US20070117010A1 - Conductive polymer materials and applications thereof including monitoring and providing effective therapy - Google Patents

Conductive polymer materials and applications thereof including monitoring and providing effective therapy Download PDF

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Publication number
US20070117010A1
US20070117010A1 US11/626,241 US62624107A US2007117010A1 US 20070117010 A1 US20070117010 A1 US 20070117010A1 US 62624107 A US62624107 A US 62624107A US 2007117010 A1 US2007117010 A1 US 2007117010A1
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United States
Prior art keywords
coupler
dialysis
tubing
patient
blood
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Abandoned
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US11/626,241
Inventor
Sherwin Shang
Ramesh Wariar
Angel Lasso
George Lamberson
Dan Marcquenski
Jan Jensen
David Kuhn
Raf Castellanos
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Baxter Healthcare SA
Baxter International Inc
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Baxter Healthcare SA
Baxter International Inc
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Priority to US10/121,006 priority Critical patent/US7138088B2/en
Priority to US10/760,849 priority patent/US20040254513A1/en
Application filed by Baxter Healthcare SA, Baxter International Inc filed Critical Baxter Healthcare SA
Priority to US11/626,241 priority patent/US20070117010A1/en
Assigned to BAXTER INTERNATIONAL INC., BAXTER HEALTHCARE S.A. reassignment BAXTER INTERNATIONAL INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LAMBERSON, GEORGE, WARIAR, RAMESH, JENSEN, JAN, CASTELLANOS, RAF, KUHN, DAVID, LASSO, ANGEL, MARCQUENSKI, DAN, SHANG, SHERWIN
Assigned to BAXTER INTERNATIONAL INC., BAXTER HEALTHCARE S.A. reassignment BAXTER INTERNATIONAL INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LAMBERSON, GEORGE, WARIAR, RAMESH, JENSEN, JAN, CASTELLANOS, RAF, KUHN, DAVID, LASSO, ANGEL, MARCQUENSKI, DAN F., JR., SHANG, SHERWIN
Publication of US20070117010A1 publication Critical patent/US20070117010A1/en
Application status is Abandoned legal-status Critical

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    • A61M1/14Dialysis systems; Artificial kidneys; Blood oxygenators; Reciprocating systems for treatment of body fluids, e.g. single needle systems for haemofiltration, pheris
    • A61M1/16Dialysis systems; Artificial kidneys; Blood oxygenators; Reciprocating systems for treatment of body fluids, e.g. single needle systems for haemofiltration, pheris with membranes
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    • A61M1/16Dialysis systems; Artificial kidneys; Blood oxygenators; Reciprocating systems for treatment of body fluids, e.g. single needle systems for haemofiltration, pheris with membranes
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    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16LPIPES; JOINTS OR FITTINGS FOR PIPES; SUPPORTS FOR PIPES, CABLES OR PROTECTIVE TUBING; MEANS FOR THERMAL INSULATION IN GENERAL
    • F16L25/00Constructive types of pipe joints not provided for in groups F16L13/00 - F16L23/00 ; Details of pipe joints not otherwise provided for, e.g. electrically conducting or insulating means
    • F16L25/01Constructive types of pipe joints not provided for in groups F16L13/00 - F16L23/00 ; Details of pipe joints not otherwise provided for, e.g. electrically conducting or insulating means specially adapted for realising electrical conduction between the two pipe ends of the joint or between parts thereof
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means
    • G01N27/02Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material
    • G01N27/04Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material by investigating resistance
    • G01N27/06Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material by investigating resistance of a liquid
    • G01N27/07Construction of measuring vessels; Electrodes therefor
    • GPHYSICS
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    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means
    • G01N27/02Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material
    • G01N27/04Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material by investigating resistance
    • G01N27/06Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material by investigating resistance of a liquid
    • G01N27/08Investigating or analysing materials by the use of electric, electro-chemical, or magnetic means by investigating the impedance of the material by investigating resistance of a liquid which is flowing continuously
    • G01N27/10Investigation or analysis specially adapted for controlling or monitoring operations or for signalling
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    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14Dialysis systems; Artificial kidneys; Blood oxygenators; Reciprocating systems for treatment of body fluids, e.g. single needle systems for haemofiltration, pheris
    • A61M1/28Peritoneal dialysis ; Other peritoneal treatment, e.g. oxygenation
    • A61M1/287Dialysates therefor
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    • A61M2205/02General characteristics of the apparatus characterised by a particular materials
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Abstract

A coupler includes a conductive polymer material that is so constructed and arranged to join tubing, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophenes, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

Description

    CROSS REFERENCE TO RELATED APPLICATIONS
  • This application is a divisional of patent application Ser. No. 10/760,849, filed Jan. 19, 2004, which is a continuation-in-part of U.S. patent application Ser. No. 10/121,006 filed on Apr. 10, 2002.
  • BACKGROUND OF THE INVENTION
  • The present invention relates generally to conductive polymer materials and methods of preparing and employing same. More specifically, the present invention relates to conductive polymer materials and applications thereof including monitoring patient access disconnection, monitoring solution mixing and compounding and the like during medical therapy, such as dialysis therapy.
  • A variety of different medical treatments relate to the delivery of fluid to and/or from a patient, such as the delivery of blood between a patient and an extracorporeal system connected to the patient via a needle or needles or any suitable access device inserted within the patient. For example, hemodialysis, hemofiltration and hemodiafiltration are all treatments that remove waste, toxins and excess water directly from the patient's blood. During these treatments, the patient is connected to an extracoporeal machine, and the patient's blood is pumped through the machine. Waste, toxins and excess water are removed from the patient's blood, and the blood is infused back into the patient. Needles or other suitable access devices are inserted into the patient's vascular access in order to transfer the patient's blood to and from the extracoporeal machine. Traditional hemodialysis, hemofiltration and hemodiafiltration treatments can last several hours and are generally performed in a treatment center about three to four times per week.
  • During any of these hemo treatments, dislodgment of the access device can occur, such as dislodgment of a needle inserted into the patient's vascular access including an arterio-venous graft or fistula. If not detected immediately, this can produce a significant amount of blood loss to the patient. The risks associated with a needle dislodgment are considerable. In this regard, important criteria for monitoring blood loss include, for example, the sensitivity, specificity and response time with respect to the detection of needle dislodgment. With increased levels of sensitivity, specificity, and response time, the detection of needle dislodgment can be enhanced, and blood loss due to dislodgment can be minimized.
  • Typically, patients undergoing medical treatment, such as hemodialysis, hemofiltration or hemodiafiltration, are visually monitored in order to detect needle dislodgment. However, the needle may not be in plain view of the patient or medical staff (i.e., it may be covered by a blanket) such that it could delay detection and, thus, responsive actions to be taken in view of dislodgment, such as stopping the blood pump of the extracorporeal machine to minimize blood loss to the patient.
  • Moreover, in view of the increased quality of life, observed reductions in both morbidity and mortality and lower costs than in-center treatments, a renewed interest has arisen for self care and home hemo therapies. Such home hemo therapies (whether hemodialysis, hemofiltration or hemodiafiltration) allow for both nocturnal as well as daily treatments. During these self care and home hemo sessions, especially during a nocturnal home hemo session, when the patient is asleep, dislodgment risks are more significant because nurses or other attendants are not present to detect the dislodgment.
  • Although devices that employ a variety of different sensors are available and known for detecting and/or monitoring a variety of different bodily fluids, these devices may not be suitably adapted to detect needle dislodgment. For example, known devices that employ sensors including pH, temperature and conductivity have been utilized to detect bedwetting and diaper wetness. Further, devices that employ pressure sensors and/or flow sensing devices are known and used during medical treatment, such as dialysis therapy, to monitor fluid flow including blood flow to and/or from the patient. However, these types of detection devices may not provide an adequate level of sensitivity and responsiveness if applied to detecting blood loss from the patient due to needle dislodgment. Although venous pressure is known to be used to monitor needle dislodgment, it is not very sensitive to needle drop-out.
  • Additional other devices and methods are generally known to monitor vascular access based on the electrical conductivity of blood. For example, Australian Patent No. 730,338 based on PCT Publication No. WO 99/12588 employs an electrical circuit which includes two points through which current is induced in blood flowing through an extracorporeal circuit in a closed loop. Electrical current is induced by means of a coil that is placed around the outside of the tubing of the blood circuit. Thus, each coil does not directly contact the blood as it circulates through the tubing. In this regard, an electrical current is induced in the blood loop by an alternating current that flows through one of the coils. The second coil is then utilized to measure a change in amperage of the induced current as it flows through the blood circuit.
  • In this regard, electrical current is coupled to a blood treatment system that includes a number of high impedance components, such a blood pump, air bubble traps, pinch clamps and/or the like. Because of the large impedance of the conducting fluid loop (due to the peristaltic pump and other components), the induction and detection of a patient-safe current requires an impractically complex design of the coil and system. Further, a high level of noise would necessarily result from the use of such levels of induced current. This can adversely impact the sensitivity of detection. If lower currents are used, the field coil would have to be increased in size to detect such low current levels. This may not be practical in use, particularly as applied during dialysis therapy.
  • PCT Publication No. WO 01/47581 discloses a method and device for monitoring access to the cardiovascular system of a patient. The access monitoring employs an electrical circuit which can generate and detect a current at separate points along a blood circuit connected to the patient. Electrical current is coupled to the blood using capacitive couplers that each have a metal tube placed around the blood circuit tubing. In this regard, the metal tube defines a first plate of a capacitor; the blood circuit tubing defines the dielectric; and the blood inside of the blood circuit tubing defines the second plate of the capacitor.
  • The generator applies a potential difference between a pair of points to generate a current in a segment of the blood circuit. A detector utilizes an additional and separate pair of contact points to measure the current along at least one section of the venous branch between a first contact point and the venous needle. The change in voltage (dV) can then be determined based on a measured change in current and compared to a reference range (I) to monitor access conditions. In this regard, PCT Publication No. WO 01/47581 requires a complex circuit design that utilizes multiple sets of capacitive couplers to monitor vascular access conditions. This can increase the cost and expense of using same.
  • Further, the mere use of capacitive coupling to inject an electric signal in the blood circuit and/or for detection purposes can be problematic. In this regard, the signal must pass through the tubing of the blood circuit as the tubing acts as a dielectric of the capacitor. This may cause an excess level of noise and/or other interference with respect to the detection of changes in vascular access conditions.
  • In this regard, it is believed that known devices, apparatuses, systems, and/or methods that can be used to monitor a patient's access conditions may not be capable of detecting change in access conditions, such as in response to needle drop-out, with sufficient sensitivity and specificity to ensure immediate detection of blood loss such that responsive measures can be taken to minimize blood loss. As applied, if twenty seconds or more of time elapses before blood loss due to, for example, dislodgment of the venous needle, over 100 milliliters in blood loss can occur at a blood flow rate of 400 ml/min, which is typical of dialysis therapy. Thus, the capability to respond quickly upon immediate detection of dislodgment of an access device, such as a needle, from a patient is essential to ensure patient safety.
  • In addition to dislodgement, additional other parameters are, in general, monitored to evaluate changes thereof during medical procedures including dialysis therapy. For example, temperature sensors, pressure sensors, conductivity sensors and the like are generally known and used in a variety of ways to detect and monitor condition changes during medical therapy.
  • As applied to dialysis therapy and the like, a dialysis solution can be administered to a patient in mixed form. In this regard, the extent to which the solution is mixed can have an impact on the effectiveness of the associated therapy. In dialysis therapy, the solutions may have varying pH levels that are at levels considered to be non-physiologic prior to mixing, while after mixing, the final solution is required to have a pH at a physiological level necessary for effective and safe administration during therapy. In general, conductivity sensors and pH sensors are known and used. However, it is believed that known sensors may not be as effective in terms of detection capabilities and relative ease of use, particularly as applied during dialysis therapy.
  • Accordingly, efforts have been directed at designing apparatuses, devices, systems and methods for improved monitoring of patient therapy, such as detecting changes in patient access conditions in response to needle dislodgment, detecting changes in solution compounding and mixing, and the like, wherein detection is sensitive, specific and immediate in response to such changes such that responsive measures can be suitably taken to provide the patient with effective therapy, such as dialysis.
