis system including heparin injection
US8114276B2 (en) 2007-10-24 2012-02-14 Baxter International Inc. Personal hemodialysis system
US8932469B2 (en) 2007-10-24 2015-01-13 Baxter International Inc. Personal hemodialysis system including priming sequence and methods of same
US8834719B2 (en) 2007-10-24 2014-09-16 Baxter International Inc. Personal hemodialysis system
US8329030B2 (en) 2007-10-24 2012-12-11 Baxter International Inc. Hemodialysis system with cassette and pinch clamp
US8323492B2 (en) 2007-10-24 2012-12-04 Baxter International Inc. Hemodialysis system having clamping mechanism for peristaltic pumping
US8992463B2 (en) 2007-11-09 2015-03-31 Baxter International Inc. Balanced flow dialysis machine
US20090124963A1 (en) * 2007-11-09 2009-05-14 Baxter International Inc. Balanced flow dialysis machine
US9415150B2 (en) 2007-11-09 2016-08-16 Baxter Healthcare S.A. Balanced flow dialysis machine
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US9005153B2 (en) 2008-08-21 2015-04-14 Fresenius Medical Care Deutschland Gmbh Method and apparatus for monitoring a peristaltic hose pump for conducting a fluid in a tubing
US20110230814A1 (en) * 2008-08-21 2011-09-22 Pascal Kopperschmidt Method and apparatus for monitoring a peristaltic hose pump for conducting a fluid in a tubing
WO2010020380A1 (en) * 2008-08-21 2010-02-25 Fresenius Medical Care Deutschland Gmbh Method and apparatus for monitoring a peristaltic hose pump for conducting a fluid in a tubing
US9370324B2 (en) 2008-11-05 2016-06-21 Fresenius Medical Care Holdings, Inc. Hemodialysis patient data acquisition, management and analysis system
WO2010065398A1 (en) 2008-12-04 2010-06-10 Therox, Inc. Method and device for combined detection of bubbles and flow rate in a system for enriching a bodily fluid with a gas
US20110196282A1 (en) * 2008-12-19 2011-08-11 Cvdevices, Llc (A California Limited Liability Company) Devices, systems, and methods for autoretroperfusion
US9724214B2 (en) 2008-12-19 2017-08-08 Cvdevices, Llc Retroperfusion systems, devices, and methods
US8888733B2 (en) * 2008-12-19 2014-11-18 Cvdevices, Llc Devices, systems, and methods for autoretroperfusion
US9504781B2 (en) 2008-12-19 2016-11-29 Cvdevices, Llc Peripheral arterialization devices and methods of using the same
WO2011079941A1 (en) * 2009-12-28 2011-07-07 Fresenius Medical Care Deutschland Gmbh Device and method for monitoring an extracorporeal blood treatment
EP3141272A1 (en) * 2009-12-28 2017-03-15 Fresenius Medical Care Deutschland GmbH Device for monitoring an extracorporeal blood treatment device and device for extracorporeal blood treatment
JP2013515523A (en) * 2009-12-28 2013-05-09 フレセニウス メディカル ケア ドイチュランド ゲーエムベーハー Monitoring apparatus and method of extracorporeal blood treatment
US8529491B2 (en) * 2009-12-31 2013-09-10 Fresenius Medical Care Holdings, Inc. Detecting blood flow degradation
US20110160637A1 (en) * 2009-12-31 2011-06-30 Fresenius Medical Care Holdings, Inc. Detecting Blood Flow Degradation
US8743354B2 (en) 2010-09-07 2014-06-03 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US9194792B2 (en) 2010-09-07 2015-11-24 Fresenius Medical Care Holdings, Inc. Blood chamber for an optical blood monitoring system
US9285305B2 (en) 2010-09-07 2016-03-15 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US9173988B2 (en) 2010-11-17 2015-11-03 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
US9801993B2 (en) 2010-11-17 2017-10-31 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
US8517968B2 (en) 2011-02-25 2013-08-27 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US20120310205A1 (en) * 2011-06-06 2012-12-06 Chaoyoung Lee Medical Pump Providing Customizable Programming Permissions
US9378334B2 (en) * 2011-06-06 2016-06-28 Zyno Medical, Llc Medical pump providing customizable programming permissions
US9267500B2 (en) * 2011-07-29 2016-02-23 Fresenius Medical Care Deutschland Gmbh Method as well as apparatuses for detecting a permeability or patency in a tube which is inserted in a tube pump
WO2013017241A1 (en) * 2011-07-29 2013-02-07 Fresenius Medical Care Deutschland Gmbh Method and devices for detecting the permability of a flexible tube inserted into a peristaltic pump
US20130030345A1 (en) * 2011-07-29 2013-01-31 Fresenius Medical Care Deutschland Gmbh Method as well as apparatuses for detecting a permeability or patency in a tube which is inserted in a tube pump
USD725261S1 (en) 2012-02-24 2015-03-24 Fresenius Medical Care Holdings, Inc. Blood flow chamber
USD757934S1 (en) 2012-02-24 2016-05-31 Fresenius Medical Holdings, Inc. Blood flow chamber
US20150165118A1 (en) * 2012-06-06 2015-06-18 Zyno Medical, LLC. Medical Pump with Operator-Authorization Awareness
US20140194817A1 (en) * 2012-06-06 2014-07-10 Zyno Medical, LLC. Medical pump with operator-authorization awareness
US9886550B2 (en) * 2012-06-06 2018-02-06 Zyno Medical, Llc Medical pump with operator-authorization awareness
CN103170024A (en) * 2012-10-18 2013-06-26 郝兴海 Normovolemic dilution autoblood collection and reinfusion system and normovolemic dilution autoblood collection and reinfusion device
US9433721B2 (en) 2013-06-25 2016-09-06 Fresenius Medical Care Holdings, Inc. Vial spiking assemblies and related methods
US9375526B2 (en) 2013-06-25 2016-06-28 Fresenius Medical Care Holdings, Inc. Vial spiking assemblies and related methods
US9968727B2 (en) 2013-08-13 2018-05-15 Cvdevices, Llc Systems, devices, and methods for organ retroperfusion along with regional mild hypothermia
USD799031S1 (en) 2015-09-09 2017-10-03 Fresenius Medical Care Holdings, Inc. Blood flow chamber with directional arrow
CN105597178A (en) * 2015-12-22 2016-05-25 济南市儿童医院 Remote monitoring method, device and equipment of blood purification system