  • SUMMARY OF THE INVENTION
  • The present invention provides improved devices, apparatuses, systems and methods that utilize electrically conductive materials to monitor a variety of different conditions or parameter changes associated with the administration of one or more solutions during medical therapy. In turn, this can facilitate the safe and effective administration of the medical therapy, such as dialysis therapy.
  • In an embodiment, the conductive material includes a polymer conductive material that can include, for example, a polymer conductive component or a polymer matrix and a separate conductive component that is incorporated within the polymer matrix. The conductive materials of the present invention can be utilized in a number of different applications. For example, the conductive materials, such as the conductive polymer material, can be employed to monitor solution mixing and compounding. This can be utilized to evaluate whether the solution or solutions have been effectively mixed prior to administration during therapy. This can be determined by monitoring a pH change in the solution based on changes in conductivity. In this regard, the solution can be derived from a mixture of solution components with varying pH levels, such as between about 1.8 to about 9.2. Thus, the present invention can be utilized to determine whether the pH of the mixed solution is effectively maintained prior to use.
  • The present invention provides improved devices, apparatuses, systems, and methods for detecting dislodgment or disconnection of an access device, such as dislodgment of a needle inserted in a patient during dialysis therapy. The devices, apparatuses, systems, and methods of the present invention utilize an electrical circuit with a number of electrical contacts which are in fluid contact with the fluid circuit such that an electrical signal can be injected into at least a segment including, for example, a loop defined along at least a portion of the conducting fluid circuit. In this regard, a direct-contact measurement can be used to provide immediate detection of a change in an electrical value in response to a change in access conditions, such as a change in impedance due to dislodgment of a needle or other access device from the patient during medical therapy including, for example, dialysis therapy and medication delivery.
  • An advantage of the present invention is to provide an improved device, apparatus, system and/or method for monitoring patient therapy, such as for detecting patient access disconnection, for monitoring solution compounding and the like.
  • Another advantage is to provide devices, apparatuses, systems and methods that employ electrically conductive materials, such as conductive polymer materials, to monitor patient therapy, such as dialysis.
  • A further advantage of the present invention is to provide an improved device, apparatus, system and/or method for detecting dislodgment of an access device from a patient during medical therapy including dialysis therapy.
  • Yet another advantage of the present invention is to provide a sensitive, specific and responsive apparatus and/or device for monitoring patient therapy, such as for detecting access disconnection during selfcare and home hemo treatments and for monitoring solution mixing conditions, such as pH changes, prior to use.
  • Moreover, an advantage of the present invention is to provide a viable device or apparatus for allowing a patient or other non-medical personnel in a non-medical facility to administer a dialysis therapy that uses a portion of the patient's circulatory system.
  • Furthermore, an advantage of the present invention is to provide an improved device, system and method for monitoring and/or controlling blood loss from a patient.
  • Yet another advantage of the present invention is an improved device for connecting an electrical contact to a fluid circuit allowing fluid and electrical communication between the electrical contact and fluid flowing through the fluid circuit.
  • Yet a further advantage of the present invention is to facilitate the safe and effective administration of medical therapy, such as dialysis therapy.
  • Additional features and advantages of the present invention are described in, and will be apparent from, the following Detailed Description of the Invention and the figures.
  • BRIEF DESCRIPTION OF THE FIGURES
  • FIG. 1A illustrates a schematic view of an embodiment of the present invention showing two needles insertable within a patient through which blood flows to and from an extracorporeal system.
  • FIG. 1B illustrates a schematic view of an embodiment of the present invention capable of detecting needle dislodgment during dialysis therapy.
  • FIG. 1C illustrates a perspective view of an embodiment of the present invention showing access disconnection detection capabilities during medical therapies administered via a single needle.
  • FIG. 2A illustrates an exploded view of an electrical contact coupling device in an embodiment of the present invention.
  • FIG. 2B illustrates a side sectional view of the coupling device of FIG. 2A in an embodiment of the present invention.
  • FIG. 2C illustrates another embodiment of the coupling device of the present invention.
  • FIG. 2D illustrates another embodiment of the coupling device of the present invention showing a threaded engagement between the components of same.
  • FIG. 2E illustrates a sectional view of FIG. 2D.
  • FIG. 3 schematically illustrates an embodiment of the present invention relating to processing of a measurable voltage signal to correct for changes in baseline impedance during treatment.
  • FIG. 4A schematically illustrates a hemodialysis machine in an embodiment of the present invention.
  • FIG. 4B schematically illustrates a hemodialysis machine coupled to a patient's access via a tubing set in an embodiment of the present invention.
  • FIGS. 5A and 5B illustrate a coupler according to an embodiment of the present invention.
  • FIG. 6 illustrates a dialyzer according to an embodiment of the present invention.
  • FIGS. 7A and 7B illustrate a sensor assembly according to an embodiment of the present invention.
  • FIGS. 8A and 8B illustrate a single-piece sensor according to an embodiment of the present invention.
  • FIG. 9 illustrates a multi-chamber bag according to an embodiment of the present invention.
  • FIG. 10 illustrates a multi-chamber bag with a peelable seal according to an embodiment of the present invention.
  • FIG. 11 illustrates an automated peritoneal dialysis system according to an embodiment of the present invention.
  • DETAILED DESCRIPTION OF THE INVENTION
  • The present invention generally relates to electrically conductive materials that can be effectively employed to monitor patient therapy. This can facilitate the safe and effective administration of patient therapy, such as dialysis therapy. In an embodiment, the conductive materials of the present invention include a conductive polymer material as described below in greater detail.
  • The present invention provides medical devices, apparatuses, systems and methods for detecting access disconnection. More specifically, the present invention provides medical devices, apparatuses, systems, and methods that employ, in part, an electrical circuit with electrical contacts in fluid contact and electrical communication with a fluid circuit allowing a direct conductivity measurement to be used such that dislodgment of a needle or other access device through which fluid flows between a patient and the fluid circuit can be immediately detected. In this regard, fluid loss (i.e., blood loss) due to, for example, dislodgment of a needle from a patient undergoing medical treatment, such as dialysis therapy, medication delivery or the like, can be controllably minimized. In an embodiment, the conductive polymer materials of the present invention can be utilized to monitor solution compounding and mixing to ensure effective administration of the mixed solution during therapy, such as to determine whether a pH level of the mixed solution is effectively maintained prior to use.
  • It should be appreciated that the present invention is not limited to the detection of needle dislodgment but can be utilized to detect the dislodgment or disconnection of any suitable access device. As used herein, the term “access disconnection” or other like terms means any suitable condition or event which can cause a loss or leak of an electrically conductive fluid flowing along a fluid circuit connected to the patient provided that a change in the electrical continuity between electrical contacts coupled to the fluid circuit can be detected. It should be appreciated that a change in the electrical continuity as measured by an electrical value, such as impedance, may be detected even in the absence of dislodgment of an access device from the patient. The term “access device” as used herein or other like terms means a suitable device that can be inserted within a patient such that fluid, including blood, can pass to, through and/or from the patient via the access device. The access device can include a variety of different and suitable shapes, sizes and material make-up. Examples of an access device includes needles, catheters, cannulas or the like. The access device can be composed of any suitable material including, for example, stainless steel, plastic or like biocompatible materials.
  • Although in the embodiment set forth below the apparatus and/or device is designed for use in a dialysis therapy, such as hemodialysis, hemofiltration or hemodiafiltration, it should be noted that the present invention can be used in a number of different medical therapies that employ a variety of different and suitable fluid systems, such as extracorporeal blood systems. For example, the invention of the present application can be used during intravenous infusion that can employ the use of a single needle insertable within the patient for delivering a medical solution or drug, blood, blood products, processed blood or the like between the patient and the fluid system. In addition, the present invention can be used in plasma exchange therapies, where a membrane is used to separate whole blood into plasma and cellular components.
  • With respect to dialysis therapy, the present invention can be used in a variety of different therapies to treat kidney failure. Dialysis therapy as the term or like terms are used throughout the text is meant to include and encompass any and all forms of therapies that utilize the patient's blood to remove waste, toxins and excess water from the patient. Such therapies include both intermittent, including hemodialysis, hemofiltration and hemodiafiltration, and continuous therapies used for continuous renal replacement therapy (CRRT). These continuous therapies include slow continuous ultrafiltration (SCUF), continuous veno-venous hemofiltration (CVVH), continuous veno-hemodialysis (CVVHD), and continuous veno-venous hemodiafiltration (CVVHDF). Dialysis therapy can also include peritoneal dialysis, such a continuous ambulatory peritoneal dialysis, automated peritoneal dialysis and continuous flow peritoneal dialysis. Further, although the present invention, in an embodiment, can be utilized in methods providing a dialysis therapy for patients having chronic kidney failure or disease, it should be appreciated that the present invention can be used for acute dialysis needs, for example, in an emergency room setting. Lastly, as one of skill in the art appreciates, the intermittent forms of therapy (i.e., hemofiltration, hemodialysis and hemodiafiltration) may be used in the in center, self/limited care as well as the home settings.
  • In an embodiment, the present invention includes an electrical circuit with a number of electrical contacts, preferably a pair of electrical contacts, in fluid contact and electrical communication with the fluid circuit. The electrical contacts can include any suitable device through which electrical connection can be made with the fluid circuit thereby defining a conductive pathway or conductor loop therein. In an embodiment, at least one of the electrical contacts includes a conductive polymer material as described below in greater detail. Changes in an electrical value or any suitable parameter associated with the conductor loop can then be monitored in response to changes in access conditions as described below. In an embodiment, the electrical contact includes an electrode which can be coupled to the fluid circuit such that an electrical connection can be made in fluid contact with fluid flowing through the fluid circuit as discussed below.
  • For example, a constant current or other suitable electrical signal can be injected into the fluid circuit via an electrode pair in contact with the fluid flowing in between the electrodes thereby defining a loop along at least a portion of the conducting fluid circuit. A change in an electrical value, preferably impedance, can then be measured in response to access disconnection. This can provide a direct conductivity measurement capable of detecting a change in impedance or other suitable electrical parameter of the fluid, such as an electrically conductive fluid including blood, medical solutions or the like, as it flows between a patient and a fluid system (i.e., an extracorporeal blood system) via a needle, needles or other access device(s) inserted within the patient.
  • In this regard, the present invention can effectively detect dislodgment of a needle (e.g., a venous needle and/or an arterial needle) or other access device through which blood or other suitable fluid can flow, for example, to, through, and from the patient, such as a blood circuit used during dialysis therapy. The detection capability of the present invention is believed to be immediate based on the measurable change in, for example, impedance of the electrically conductive fluid or fluids due to fluid loss resulting from disconnection of the access device from the patient.
  • The immediate detection capabilities of the present invention are important, particularly as applied to dialysis therapy where a significant amount of blood loss can occur within a relatively short period of time if delays in detection and responsive actions to stop the blood loss occur. Under typical dialysis conditions, if 20 seconds or more time elapses before blood loss due to dislodgment is detected and stopped, over 100 milliliters of bloods can be lost based on typical blood flow rates of 400 milliliters/minute.
  • Applicants have discovered that the present invention can detect access disconnection, particularly in response to venous needle dislodgment during dialysis therapy, with a high degree of sensitivity and specificity in addition to its immediate detection capabilities. The direct-contact measurement of the present invention is capable of detecting a change of an electrical value, preferably impedance, due to needle dislodgment or the like as the blood flows through the blood circuit during dialysis therapy. As used herein, the term “electrical value” or other like terms means any suitable electrical parameter such as, impedance, resistance, voltage, current, rates of change thereof and combinations thereof. The detection of a change in impedance or the like is an indication that the needle has become dislodged or other like condition has occurred. It is noted that the detection capabilities of the present invention can also effectively detect blood loss during medical therapy resulting from a disconnection in the fluid circuit, even if the needle or needles have not become dislodged. In this regard, the present invention can be effectively utilized to controllably minimize blood loss from the patient based on the ability of the present invention to immediately measure a change in impedance or the like due to blood loss with a high degree of sensitivity and specificity. This can facilitate the safe and effective administration of patient therapy as previously discussed.
  • The devices and apparatuses of the present invention can include a variety of different components and configurations depending on the applied medical therapy such that fluid loss, particularly blood loss due to needle dislodgment or the like, can be effectively monitored.
  • Multiple Access Disconnection
  • Referring now to FIG. 1A, an embodiment of the apparatus 10 of the present invention includes a pair of electrical contacts 12 in fluid contact with a blood tubing set 14 of a blood circuit 16. The blood circuit 16 connects a patient 18 to an extracorporeal blood system 20 as applied to, for example, dialysis therapy including hemodialysis, hemofiltration, hemodiafiltration, continuous renal replacement or the like or plasma therapies. The pair of electrical contacts 12 includes a first electrical contact 22 and a second electrical contact 24 which are attached to a respective first tube member 26 and second tube member 28 of the blood circuit 16. The first tube member 26 is connected to a venous needle or other suitable access device inserted into a vascular access region (not shown) of the patient. The second tube member 28 is connected to an arterial needle or the like also inserted into a vascular access region (not shown) of the patient. During dialysis therapy, for example, blood flows from the patient 18 through the arterial needle to the extracorporeal blood system 20 that includes, for example, a dialysis machine, via the second tube member 28 where the blood is treated and delivered to the patient 18 through the venous needle via the first tube member 26.
  • As the blood flows through the blood circuit during dialysis therapy, a constant electric current or the like generated by a controller 29 can be injected or passed into the flowing blood via the electrical contact pair, preferably an electrode pair as described below. In an embodiment, at least one additional electrode can also be utilized in any suitable manner.
  • The electrode pair connected to the controller 29 or other suitable electronic device can then be used to measure a voltage change across an unknown fluid (e.g., blood) impedance or other like electrical value to detect a change in impedance or the like across the vascular access region. In an embodiment, one electrode can be used to inject the electrical signal into the fluid circuit while the other electrode of the pair can be used to sense a change in the electrical value and pass an electrical signal indicative of the same to the controller for processing and detection purposes. Upon dislodgment of at least one of the venous needle and arterial needle from the blood circuit or other suitable condition, an immediate and detectable increase in impedance or the like can be measured as compared to the impedance or other suitable parameter measured under normal operating conditions.
  • It should be appreciated that the present invention as embodied in FIG. 1A can be modified in a variety of suitable ways depending on the medical therapy as applied. For example, the venous and arterial needles can be inserted into the vascular access of the patient on any suitable part of the patient's body, such as the upper arm, lower arm, upper thigh area or the like during dialysis therapy. As previously discussed, the present invention can be applied to a variety of different medical therapies including intravenous infusions, plasma exchanges, medication delivery, drug delivery, blood delivery and dialysis therapies (i.e., hemofiltration, hemodialysis, hemodiafiltration and continuous renal replacement).
  • As illustrated in FIG. 1B, an embodiment of an apparatus 30 of the present invention is shown as applied during dialysis therapy. In an embodiment, the present invention includes a venous needle 32 and arterial needle 34 inserted within a patient access 36. The venous needle 32 and arterial needle 34 are connected to the dialysis system 35 via a number of tube members 38 that connect the various components of the dialysis system 35 including, for example, a venous drip chamber 40, a dialyzer 42, an arterial drip chamber 44 and a blood pump 46. It should be appreciated that one or more of the components of the dialysis system can be provided within a dialysis machine coupled to the blood circuit. As shown in FIG. 1B, a first electrical contact coupling device 48 and a second electrical contact coupling device 50 are positioned between the dialysis system 35 and the venous needle 32 and the arterial needle 34. As used herein, the term “electrical contact coupling device, “coupling device” or other like terms means any suitable device that can be used to connect an electrical contact to the fluid circuit. In an embodiment, the electrical contact coupling device can be used to contact the electric contact to the fluid circuit allowing fluid contact and electrical connection with the fluid flowing through the fluid circuit as described below.
  • In an embodiment, the electrical contact pair, preferably an electrode pair, is connected to a controller 52 or other suitable electronic device. The controller can be used to inject an electric signal via the electrode pair and into the blood and/or other fluid as it flows through the blood circuit. This provides a conductor loop along which changes in electrical parameters or values can be measured. The controller 52 which is coupled to the electrode pair can also be used to measure this change. It should be appreciated that the controller can include a single electronic device or any suitable number of devices in electrical connection with the electrical contacts to input an electrical signal into the blood circuit thereby defining a conductor loop, to measure a change in an electrical parameter or value associated with the conductor loop and/or perform any other suitable tasks, such as processing the detectable signal as discussed below.
  • Preferably, the electrical signal is generated from a constant current that is supplied to the electrodes until dislodgment occurs. The voltage across an unknown impedance of the fluid (e.g., blood) circulating through the blood circuit can then be measured (not shown) to detect a change in impedance due to changes in access conditions. However, it should be appreciated that any suitable electrical parameter and changes thereof can be monitored to detect needle drop-out or the like as previously discussed.
  • As demonstrated below, the detection capabilities of the present invention are highly sensitive, specific and virtually immediate in response to access disconnection, such as needle dislodgment. Further, the electronic circuit of the present invention is relatively simple in design such that preferably one electrode pair is necessary to conduct direct conductivity measurement. This can reduce costs and effort as compared to known vascular access monitoring techniques that only employ non-invasive detection techniques, such as, capacitive couplers and induction coils as previously discussed.
  • Applicants have discovered that the total impedance measured (“Z”) can be modeled as two lumped impedances in parallel with one impedance (“ZD”) being produced by the pump segment, the dialyzer, the drip chambers and/or other suitable components of the dialysis system and/or the like. The other impedance component (“ZP”) is formed by the patient's vascular access and associated tubing which carries blood to and from the vascular access and/or the like. In this regard, the total impedance measured can be characterized as a function of both ZD and ZP as follows:
    Z=(1/Z D+1/Z P)−1
  • Despite this parallel impedance, Applicants have discovered that the electrical contacts in connection with the controller can be used to measure a change in impedance along the conductor loop as blood flows through the blood circuit in response to access disconnection, such as needle dislodgment. If needle dislodgment occurs, the conductor loop along at least a portion of the fluid circuit changes from a closed circuit to an open circuit and thus Z=ZD where ZP approaches infinity. In this regard, the direct conductive measurement capabilities of the present invention can be effectively used to detect access disconnection.
  • Applicants note that the ZD component can produce a level of electrical interference associated with the time-varying high impedance of the components of a medical system coupled to the fluid circuit, such as a dialysis system and its components including, for example, a blood pump, a drip chamber and/or the like. Applicants have discovered that the interference due to the ZD component can be effectively eliminated, or at least reduced, if necessary. In an embodiment, the signal associated with the detection of Z or the like can be further processed as discussed below. Alternatively, in an embodiment, the electrical circuit of the present invention can be designed to block or bypass one or more components of the dialysis system from the conductor loop or pathway defined along the blood circuit as described below. In this regard, the accuracy, sensitivity and responsiveness with respect to the detection of access disconnection can be enhanced.
  • In an embodiment, a third electrical contact point 53 can be utilized to minimize or effectively eliminate the interferences with respect to the high impedance components coupled to the blood circuit, such as the blood pump and the like. The additional contact point can be made in any suitable way. For example, the third contact point can be an electrode or other suitable device through which electrical continuity can be established between it and one of the electrodes of the coupling devices. In an embodiment, the third electrical contact can be attached to a fluid circuit in fluid and electrical communication with fluid flowing through same.
  • The third contact point 53 can be positioned at any suitable position along the blood circuit. Preferably, the third contact point 53 is positioned at any suitable location between the blood pump 46 and the coupling device 50 as shown in FIG. 1B. An equalization potential can then be applied between the third contact point 53 and the electrode of the coupling device 50. The potential is applied at a voltage that is equal to the potential applied between the electrodes of the first coupling device 48 and the second coupling device 50.
  • This effectively causes the electric current or the like, once injected into the blood circuit, to bypass one or more of the components of the dialysis system. In an embodiment, the third contact point 53 can be positioned such that the electric current or the like would effectively bypass all of the components of the dialysis system as shown in FIG. 1B.
  • Single Access Disconnection
  • The electrical contacts of the present invention can be positioned in any suitable location relative to the needle, needles or suitable access device inserted within the patient. As illustrated in FIG. 1C, an embodiment of the present invention as applied with respect to the detection of access detection, such as the dislodgment of a single access device inserted within the patient is shown. This type of application is applicable to a variety of different and suitable medical therapies administered via a single access device, such as a single needle, including intravenous infusion and dialysis therapy including hemodialysis, hemofiltration, hemodiafiltration and continuous renal replacement.
  • As applied, an electrically conductive fluid, such as blood, a blood product, a medical fluid or the like flows between the patient and a fluid system via a single access device. Dislodgment detection of a single access device can include, for example, the detection of needle dislodgment during the delivery of any suitable and electrically conductive fluid or fluids including, for example, blood or medical drug or solution (i.e., a medication contained in an electrically conductive fluid, such as saline), processed blood, blood products, intravenous solutions, the like or combinations thereof. The fluid delivery can be made between a suitable container, such as blood bags or like fluid delivery devices, and a patient. In this regard, immediate and responsive detection of access disconnection via the present invention can be effectively utilized to monitor and control the transfer of blood or a medical fluid, such as a medication or drug, during medical therapy administered via a single needle.
  • As shown in FIG. 1C, an embodiment of the apparatus or device 54 of the present invention includes an access device 56; such as a needle, inserted into a blood vessel 58 within a needle insertion site 60 of the patient 62. The needle 56 is connected to the fluid system 63, such as a fluid infusion system, via a tube member 64. The infusion system includes, for example, an infusion pump 66 for transferring the blood or the like from a container 68 (e.g., blood bag) to the patient. A first electrical contact 70 is spaced apart from the needle 56 along the tube member 64 and a second electrical contact 72 is attached to the patient near the insertion site 60. The first electrical contact 70 is in fluid contact with the fluid as it flows from the delivery container 68 to the patient.
  • In this configuration, the first and second electrical contacts, preferably electrodes, can be used to monitor changes in an electrical value, preferably impedance, within a conductor loop formed by at least a portion of the fluid circuit as an electric signal passes therein. In an embodiment, at least one of the electrical contacts can include a conductive polymer material as described below in greater detail. The electrical contact points can be coupled to an electronic device 74 which is capable of processing a detectable signal transmitted through the electrodes in response to a change in impedance or the like due to dislodgment of the single access device as described in detail below. Preferably, the electrical signal is generated by a constant current supplied to the electrodes such that a direct conductivity measurement can be conducted to detect a change in impedance or the like in response to changes in vascular access conditions, such as dislodgment of the access needle.
  • It is believed that the measured impedance, in the single needle application, is a function of both the impedance of the fluid (i.e., blood) and the impedance as measured across the insertion site. In this regard, the electronic device 74 can be adjusted to detect the impedance at the level equivalent to the combined impedance of all items of the electrical path (i.e., the conductive fluid in the tube, needle, blood stream of venous vessel, body tissue, impedance across the skin with respect to the sensing electrode 72 and the like).
  • Electrical Contacts
  • As previously discussed, the electrical contacts of the present invention are in fluid contact with the fluid as it flows through the fluid circuit. In this regard, the electrical contacts can be utilized to monitor changes in conditions associated with patient therapy. For example, the electrical contacts allow for a direct conductivity measurement which is capable of immediately detecting, with high sensitivity and specificity, a change (e.g., an increase) in impedance or the like due to access disconnection, such as dislodgment of a venous needle (arterial needle or both) from the blood circuit during dialysis therapy. Other types of monitoring applications include monitoring conductivity changes in response to solution compounding as described below in greater detail. It should be appreciated that the present invention can be utilized to monitor one or a combination of condition changes.
  • The electrical contacts can be composed of any suitable conductive and biocompatible material, such as, any suitable electrode material including stainless steel, other suitable conductive materials or combinations thereof. It is essential that the electrode material is biocompatible. In an embodiment, the electrical contact includes a conductive polymer material as described below in greater detail.
  • It should be appreciated that the electrical contacts can be constructed in a variety of different shapes and sizes, illustrative examples of which are described below. For example, the electrical contacts can be configured or designed as a plaster electrode which includes an agent capable of expanding when in contact with moisture. The agent can include a variety of suitable materials including gels that are known to expand more than ten times in volume upon contact with moisture.