Also Published As

Publication number Publication date Type
WO2002070042A1 (en) 2002-09-12 application
WO2002070042B1 (en) 2002-10-31 application
US7004924B1 (en) 2006-02-28 grant

Similar Documents

Publication Publication Date Title
US6526357B1 (en) Associated parameter measuring and/or monitoring such as in the evaluation of pressure differences
US4995268A (en) Method and apparatus for determining a rate of flow of blood for an extracorporeal blood therapy instrument
US4828543A (en) Extracorporeal circulation apparatus
US20090101577A1 (en) Methods and Systems for Controlling Ultrafiltration Using Central Venous Pressure Measurements
US20090101550A1 (en) Dialysis system having non-invasive fluid velocity sensing
US20070215545A1 (en) Extracorporeal renal replacement modeling system
US7273465B2 (en) Device and methods for body fluid flow control in extracorporeal fluid treatments
US4596550A (en) Method and apparatus for ultrafiltration measurement in a two pump dialysis system
US7087033B2 (en) Method and apparatus for leak detection in a fluid line
US6808508B1 (en) Method and system for closed chest blood flow support
US6280632B1 (en) Device and method for preparation of substitution solution
US20080027368A1 (en) Disposable cartridge for a blood perfusion system
US5213573A (en) Iv administration set infiltration monitor
US6767333B1 (en) Safety device for a blood treatment machine and a method of increasing the safety of a blood treatment machine
US6579257B1 (en) Automated occlusion clamp for centrifugal blood pumps
US7022099B2 (en) Extracorporeal blood handling system with automatic flow control and methods of use
US6916424B2 (en) Method and apparatus for a hemodiafiltration delivery module
US5178603A (en) Blood extraction and reinfusion flow control system and method
US5211201A (en) Intravenous fluid delivery system with air elimination
US20100234786A1 (en) System and Method for Detection of Disconnection in an Extracorporeal Blood Circuit
US5536237A (en) Blood extraction flow control calibration system and method
US5344568A (en) Hemofiltration system and method
US20060015056A1 (en) Disposable cartridge for a blood perfusion system
US5378227A (en) Biological/pharmaceutical method and apparatus for collecting and mixing fluids
US4464164A (en) Flowrate control for a blood flow system