  • In an embodiment, the plaster electrode can be utilized to detect fluid (i.e., blood leakage) at an insertion site of an access device insertable within a patient during the administration of medical therapy via a single access device as previously discussed. Upon contact with the fluid, the plaster electrode would necessarily expand to such an extent that the electrode contact is broken, thus causing a detectable increase in impedance of the fluid as it flows from the fluid system to the patient via the needle.
  • In an embodiment, one or more electrodes (not shown), such as one or more plaster electrodes as previously discussed, can be used in combination with the electrical contact pair as shown, for example, in FIGS. 1A and 1B. For example, a plaster electrode can be attached to the patient near the insertion site of either or both of the arterial and venous needles. In this regard, the plaster electrode(s) can be utilized to detect leakage of fluid, such as blood, from the insertion site of the access device(s).
  • In an embodiment, an electrode pair is coupled to the blood circuit in an invasive manner (illustrated in FIGS. 2A-2C as discussed below) such that the electrodes contact the blood as previously discussed. An excitation source that includes a constant current source or the like can be applied to the electrodes to inject an electric signal into the blood circuit thereby defining a conductor loop along which direct conductivity measurements can be performed.
  • To ensure patient safety, the excitation source is typically isolated from the instrument power. Preferably, the excitation source produces a constant electrical current that passes through the blood via the electrodes. Any suitable amount of current can be generated for detection purposes. In an embodiment, the electrical current as it passes through the blood is maintained at a level of about 10 microamperes or less, preferably about 5 microamperes or less. It should be appreciated that the present invention can be operated at low levels of current (e.g., 10 microamperes or less) such that the level of current has negligible, if any, effect on the health and safety of the patient.
  • It should be appreciated that the impedance or other suitable parameter can be measured and calculated in a variety of different and suitable ways. For example, the amplitude, phase and/or frequency of the constant current excitation source can be measured and varied during the detection of a change in impedance. Impedance levels can then be detected by measuring the voltage across the electrodes In this regard, the amplitude, frequency and/or phase of the voltage can then be measured and utilized in combination with the measured amplitude, frequency and/or phase of the excitation source to calculate blood impedance levels based on derivations or equations which are typically used to calculate impedance.
  • The electrical contacts can be connected to the blood circuit in a variety of different and suitable ways. For example, the electrical contacts can be an integral component of the extracorporeal system, a disposable component that can be connected and released from the tubing members of the blood circuit, a reusable component that can be autoclaved between uses, or the like.
  • Electrical Contact Coupling Device
  • In an embodiment, the apparatus of the present invention includes an electrical contact coupling device that can be utilized to secure the electrical contacts, preferably electrodes, to the blood circuit such that the electrodes effectively contact the blood and, thus, can be used to effectively monitor changes in access conditions as previously discussed. In an embodiment, at least one of the electrical contacts includes a conductive polymer material as described below. The coupling device of the present invention can also be designed to facilitate the protection of the user against contact with potential electrical sources. In an embodiment, the device can include a conductive element connected to a tube, through which a medical fluid can flow wherein the conductive element has a first portion exposed to the medical fluid, such as blood, and a second portion external to the tube.
  • The coupling device of the present invention can include a variety of different and suitable configurations, components, material make-up or the like. In an embodiment, the present invention can include a device for connecting an electrical contact to a fluid conduit providing fluid and electrical communication between the electrical contact and fluid flowing through the fluid conduit. The device can include a first member including an annular portion capable of accommodating the electrical contact and a first stem portion connected to the annular member wherein the stem portion has an opening extending therethrough to the annular portion; a second member including a base portion with a groove region and a second stem portion with an opening extending therethrough to the groove region allowing the first member to be inserted and secured to the second member; and a contact member adapted to fit the first and second stem portions allowing the contact member to abut against at least a portion of the electrical contact member allowing an electrical connection to be made between the electrical contact and the contact member. Illustrative examples of the electrical contact coupling device of the present invention are described below.
  • As illustrated in FIGS. 2A and 2B, the electrical contact coupling device 80 includes a probe member 82 that has a cylindrical shape with an opening 84 extending therethrough. In this regard, an electrical contact, preferably an electrode 86 having a cylindrical shape can be inserted into the opening 84 such that the electrode 86 is secure within the probe member 82. In an embodiment, the probe member 82 has a channel 85 extending along at least a portion of the opening 84 within which the electrode 86 can be inserted into the probe member 82. A tube member, for example, from a blood tubing set, connector tube member of a dialysis machine or the like, can be inserted into both ends of the opening 84 of the probe member 82 in contact with an outer portion of the channel 85 allowing blood or other suitable fluid to make fluid contact with the electrode 86 in any suitable manner. The electrode 86 has an opening 88 that extends therethrough within which blood (not shown) or other suitable fluid from the fluid circuit can flow. In an embodiment, the diameter of the opening 88 of the electrode 86 is sized to allow blood flow through the electrode 86 such that blood flow levels under typical operating conditions, such as during dialysis therapy, can be suitably maintained. In this regard, the coupling device of the present invention can be readily and effectively attached to a fluid circuit, including a blood circuit or the like, for use during medical therapy including, for example, dialysis therapy. It should be appreciated that the coupling device 80 of the present invention can be attached to the fluid circuit in any suitable way such that electrical and fluid connection can be made with the fluid flowing through the fluid circuit.
  • The probe member 82 also includes a stem portion 90 that extends from a surface 92 of its cylindrical-shaped body. The stem portion 90 has an opening 93 that extends therethrough. In an embodiment, the stem portion 90 is positioned such that at least a portion of the electrode 86 is in contact with the opening 93 of the stem portion 90.
  • In order to secure the electrode 86 to the blood circuit, the coupling device 80 includes a socket member 94 that includes a body portion 96 with an opening 98 for accepting the probe member 82 and for accepting a blood tube member (not shown) of the blood circuit such that blood directly contacts the electrode as it circulates through the blood circuit during dialysis therapy. In an embodiment, the socket member 94 includes a stem portion 100 extending from the body member 96 wherein the stem portion 100 includes an opening 102 extending therethrough. As the probe member 82 is inserted through the opening 98 of the body member 96, the stem portion 90 of the probe member 82 can be inserted into the opening 102 of the stem portion 100 of the body 96 of the socket member 94.
  • In an embodiment, the socket member 94 includes a groove region 104 extending along at least a portion of the body 96 of the socket member 94. In this regard, the probe member 82 can be inserted through the opening 98 and then moved or positioned into the groove region 104 to secure the probe member 82 within the body 96 of the socket member 94.
  • In an embodiment, the coupling device 80 includes an electrical contact member 106 that is inserted within the opening 102 of the stem portion 100 of the body 96 of the socket member 94 such that the electrical contact member 106 extends through the opening 93 of the stem portion 90 of the probe member 82 to contact at least a portion of a surface 108 of the electrode 86.
  • The electrical contact member 106 is utilized to connect the electronics (not shown) of, for example, the excitation source, a signal processing device, other like electronic devices suitable for use in monitoring and/or controlling changes in access conditions, such as needle dislodgment. The electrical contact member 106 can be made of any suitable material, such as any suitable conductive material including, stainless steel, other like conductive materials or combinations thereof. In order to secure the electrical contact member 106 in place, a contact retainer member 110 is inserted within the opening 102 of the stem portion 100 at an end region 112 thereof.
  • In an embodiment, the coupling device is mounted to a dialysis machine, device or system in any suitable manner. For example, the coupling device can be mounted as an integral component of the dialysis machine. As well, the coupling device can be mounted as a separate and/or stand alone component which can interface with any of the components of the apparatus and system of the present invention. In an embodiment, the coupling device 80 can be insertably mounted via the stem portion 100 of the socket member 94 to a dialysis machine or other suitable components.
  • It should be appreciated that the electrical contact coupling device can include a variety of different and suitable shapes, sizes and material components. For example, another embodiment of the coupling device is illustrated in FIG. 2C. The coupling device 114 in FIG. 2C is similar in construction to the coupling device as shown in FIGS. 2A and 2B. In this regard, the coupling device 114 of FIG. 2C can include, for example, a cylindrical-shaped electrode or other suitable electrical contact, a probe member for accepting the electrode and securing it in place within a socket member of the sensing device. The probe member includes a stem portion that is insertable within a stem portion of the socket member. An electrical contact member is insertable within the stem portion such that it can contact the electrode. The coupling device of FIG. 2C can also include a contact retainer member to hold the electrical contact member in place similar to the coupling device as shown in FIGS. 2A and 2B.
  • As shown in FIG. 2C, the probe member 116 of the electrical contact coupling device 114 includes a handle 118 which can facilitate securing the probe member 116 within the socket member 120. The handle 118, as shown, has a solid shape which can facilitate the use and manufacture of the coupling device 114. In addition, the stem portion (not shown) of the probe member 116 is larger in diameter than the stem portion of the probe member as illustrated in FIG. 2A. By increasing the stem size, the probe member can be more easily and readily inserted within the socket member. Further, the probe member is greater in length as compared to the probe member as shown in FIGS. 2A and 2B such that the end regions 122 of the probe member 116 extend beyond a groove region 124 of the socket member 120. This can facilitate securing the probe member within the groove region 124 of the socket member 120.
  • In an embodiment, an opening 126 of the socket member 120 can include an additional opening portion 128 to accommodate the insertion of the stem portion of the probe member 116, having an increased size, therethrough. This can ensure proper alignment of the probe member with respect to the socket member before insertion of the probe member into the socket member thus facilitating the insertion process.
  • It should be appreciated that the probe member, socket member and contact retainer member can be composed of a variety of different and suitable materials including, for example, plastics, molded plastics, like materials or combinations thereof. The various components of the coupling device, such as the probe member, socket member and contact retainer member, can be fitted in any suitable way. For example, the components can be fitted in smooth engagement (as shown in FIGS. 2A and 2B), in threaded engagement (as shown in FIGS. 2D and 2E) and/or any suitable fitting engagement or arrangement to one another.
  • As shown in FIGS. 2D and 2E, the coupling device 130 of the present invention can be made of threaded parts which are removably connected to one another to form the coupling device. The threaded parts can facilitate securing the electrode to the blood circuit as well as general use of same as described below.
  • In an embodiment, the stem portion 132 of the body 134 of the coupling device 130 has a threaded region 136 which can be insertably attached to a dialysis machine or other suitable mounting device in threaded engagement. This can facilitate the ease in which the coupling device is attached and detached from the mounting device.
  • As shown in FIG. 2E, the stem portion 132 is threaded on both sides allowing it to be in threaded engagement with an annular member 138. The annular member 138 provides direction and support allowing the electrical contact member 140 to abut against the electrode 142 housed in the probe member 144 as previously discussed.
  • In an embodiment, a plate member 146 made of any suitable conductive material can be depressed against a spring 148 as the probe member 144 is secured to the body 134. At the same time, another spring 150 can be displaced against the electrical contact member 140 in contact with the retainer 152 which is inserted within an annular region of the annular member 138 to secure the electrical contact member 140 to the body 134.
  • The spring mechanism in an embodiment of the present invention allows the parts of the coupling device 130 to remain in secure engagement during use. It can also facilitate use during detachment of the parts for cleaning, maintenance or other suitable purpose.
  • As previously discussed, the present invention can be effectively utilized to detect dislodgment of an access device, such as a needle, inserted within a patient through which fluid can pass between the patient and a fluid delivery and/or treatment system. The present invention can be applied in a number of different applications, such as medical therapies or treatments, particularly dialysis therapies. In dialysis therapies, access devices, such as needles, are inserted into a patient's arteries and veins to connect blood flow to and from the dialysis machine.
  • Under these circumstances, if the needle becomes dislodged or separated from the blood circuit, particularly the venous needle, the amount of blood loss from the patient can be significant and immediate. In this regard, the present invention can be utilized to controllably and effectively minimize blood loss from a patient due to dislodgment of the access device, such as during dialysis therapy including hemodialysis, hemofiltration, hemodiafiltration and continuous renal replacement.
  • Signal Detection and Processing
  • As previously discussed, the electrical contacts in connection with the controller can be used to detect a change in impedance or the like in response to needle drop-out or other like changes in access conditions. The electrical contacts can include a variety of suitable conductive materials, such as conductive polymer materials as described below. In an embodiment, the present invention can be adapted to correct for any variations in the baseline impedance over time. This can increase the level of sensitivity with respect to the detection capabilities of the present invention. In this regard, if changes in the baseline impedance are too great and not adequately corrected for, changes in impedance due to needle dislodgment may not be as readily, if at all, detectable above baseline values.
  • From a practical standpoint, there are a number of different process conditions that may influence a change in the baseline impedance over time. For example, a gradual drift or change in the baseline can occur due to a change in the characteristics, such as the hematocrit, plasma protein, blood/water conductivity and/or the like, of the blood or other suitable fluid during treatment. This can arise due to changes in the level of electrolytes or other components during dialysis therapy.
  • As illustrated in FIG. 3, the present invention can process a measurable voltage signal to correct for changes in baseline impedance over time. This can enhance the detection capabilities of the present invention as previously discussed. In an embodiment, a current source 160 or the like generates an electric current to pass through the blood as it circulates into, through and out of the patient along the extracorporeal blood circuit 162 which connects the patient via venous and arterial needles to the dialysis system including a variety of process components. The electric current is injected into the blood circuit via a first electrical contact 163a thereby defining a conductor loop or pathway along the blood circuits. Preferably, the current is maintained at a constant level until dislodgment occurs. The second electrode 163b is used to sense voltage or the like along the conductor loop and then pass a signal indicative of same and/or changes thereof to an electronic device for detection and processing as previously discussed. The voltage signal can be measured and processed in any suitable manner.
  • In an embodiment, the signal is passed through a series of components including a filter or filters 164 which can act to filter noise from the signal, particularly noise derived from the rotation from the pump in order to minimize a false negative and/or positive detection of needle dislodgment, a rectifier 166, a peak detector 168 and an analog to digital converter (“ADC”) 170 to digitize the signal. In this regard, the digital signal can then be stored in a computer device (not shown) for further processing. The voltage signal is continually measured and processed over time. With each measurement, the digitized signals are compared to evaluate changes due to baseline changes associated with variations in process conditions over time, such as a change in the characteristics of blood as previously discussed. If a baseline change is determined, the digitized signal can be further processed to correct for the change in baseline.
  • The voltage data is continually sent to a control unit 172 coupled to the ADC. The control unit continually performs a calculation to determine whether a change in impedance or the like in response to needle dislodgment has occurred. In an embodiment, dislodgment of an access device is detected when [V(t)−V(t-T)]>C1, where t is time, where T is the period of blood pump revolution, where C1 is a constant and where V(t)=Io* Z, where Io is current and where Z is the impedance of the bloodline which is a function of the impedance associated with patient's vascular access and the impedance associated with various components of the dialysis system, such as the dialyzer, as previously discussed.
  • If disconnection of the patient from the blood circuit is detected, the control unit 172 can be utilized to process the signal in order to minimize blood loss from the patient. In an embodiment, the controller is in communication with a dialysis system as applied to administer dialysis therapy including, for example, hemodialysis, hemofiltration, hemodiafiltration and continuous renal replacement. This communication can be either hard-wired (i.e., electrical communication cable), a wireless communication (i.e., wireless RF interface), a pneumatic interface or the like. In this regard, the controller can process the signal to communicate with the dialysis system or device to shut off or stop the blood pump 174 associated with the hemodialysis machine and thus effectively minimize the amount of blood loss from the patient due to needle dislodgment during hemodialysis.
  • The controller can communicate with the dialysis system in a variety of other ways. For example, the controller and hemodialysis machine can communicate to activate a venous line clamp 176 for preventing further blood flow via the venous needle thus minimizing blood loss to the patient. In an embodiment, the venous line clamp is activated by the controller and attached to or positioned relative to the venous needle such that it can clamp off the venous line in close proximity to the needle. Once clamped, the dialysis system is capable of sensing an increase in pressure and can be programmed to shut-off the blood pump upon sensing pressure within the blood flow line which is above a predetermined level. Alternatively, the venous line clamp can be controllably attached to the dialysis system.
  • In an embodiment, an alarm can be activated upon detection of blood loss due to, for example, needle dislodgment during dialysis therapy. Once activated, the alarm (i.e., audio and/or visual or the like) is capable of alerting the patient, a medical care provider (i.e., doctor, registered nurse or the like) and/or a non-medical care provider (i.e., family member, friend or the like) of the blood loss due to, for example, needle dislodgment. The alarm function is particularly desirable during dialysis therapy in a non-medical facility, such as in a home setting or self care setting where dialysis therapy is typically administered by the patient and/or a non-medical care provider in a non-medical setting or environment excluding a hospital or other like medical facility.
  • In this regard, the alarm activation allows, for example, the patient to responsively act to ensure that the dialysis therapy is terminated by, for example, to check that the blood pump has been automatically shut off to minimize blood loss to the patient. Thus, the patient has the ability to act without the assistance of a third party (i.e., to act on his or her own) to ensure that responsive measures are taken to minimize blood loss. The alarm can thus function to ensure the patient's safety during the administration of dialysis therapy, particularly as applied to home hemo treatments where at least a portion of the dialysis therapy can be administered while the patient is sleeping.
  • Dialysis Machine
  • As previously discussed, the present invention can be adapted for use with any suitable fluid delivery system, treatment system or the like. In an embodiment, the present invention is adapted for use with a dialysis machine to detect access disconnection as blood flows between the patient and the dialysis machine along a blood circuit during treatment, including, for example hemodialysis, hemofiltration and hemodiafiltration.
  • The present invention can include any suitable dialysis machine for such purposes. An example, of a hemodialysis machine of the present invention is disclosed in U.S. Pat. No. 6,143,181 herein incorporated by reference. In an embodiment, the dialysis machine 190 includes a mobile chassis 192 and it has at the front side 194 thereof a common mechanism 196 for connecting tubing or the like by which a patient can be connected to the dialysis machine as shown in FIG. 4B. A flat touch screen 197 which can show several operational parameters and is provided with symbols and fields for adjustment of the dialysis machine by relevant symbols and fields, respectively, on the screen being touched can be adjusted vertically and can be universally pivoted on the dialysis machine and can be fixed in the desired adjusted position.
  • In an embodiment, the dialysis machine includes a chassis having one or more connectors for connecting a patient to the dialysis machine via a blood circuit allowing blood to flow between the patient and the dialysis machine during dialysis therapy wherein one or more electrical contacts are connected to the blood circuit in fluid communication with the blood allowing detection of a change in an electrical value in response to access disconnection as the blood flows through the blood circuit having an electrical signal passing therein.
  • In an embodiment, the dialysis machine of the present invention can be designed to accommodate one or more of the electrical contact coupling devices, such as a pair of coupling device, used to detect access disconnection as shown in FIG. 4B. For example, one or more coupling devices 198 can be attached to the front panel 194 of the dialysis machine 190. This can be done in any suitable way. In an embodiment, the a stem portion of the coupling device is insertably mounted via a threaded fit, frictional fit or the like, as previously discussed. This connects the patient to the dialysis machine 190 via a blood tubing set 202. The blood tubing set includes a first blood line 204 and a second blood line 206. In an embodiment, the first blood line 204 is connected to the patient via an arterial needle 208 or the like through which blood can flow from the patient 200 to the dialysis machine 190. The second blood line 206 is then connected to the patient 200 via a venous needle 210 or the like through which fluid flows from the dialysis machine to the patient thereby defining a blood circuit. Alternatively, the first blood line and the second blood line can be coupled to the venous needle and the arterial needle, respectively. The blood lines are made from any suitable medical grade material. In this regard, access disconnection, such as dislodgment of an arterial needle and/or a venous needle can be detected as previously discussed. Alternatively, the coupling device can be attached to the blood tubing set which is then attached to the dialysis machine in any suitable way.
  • Dialysis Treatment Centers
  • As previously discussed, the present invention can be used during dialysis therapy conducted at home and in dialysis treatment centers. The dialysis treatment centers can provide dialysis therapy to a number of patients. In this regard, the treatment centers include a number of dialysis machines to accommodate patient demands. The therapy sessions at dialysis treatment centers can be performed 24 hours a day, seven days a week depending on the locale and the patient demand for use.
  • In an embodiment, the dialysis treatment centers are provided with the capability to detect access disconnection during dialysis therapy pursuant to an embodiment of the present invention. For example, one or more of the dialysis machines can be adapted for use with an electrical contact coupling device along with the necessary other components to detect access disconnection as previously discussed.
  • In an embodiment, the electrical contact coupling device can be directly attached to one or more of the dialysis machines of the dialysis treatment center. It should be appreciated that the apparatuses, devices, methods and/or systems pursuant to an embodiment of the present invention can be applied for use during dialysis therapy administered to one or more patients in the dialysis treatment center in any suitable way. In an embodiment, the treatment center can have one or more patient stations at which dialysis therapy can be performed on one or more patients each coupled to a respective dialysis machine. Any suitable in-center therapy can be performed including, for example, hemodialysis, hemofiltration and hemodiafiltration and combinations thereof. As used herein, the term “patient station” or other like terms mean any suitably defined area of the dialysis treatment center dedicated for use during dialysis therapy. The patient station can include any number and type of suitable equipment necessary to administer dialysis therapy.
  • In an embodiment, the dialysis treatment center includes a number of patient stations each at which dialysis therapy can be administered to one or more patients; and one or more dialysis machines located at a respective patient station. One or more of the dialysis machines can include a chassis having one or more connectors for connecting a patient to the dialysis machine via a blood circuit allowing blood to flow between the patient and the dialysis machine during dialysis therapy wherein a pair of electrical contacts are connected to the blood circuit in fluid communication with the blood allowing detection of a change in an electrical value in response to access disconnection as the blood flows through the blood circuit having an electrical signal passing therein.
  • As previously discussed, the access disconnection detection capabilities of the present invention can be utilized to monitor and control a safe and effective dialysis therapy. Upon dislodgment of an access device, such as a needle, from the patient, the direct conductive measurement capabilities of the present invention can be used to provide a signal indicative of dislodgment that can be further processed for control and/or monitoring purposes. In an embodiment, the signal can be farther processed to automatically terminate dialysis therapy to minimize blood loss due to dislodgment as previously discussed. Further, the signal can be processed to activate an alarm which can alert the patient and/or medical personnel to the dislodgment condition to ensure that responsive measures are taken. It should be appreciated that the present invention can be modified in a variety of suitable ways to facilitate the safe and effective administration of medical therapy, including dialysis therapy.
  • Applicants have found that the direct conductive measurement capabilities of the apparatus of the present invention can immediately detect blood loss or the like due to access disconnection, such as needle dislodgment, with high sensitivity and selectivity such that responsive measures can be taken to minimize blood loss due to same. The ability to act responsively and quickly to minimize blood loss upon detection thereof is particularly important with respect to needle dislodgment during hemodialysis. If not detected and responded to immediately, the amount of blood loss can be significant. In an embodiment, the present invention is capable of taking active or responsive measures, to minimize blood loss (i.e., shut-off blood pump, activate venous line clamp, activate alarm and/or the like) within about three seconds or less, preferably within about two to about three second upon immediate detection of needle dislodgment.
  • In addition, the controller can be utilized to monitor and/or control one or more treatment parameters during hemodialysis. These parameters can include, for example, the detection of blood due to blood loss upon needle dislodgment, the change in blood flow, the detection of air bubbles in the arterial line, detection of movement of the sensor during treatment, detection and/or monitoring of electrical continuity of the sensor or other like treatment parameters. In an embodiment, the controller includes a display (not shown) for monitoring one or more of the parameters. Thus, the present invention can be utilized to promote the safe and effective administration on patient therapy, such as dialysis therapy, as previously discussed.
  • As used herein “medical care provider” or other like terms including, for example, “medical care personnel”, means an individual or individuals who are medically licensed, trained, experienced and/or otherwise qualified to practice and/or administer medical procedures including, for example, dialysis therapy, to a patient. Examples of a medical care provider include a doctor, a physician, a registered nurse or other like medical care personnel.
  • As used herein “non-medical care provider” or other like terms including, for example, “non-medical care personnel” means an individual or individuals who are not generally recognized as typical medical care providers, such as doctors, physicians, registered nurses or the like. Examples of non-medical care providers include patients, family members, friends or other like individuals.
  • As used herein “medical facility” or other like terms including, for example, “medical setting” means a facility or center where medical procedures or therapies, including dialysis therapies, are typically performed under the care of medical care personnel. Examples of medical facilities include hospitals, medical treatment facilities, such as dialysis treatment facilities, dialysis treatment centers, hemodialysis centers or the like.
  • As used herein “non-medical facility” or other like terms including, for example, “non-medical setting” means a facility, center, setting and/or environment that is not recognized as a typical medical facility, such as a hospital or the like. Examples of non-medical settings include a home, a residence or the like.
  • It should be appreciated that the electrode output signal can be combined with other less sensitive blood loss detection methods, such as venous pressure measurements, systemic blood pressure, the like or combinations thereof, to improve specificity to needle dislodgment.
  • Conductive Polymer
  • As previously discussed, the present invention provides conductive polymer materials and devices, apparatuses, systems and methods that employ same. The conductive polymer material can be utilized in a number of different applications, such as to monitor patient therapy. For example, the conductive polymer materials can be utilized to monitor patient access conditions as discussed above and as further detailed below. Other types of monitoring applications include, for example, monitoring solution mixing or compounding as described in greater detail below. The present invention contemplates monitoring one or a combination of condition changes associated with patient therapy, such as monitoring patient access conditions and solution mixing conditions, alone or in combination.
  • In an embodiment, the conductive polymer material includes a polymer matrix and a conductive component that is incorporated in the polymer matrix. Alternatively, the conductive polymer material, in an embodiment, includes a conductive polymer component without a separate conductive component, such as stainless steel. It should be appreciated that the conductive polymer material can be made from any suitable types and amounts of materials and in any suitable way.
  • As discussed above, the conductive polymer can include a polymer matrix and a conductive component incorporated in the matrix. The polymer matrix can include a variety of different polymer-based materials that are suitable for use in a variety of applications, particularly including medical applications, such as dialysis therapy. In an embodiment, the polymer matrix includes polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene, like polymeric materials and suitable combinations thereof.
  • The conductive component can include any suitable material or combination of materials that have conductive properties applicable for a number of different applications including, for example, detecting patient access disconnection during medical therapy as previously discussed, monitoring the mixing or compounding of solution components to form a mixed solution, and/or other like applications. Preferably, the conductive component includes stainless steel, fillers, carbon black, fibers thereof and/or the like.
  • The conductive component can be sized and shaped in any suitable way such that it can be readily incorporated in the polymer matrix. For example, the conductive component can include conductive fibers made from any suitable material, such as stainless steel, a carbonaceous material and/or the like. The fibers, in an embodiment, have an aspect ratio that ranges from about 2:1 to about 30:1.
  • The conductive polymer material can include any suitable amount of the conductive polymer matrix and the conductive component. This can vary depending on the application of the conductive polymer material. In an embodiment, the conductive component includes greater than about 10% by weight of the conductive polymer material. Preferably, the conductive component ranges from about 10% to about 50% by weight of the conductive polymer material. It should be appreciated that more than about 50% by weight of the conductive component can be utilized but may provide minimal, if any, increase in performance of the conductive polymer material depending on the application. Preferably, the conductive component is uniformly dispersed throughout the polymer matrix.
  • As previously discussed, the conductive polymer material, in an embodiment, is composed of a conductive polymer component. This type of component has sufficient electrical conductivity properties such that an additional conductive component, such as stainless steel, is not required. Examples of conductive polymer material components include polyaniline, polypyrrole, polythiophenes, polyethylenedioxythiophene, poly(p-phenylene vinylene), the like and mixtures thereof.
  • As previously discussed, the conductive polymer material can be made in any suitable way. In general, the conductive component is mixed with the polymer component under suitable processing conditions including temperature and pressure, for example, to form a polymer matrix with the conductive component incorporated therein. The mixing should take place over a suitable period of time and with a sufficient amount of force such that the conductive component is uniformly distributed throughout the polymer matrix.
  • The polymer matrix incorporated with a conductive component is then shaped and formed into a final product in any suitable way. For example, the polymer matrix incorporated with the conductive component can be formed into a single piece part via an injection molding process, extrusion process or the like under suitable processing conditions. Thus, the conductive polymer material can be readily made with manufacturing techniques, such as injection molding and extrusion. This can effectively provide a cost savings to the manufacturing process that can be inevitably passed along to the consumer.
  • The conductive polymer material can be formed into any suitable shape and size depending on the application. In an embodiment, the conductive polymer material is formed into an electrode or other like electrical contact that can be utilized for a number of different applications, including, for example, monitoring patient access conditions and/or monitoring solution mixing or compounding as discussed above and described below in greater detail. The conductive polymer electrode can have a variety of different and suitable configurations depending on the application. For example, the conductive polymer electrode can be made into a coupler that can be used to join tubing to form a tubing joint as described below.
  • As shown in FIGS. 5A and 5B, the conductive polymer coupler has a generally cylindrical shape. With this configuration, the conductive polymer can be readily attached to a tube through which fluid flows, thus forming a tubing joint.
  • As shown in FIG. 5A, the coupler 220 has a member 222 that extends from an inner surface 224 of the coupler electrode 220. The member 222 acts as a stop for the tube 226 that is attached to the electrode such that a desired length of the tubing joint 228 can be preset. The coupler 220 as shown in FIG. 5A, in an embodiment, is made via an injection molding process.
  • As shown in FIG. 5A, a first tube member 230 is attached to a first end 232 of the coupler 220 and positioned or stopped by a first end 234 of the member 222. A second tube member 236 is attached to a second end 238 of the coupler 220 and stopped or positioned by a second end 240 of the member 222. This forms a tubing joint 228, such as a tubing joint that is integrated within a blood circuit and utilized during dialysis therapy as described in the present application.
  • As shown in FIG. 5B, the coupler 242 is formed without a member that allows the length of the tubing joint to be preset as discussed above. In this regard, the tubing joint length can be adjusted accordingly depending on the application. Further, the coupler 242 as shown in FIG. 5B can be made via an extrusion process instead of an injection molding process. This can provide a further cost savings with respect to manufacturing of the coupler as compared to an injection molding process as discussed above. As shown in FIG. 5B, a first tube member 244 is attached to a first end 246 of the coupler 242 and a second tube member 248 is attached to the second end 250 of the coupler 242, thus forming the tubing joint 252.
  • The tube member can be attached to the conductive polymer coupler in any suitable way. For example, the conductive polymer material can be solvent bonded, heat sealed, laser welded, radio frequency sealed, or the like to the tubing.
  • The tubing can be made of any suitable material depending on the application. For example, the tubing can be made from polyvinyl chloride (“PVC”). Preferably, the PVC tubing is attached to a conductive polymer material that is made with a polymer matrix composed of acrylonitrile butadiene styrene (“ABS”) where the ABS-based conductive material is solvent bonded to the PVC tubing.
  • However, the tubing can be made of a variety of different materials depending on the application. In an embodiment, the tubing includes a non-PVC material, such as metallocene-based polyethylene polymers, cyclo olefin copolymers, cyclo olefin copolymer blends and the like. The non-PVC materials can include any suitable type and amount of constituents. Metallocene-based polyethylene polymers and the like illustrative of the present invention can be found, for example, in U.S. Pat. No. 6,372,848, the disclosure of which is herein incorporated by reference. These types of non-PVC polymers can include a polymer blend that has a first ethylene and a-olefin copolymer obtained using a single site catalyst present in an amount by weight of from about 0% to about 99% by weight of the blend and having a melt flow index from fractional, such as about 0.1 g/10 min to about 5 g/10 min, a second ethylene and α-olefin copolymer obtained using a single site catalyst and being present in an amount by weight of the blend from about 0% to about 99% and having a melt flow index from higher than about 5 g/10 min to about 20 g/10 min; and a third ethylene and α-olefin copolymer obtained using a single-site catalyst and being present in an amount by weight of the blend from about 0% to about 99% and having a melt flow index greater than about 20 g/10 min. In an embodiment, the α-olefin copolymer has a molecular weight distribution of less than about 3.
  • Cyclo olefin copolymers and blends thereof illustrative of the present invention can be found, for example, in U.S. Pat. No. 6,255,396, the disclosure of which is herein incorporated by reference. These types of non-PVC polymers can include as a component homopolymers or copolymers of cyclic olefins or bridged polycyclic hydrocarbons. For example, the polymer composition includes a first component obtained by copolymerizing a norbornene monomer and an ethylene monomer wherein the first component is in an amount from about 1-99% weight of the composition; and a second component of an ethylene and α-olefin copolymer that has six carbons wherein the second component is in an amount from about 99% to about 1% by weight of the composition. In an embodiment, the polymer composition can include an additional component, such as a second homopolymer or copolymer of a cyclic olefin or a bridged polycyclic hydrocarbon.
  • The non-PVC based tubing and the non-PVC based conductive coupler can be joined in any suitable way to form a tubing joint. In an embodiment, the non-PVC based tubing and coupler are joined via solvent bonding, such as disclosed in U.S. Pat. Nos. 6,255,396 and 6,372,848. As used herein the term solvent bonding or other like terms means that the tubing can be exposed to a solvent to melt, dissolve or swell the tubing and then be attached to another polymeric component to form a permanent bond. Suitable solvents typically include those having a solubility parameter of less than about 20 (Mpa)1/2. Suitable solvents can also have a molecular weight less than about 200 g/mole. The solvent can include, for example, aliphatic hydrocarbons, aromatic hydrocarbons, and mixtures thereof. As used herein, the terms aliphatic hydrocarbon and aromatic hydrocarbon are compounds containing only carbon and hydrogen atoms.
  • Suitable aliphatic hydrocarbons can include substituted and unsubstituted hexane, heptane, cyclohexane, cycloheptane, decalin and the like. Suitable aromatic hydrocarbons can include substituted and unsubstituted aromatic hydrocarbon solvents, such as xylene, tetralin, toluene, cumene and the like. Suitable hydrocarbon substituents can include aliphatic substituents that have from 1-12 carbons and include propyl, ethyl, butyl, hexyl, tertiary butyl, isobutyl, the like and combinations thereof.
  • As previously discussed, the conductive polymer of the present invention can be constructed and arranged into a variety of different configurations, such as a conductive polymer coupler as shown in FIGS. 5A and 5B and discussed above. Another example includes a dialyzer header that is made from the conductive polymer according to an embodiment. Referring to FIG. 6, a dialyzer 253 is generally illustrated. The dialyzer 253 includes a body member 254 that generally includes a casing 256. The casing 256 includes a core section as well as two bell members 260 located at each end of the dialyzer. Located within the core is a fiber bundle 258. The dialyzer also includes a dialysate inlet 262 and a dialysate outlet 264.
  • Located at a first end 266 of the dialyzer 253 is a fluid inlet 268 and at a second end 270 is a fluid outlet 272 defined by a fluid inlet header 274 and a fluid outlet header 276, respectively. The dialyzer 253 is connected to a dialysis blood circuit in any suitable manner. In an embodiment, the inlet 274 and outlet 276 headers are made from the conductive polymer material of the present invention as discussed above. The inlet 274 and outlet 276 headers can be connected to a controller 278 such that the conductive polymer headers can be utilized to monitor patient access conditions as previously discussed.
  • A variety of different header and dialyzer designs can be utilized. For example, U.S. Pat. No. 6,623,638 and U.S. Patent Publication No. 2003/0075498 provide a number of different examples illustrative of the present invention. The disclosures of U.S. Pat. No. 6,623,638 and U.S. Patent Publication No. 2003/0075498 are herein incorporated by reference.
  • The conductive polymer of the present invention can be utilized in any suitable way and in a variety of different devices, apparatuses, systems and applications thereof. For example, the conductive polymer can be utilized to detect a change in impedance in response to dislodgement of an access device, to detect a change in conductivity in response to a change in solution composition and/or other suitable applications.
  • In an embodiment, the conductive polymer is part of a sensor assembly or apparatus that can be utilized, for example, for monitoring dialysis applications as discussed in the present application. The sensor apparatus of the present invention can include a number of different configurations and designs. Two examples of such designs illustrative of the present invention are described below in FIGS. 7A and 7B.
  • In FIG. 7A, the tubing joint 284 that includes the conductive polymer electrode 286 attached to a tube member 288 as described above, for example, is positioned in place by a holding device 290 or holder for purposes of detection capabilities associated with the sensor apparatus 291 in an embodiment. In general, the holder 290 as shown in FIG. 7A has a hub design. More specifically, the holder 290 includes a base member 292 onto which the tubing joint 284 can be placed. The base member 292 includes a first portion 294 that is made from a plastic or other suitable material. The first portion 294 defines an outer surface 296 of the base member 292. Along the outer surface 296, the first portion 294 includes two openings that are spaced apart as shown in FIG. 7A. The first opening 298 is located on a first edge 300 of the first portion of the base and the second opening 302 is located on a second edge 304 of the first portion of the base. The openings can be configured in any suitable way and be utilized for mounting purposes.
  • The second portion of the base member includes a conductive portion 306 as shown in FIG. 7A. In an embodiment, the conductive portion 306 includes a single piece part 308 that is made from any suitable conductive material, such as stainless steel and/or the like. As shown in FIG. 7A, the conductive polymer of the tubing joint is placed against a curved edge 310 of the second portion that substantially forms to an outer surface 312 of the conductive polymer electrode 286. The electrode is substantially cylindrical in shape.
  • The holder 290 further includes an arm member 314 that is pivotally attached to the base member 292 as shown in FIG. 7A. The arm member 314 includes a generally curved region such that the arm 314 can be positioned over the tubing joint 284 allowing it to substantially conform to the generally cylindrical surface of the tube joint and thus further securing the tubing joint 284 in place.
  • Another configuration of a hub design illustrative of the sensor apparatus of the present invention is shown in FIG. 7B. In general, this design provides a box-like holder 316 that encloses the tubing joint 318 wherein the tubing joint includes the conductive polymer electrode 320 in the form of a coupler that is attached to the tube member 322 as discussed above. The holder 316 includes a base member 324. The base member 324 includes side portions 326, a bottom portion 328 and an opening 330 at a top portion 332. As shown in FIG. 7B, the sensor apparatus 334 includes a conductive member 336 that is contained in the base member 324. The conductive member 336 can be made of any suitable material as described above. The conductive member 336 includes an annular-shaped surface 338 against which the tubing joint 318 can be placed. The sensor apparatus 334 further includes a lid 340 that is pivotally attached to the base member 324. The lid 340 has a member 342 that abuts against a portion of the tubing joint in a closed position. This secures the tubing joint in place for use.
  • As previously discussed, the sensor apparatus of the present application can be used in a number of suitable applications. For example, the sensor apparatus can be suitably coupled to a blood circuit and used for purposes of detecting disconnection of an access device as described in the present application. Another application includes the monitoring of solution compounding as described in greater detail below. In this regard, the sensor apparatus as shown in FIGS. 7A and 7B can be used in combination with or in place of the electrical coupling devices as illustrated in FIGS. 2A-2E and further described above. Thus, the present invention can be utilized to monitor one or a combination of conditions, such as patient access and solution mixing, during use. As applied, the sensor apparatus can be connected to a controller or other like device for detection purposes. The controller can include one or a number of different devices that are in electrical contact with the sensor apparatus in any suitable way.
  • In another embodiment, the sensor apparatus can include a single piece part that is made from the conductive polymer material. The single piece part can be made in any suitable way such as through injection molding as described above. A number of different and suitable shapes and sizes can be formed. One such example illustrative of the present invention of a single piece part conductive electrode 344 is shown in FIGS. 8A and 8B.
  • In general, the conductive polymer electrode 344 is configured as a coupler that can join tubing to form a tubing joint through which fluid can flow as shown in FIGS. 8A and 8B. The conductive polymer electrode 344 includes a base member 346 that has an annular opening 348 extending therethrough. A tube member 350 can be attached to the ends 351 of the annular opening 348 such that the tubing joint can be formed as described above. The base member 346 includes a stem portion 352 that extends from a portion of a surface 354 of the base member 346. This can be used to mount or attach the conductive polymer electrode 344 to a control panel or other suitable component, such as a hemodialysis machine as described above. The stem portion 352 defines an annular-shaped channel 356 that ends from the surface 354 of the base member 346. Within the annular-shaped channels, an inner annular-shaped channel 360 is also provided that extends from the surface 354 of the base 346, as shown in FIG. 8B. The stem portion can be utilized to provide a pathway through which the electrode can be in electrical contact with one or more other devices, such as a controller, in any suitable way. The base member further includes a top member 362 that extends from a portion of the surface 354 of the base member 346. The top member 362 can be used to secure the stem portion 352 of the base member 346 in place for use and/or to remove the electrode after use.
  • As shown in FIGS. 8A and 8B, the conductive polymer electrode 344 includes a member 366 that extends from an inner surface of the annular opening 348. The member 366 acts as a stop against which the tubing can be placed to form the tubing joint. The member 366 has a generally-cylindrical shape with an opening 368 through which fluid can flow.
  • As previously discussed, the conductive polymer material of the present invention can be utilized in a number of different applications. In an embodiment, the conductive polymer material can be utilized to monitor patient access conditions, such as to detect disconnection of an access device that is inserted in a patient through which fluid flows during medical therapy. Preferably, the disconnection detection application is applied during dialysis therapy, such as during hemodialysis therapy.
  • As applied to dialysis applications, the conductive polymer can be formed into an electrode and attached to a dialysis blood circuit in any suitable manner. As shown in FIGS. 1A and 2A and further described above, at least one of the sensors can include an electrode made with the conductive polymer material of the present invention. The sensors 22 and 24 are in electrical contact with a controller 29 and thus the conductive polymer electrode can be utilized for detection, monitoring and control purposes related to dialysis therapy as described above. As shown in FIGS. 4A and 4B and described in the present application, the sensors 198 can be attached directly to the hemodialysis machine wherein at least one of the sensors includes a conductive polymer electrode according to an embodiment of the present invention. The conductive polymer sensor can be configured in any suitable way, such as the coupler and hub design (See, FIGS. 5A, 5B, 7A and 7B), the single-piece part design (See, FIGS. 8A and 8B) and dialyzer header design (See, FIGS. 8A and 8B) as described above. It should be appreciated that the present invention contemplates the use of one or a combination of different sensors to monitor medical therapy, such as patient access and solution mixing conditions.
  • In an embodiment, the conductive polymer material of the present invention can be utilized for monitoring the mixing of solutions to form a mixed solution, such as a mixed solution used during medical therapy. One type of application illustrative of the present invention for such monitoring purposes is during dialysis therapy, particularly during peritoneal dialysis. In general, the conductive polymer material can be formed into an electrode or other sensing device that can effectively detect changes in conductivity associated with a dialysis solution that is administered to the patient during peritoneal dialysis.
  • The dialysis solution can be formed from a number of solution components that are mixed to form a mixed dialysis solution prior to administration. The dialysis solution components can have varying pH levels, such as ranging from about 1.8 to about 9.2. Once mixed, the pH of the mixed dialysis solution should be at a physiologically acceptable level, such as ranging from about 6.8 to about 7.5, prior to use. The pH level can be monitored in relation to changes in the conductivity level of the dialysis solution. In this regard, the conductive polymer of the present invention can be utilized to detect changes in conductivity level and thus can be utilized to determine whether the solution components are properly mixed to form the mixed dialysis solution at an acceptable pH level prior to use. A general description of peritoneal dialysis is provided below and is illustrative of the present invention.
  • Peritoneal dialysis utilizes a sterile dialysis solution, which is infused into a patient's peritoneal cavity and into contact with the patient's peritoneal membrane. Waste, toxins and excess water pass from the patient's bloodstream through the peritoneal membrane and into the dialysis solution. The transfer of waste, toxins, and excess water from the bloodstream into the dialysis solution occurs due to diffusion and osmosis during a dwell period as an osmotic agent in the dialysis solution creates an osmotic gradient across the membrane. The spent solution is later drained from the patient's peritoneal cavity to remove the waste, toxins and excess water from the patient.
  • There are various types of peritoneal dialysis therapies, including continuous ambulatory peritoneal dialysis (“CAPD”) and automated peritoneal dialysis. CAPD is a manual dialysis treatment, in which the patient connects the catheter to a bag of fresh dialysis solution and manually infuses fresh dialysis solution through the catheter or other suitable access device and into the patient's peritoneal cavity. The patient disconnects the catheter from the fresh dialysis solution bag and allows the solution to dwell within the cavity to transfer waste, toxins and excess water from the patient's bloodstream to the dialysis solution. After a dwell period, the patient drains the spent dialysis solution and then repeats the manual dialysis procedure. Tubing sets with “Y” connectors for the solution and drain bags are available that can reduce the number of connections the patient must make. The tubing sets can include pre-attached bags including, for example, an empty bag and a bag filled with dialysis solution.
  • In CAPD, the patient performs several drain, fill, and dwell cycles during the day, for example, about four times per day. Each treatment cycle, which includes a drain, fill and dwell, takes about four hours.
  • Automated peritoneal dialysis is similar to continuous ambulatory peritoneal dialysis in that the dialysis treatment includes a drain, fill, and dwell cycle. However, a dialysis machine automatically performs three or more cycles of peritoneal dialysis treatment, typically overnight while the patient sleeps.
  • With automated peritoneal dialysis, an automated dialysis machine fluidly connects to an implanted catheter. The automated dialysis machine also fluidly connects to a source or bag of fresh dialysis solution and to a fluid drain. The dialysis machine pumps spent dialysis solution from the peritoneal cavity, through the catheter, to the drain. The dialysis machine then pumps fresh dialysis solution from the source, through the catheter, and into the patient's peritoneal cavity. The automated machine allows the dialysis solution to dwell within the cavity so that the transfer of waste, toxins and excess water from the patient's bloodstream to the dialysis solution can take place. A computer controls the automated dialysis machine so that the dialysis treatment occurs automatically when the patient is connected to the dialysis machine, for example, when the patient sleeps. That is, the dialysis system automatically and sequentially pumps fluid into the peritoneal cavity, allows for dwell, pumps fluid out of the peritoneal cavity, and repeats the procedure.
  • Several drain, fill, and dwell cycles will occur during the treatment. Also, a final volume “last fill” is typically used at the end of the automated dialysis treatment, which remains in the peritoneal cavity of the patient when the patient disconnects from the dialysis machine for the day. Automated peritoneal dialysis frees the patient from having to manually perform the drain, dwell, and fill steps during the day.
  • In general, the dialysis solution includes an osmotic agent, such as dextrose or other suitable constituent in any suitable amount, such as from about 1.5% to about 4.25% by weight. The dialysis solution further includes one or more electrolytes, such as sodium, calcium, potassium, magnesium chloride and/or the like in any suitable amount. The dialysis solution may also include other constituents, such as buffers including lactate and bicarbonate, or the like, and other constituents, such as stabilizers. The dialysis solution can be made from multiple solution components that can vary in the amounts and types of constituents thereof and have varying pH levels.
  • A variety of different and suitable types of multi-part dialysis solutions can be utilized. For example, a multi-part bicarbonate-based solution can be found in U.S. patent application Ser. No. 09/955,248, entitled BIOCHEMICALLY BALANCED PERITONEAL DIALYSIS SOLUTIONS, filed on Sep. 17, 2001, the disclosure of which is incorporated herein by reference. An example of a multi-part lactate-based solution can be found in U.S. patent application Ser. No. 10/628,065, entitled DIALYSIS SOLUTIONS WITH REDUCED LEVELS OF GLUCOSE DEGRADATION PRODUCTS, filed on Jul. 25, 2003 the disclosure of which is herein incorporated by reference.
  • Another example of a bicarbonate-based solution can be found in U.S. patent application Ser. No. 10/044,234, entitled BICARBONATE-BASED SOLUTIONS FOR DIALYSIS THERAPIES, filed on January 11, 2002 and as further disclosed in U.S. Pat. No. 6,309,673, the disclosures of which are herein incorporated by reference. The bicarbonate-based solution can be made from solution components that have varying pH conditions, such as under moderate and extreme pH conditions. In an embodiment, the solution components can vary in pH from between about 1.0 to about 10.0. Once mixed, the desired pH of the mixed solution is a physiological acceptable level, such as between about 6.5 to about 7.6 (i.e., close to the pH of blood).
  • For example, under moderate pH conditions, the bicarbonate-based solution can be formulated by the mixing of a bicarbonate concentrate with a pH that ranges from about 7.2 to about 7.9, preferably from about 7.4 to about 7.6, and an electrolyte concentrate with a pH that ranges from about 3.0 to about 5.0. Under extreme pH conditions, for example, the bicarbonate concentrate has a pH that can range from about 8.6 to about 9.5 and is mixed with an electrolyte concentrate that has a pH from about 1.7 to about 2.2. A variety of different and suitable acidic and/or basic agents can be utilized to adjust the pH of the bicarbonate and/or electrolyte concentrates. For example, a variety of inorganic acids and bases can be utilized, such as hydrochloric acid, sulfuric acid, nitric acid, hydrogen bromide, hydrogen iodide, sodium hydroxide, the like or combinations thereof.
  • The solution components, such as the electrolyte concentrate and the dextrose concentrate, can then be mixed in the solution bag and then administered as a mixed solution to the patient during peritoneal dialysis. An illustrated example of a multi-chamber container that separately contains solution components of a dialysis solution according to embodiment of the present invention is shown in FIG. 9.
  • It should be appreciated that the components of the dialysis solutions of the present invention can be housed or contained in any suitable manner such that the dialysis solutions can be effectively prepared and administered. In an embodiment, the present invention includes a multi-part dialysis solution in which two or more parts are formulated and stored separately, and then mixed just prior to use. A variety of containers can be used to house the various parts of the dialysis solution, such as separate containers (i.e., flasks or bags) that are connected by a suitable fluid communication mechanism.
  • In an embodiment, a multi-chamber container or bag can be used to house the separate components of the solution including, for example, a dextrose concentrate and a buffer concentrate. In an embodiment, the separate components are mixed within the multi-chamber bag prior to use, such as applied during peritoneal dialysis.
  • FIG. 9 illustrates a suitable container for storing, formulating, mixing and administering a dialysis solution, such as during continuous ambulatory peritoneal dialysis, according to an embodiment of the present invention. The multi-chamber bag 380 has a first chamber 382 and a second chamber 384. The interior of the container is divided by a heat seal 386 into the two chambers. It should be appreciated that the container can be divided into separate chambers by any suitable seal.
  • In an embodiment, the container can be divided into separate chambers, such as two or more chambers, by a peel seal. With the use of a peel seal, a frangible connector or other suitable type of connector would not be required to mix the solution components within the multi-chamber bag. An example of a multi-chamber solution bag that includes a peel seal is disclosed in U.S. Pat. No. 6,319,243, the disclosure of which is herein incorporated by reference. As shown in FIG. 10, a container 388 includes at least three chambers 390, 392 and 394. The chambers 390, 392 and 394 are designed for the separate storage of liquids and/or solutions, that can be mixed within the container to form a mixed solution ready-for-use. It should be appreciated that more or less than three chambers can be utilized.
  • The peelable seals 396 and 398 are provided between the chambers 390, 392 and 394, respectively. Examples of peelable seals can be found in U.S. patent application Ser. No. 08/033,233 filed on Mar. 16, 1993 entitled “PEELABLE SEAL AND CONTAINER HAVING SAME”, the disclosure of which is herein incorporated by reference. The peelable seals allow for the selective opening of the chambers to allow for the selective mixing of the liquids contained therein.
  • The container 388 can also include tubular ports, such as tubular ports 400, 402 and 404 as shown in FIG. 10. The tubular ports are mounted to the container so as to allow fluid communication with the container and specifically with chambers 390, 392 and 394. To this end, the tubular ports 400, 402 and 404 can include a membrane that is pierced, for example, by a cannula or a spike or an administration set for delivery of the contents of the container to the patient. It should be appreciated that more or less than three ports can be utilized.
  • As shown in FIG. 9, the multi-chamber container 380 has a frangible connector 406 to sealingly couple the first chamber 382 to the second chamber 384 instead of a peelable seal. To mix the solution within the multi-chamber bag 380, the frangible connector 406 is broken.
  • The first container or chamber 382 includes two port tubes 408 of suitable sizes and lengths. It should be appreciated that more or less than two port tubes may be used. One of the port tubes, for example, can be utilized to add other constituents to the first chamber 382 during formulation of the solution of the present invention, if necessary. The remaining port tube, for example, can be utilized to adaptedly couple the first chamber 382 to the patient via a patient's administration line (not shown), be used to add additional other constituents or the like. The second container or chamber 384 has a single port tube 410 extending there from. In an embodiment, the port tube 410 is connected to a patient's administration line through which a solution can flow to the patient once the solution is mixed as described below.
  • In an embodiment, the transfer of product within the multi-chamber bag 380 can be initiated from the first chamber 382 to the second chamber 384 such that the components of each chamber can be properly mixed to form the dialysis solution of the present invention. In an embodiment, a dextrose concentrate 412 is contained in the first chamber 382 and a buffer concentrate 414 is contained in the second chamber 384. It should be appreciated that any suitable type or number of solution components can be separated with a multi-chamber bag and then mixed to form a mixed solution prior to administration to the patient. Illustrative examples of peritoneal dialysis solutions include those described in U.S. patent application Ser. Nos. 09/955,298 and 10/628,065 and U.S. Pat. No. 6,309,673 as described above.
  • The first chamber 382 is smaller in volume than the second chamber 384 such that the components of each chamber can be properly mixed once the transfer from the first chamber to the second chamber has occurred. Thus, the multi-chamber bag 380 can house at least two solution component parts that after mixture will result in a ready-to-use dialysis solution. An example of the multi-chamber container is set forth in U.S. Pat. No. 5,431,496, the disclosure of which is incorporated herein by reference. The multi-chamber bag can be made from a gas permeable material, such as polypropylene, polyvinyl chloride or the like.
  • It should be appreciated that the multi-chamber bag can be manufactured from a variety of different and suitable materials and configured in a number of suitable ways such that the dialysis solutions of the present invention can be effectively formulated and administered to the patient during medical therapy in any suitable manner. For example, the first chamber can be larger in volume than the second chamber and further adapted such that the dialysis solution of the present invention can be readily and effectively made and administered to the patient.
  • In an embodiment, the dialysis solution is contained and administered from a multi-chamber solution bag during peritoneal dialysis, such as during CAPD. The solution bag can include multiple chambers that each contain separate components of the dialysis solution prior to mixing as discussed above. This may be necessary to maintain separation of the non-compatible solution components prior to mixing for purposes of stability, sterility, effectiveness or the like associated with the dialysis solution prior to use.
  • In another embodiment, the solution components can be prepared and stored in separate containers and then mixed via an admix device prior to use, such as applied during automated peritoneal dialysis. As shown in FIG. 11, a first solution component, such as a dextrose concentrate 416 and a second solution component, such as a buffer concentrate 420 are stored in the respective separate containers 422 and 424 or bags which are fluidly connected to an admix device 426 suitable for use during automated peritoneal dialysis, an example of which includes ADMIX HOMECHOICE by BAXTER INTERNATIONAL, INC. In addition to the first and second components, a first bag 428 and last bag 430 filled with a suitable solution can also be used during dialysis therapy as generally known.
  • In an embodiment, an effective amount of the first solution component 416 and the second solution component 420 are drawn from each respective container and into a heater bag 432 where the solution components (e.g., dextrose and buffer concentrates) can be mixed and heated prior to infusion into a patient 434 during dialysis therapy. As further shown in FIG. 11, a drain line 436 is coupled to the admix device 426 from which waste fluids can be removed from the patient during therapy.
  • According to an embodiment of the present invention, the conductive polymer material can be used as a sensor to monitor solution compounding, such as during peritoneal dialysis. For example, the conductive polymer sensor 438 can be attached to a tube 440 through which the mixed dialysis solution flows to the patient from the multi-chamber solution bag 380 as shown in FIG. 9. The conductive polymer sensor 438 is in electric contact with a controller 442 or other like device such that a change in conductivity of the mixed dialysis solution that is fed to the patient can be monitored. Based on the conductivity level, one can monitor the pH level of the mixed solution to determine whether the solution components (e.g., dextrose concentrate and buffer concentrate) have been properly and sufficiently mixed to form the dialysis solution prior to use. If the dialysis solution is not properly mixed, the conductivity level will exist above or below a baseline conductivity level that is generally associated with a desired pH level of a dialysis solution that is ready-for-use. As previously discussed, the desired pH of the mixed dialysis solution is maintained at a physiological acceptable level, such as between about 6.5 to about 7.6 prior to use. Based on this information, adjustments can be made to the process such that the solution chemistry of the dialysis solution is modified for proper use. This can facilitate the safe and effective use of the solution during use, such as during dialysis therapy.
  • As shown in FIG. 11, the conductive polymer sensor 444 of the present invention can be applied during automated peritoneal dialysis. More specifically, the conductive polymer sensor 444 of the present invention can be attached to the tube member 446 through which a dialysis solution flows to the patient. The dialysis solution is a product of the mixing of solution components that are stored in separate solution bags as previously discussed. The conductive polymer sensor 444 can be attached to a controller 448 or other like device in electrical contact such that the conductivity level and thus the pH level of the solution that is administered to the patient can be monitored as previously discussed. Optionally, at least one additional conductive polymer sensor 450 in an embodiment can also be utilized as shown in FIG. 11. In this regard, the additional sensor(s) can be utilized to monitor the conductivity level of the solution components prior to mixing. This can be utilized to evaluate whether the solution components are maintained at desired pH levels based on a conductivity measurement as discussed above.
  • It should be understood that various changes and modifications to the presently preferred embodiments described herein will be apparent to those skilled in the art. Such changes and modifications can be made without departing from the spirit and scope of the present invention and without diminishing its intended advantages. It is therefore intended that such changes and modifications be covered by the appended claims.

Claims (20)

1. A coupler comprising a conductive polymer material that is so constructed and arranged to join tubing, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophenes, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.
2. The coupler of claim 1, which has a generally cylindrical shape with a first opening to receive a first tubing member and a second opening to receive a second tubing member.
3. The coupler of claim 1, which is extruded.
4. The coupler of claim 1, which includes a member that extends from at least a portion of an inner surface of the coupler to allow a length of a tubing joint that is formed with the coupler and the tubing to be pre-set.
5. The coupler of claim 1, which is injection molded.
6. The coupler of claim 1, which is at least one of solvent bondable, heat sealable, laser weldable, and radio frequency sealable to the tubing.
7. A coupler comprising a conductive polymer material that is so constructed and arranged to join tubing, wherein the conductive polymer material includes a polymer matrix and a conductive component incorporated within the polymer matrix, and wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.
8. The coupler of claim 7, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.
9. The coupler of claim 7, which has a generally cylindrical shape with a first opening to receive a first tubing member and a second opening to receive a second tubing member.
10. The coupler of claim 7, which is extruded.
11. The coupler of claim 7, which includes a member that extends from at least a portion of an inner surface of the coupler to allow a length of a tubing joint that is formed with the coupler and the tubing to be pre-set.
12. The coupler of claim 7, which is injection molded.
13. The coupler of claim 7, which is at least one of solvent bondable, heat sealable, laser weldable, and radio frequency sealable to the tubing.
14. A coupler comprising:
a housing made of a conductive polymer material;
a first opening at a first end of the housing to receive a first tubing member; and
a second opening at a second end of the housing to receive a second tubing member.
15. The coupler of claim 14, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophenes, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.
16. The coupler of claim 14, wherein the conductive polymer material includes a polymer matrix and a conductive component incorporated within the polymer matrix, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof, and wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.
17. The coupler of claim 14, which is extrudable.
18. The coupler of claim 14, which includes a member that extends from at least a portion of an inner surface of the coupler and acts as a stop for the first and second tubing members, thereby allowing a length of a tubing joint that is formed with the coupler and the first and second tubing members to be pre-set.
19. The coupler of claim 14, which is injection molded.
20. The coupler of claim 14, which is at least one of solvent bondable, heat sealable, laser weldable, and radio frequency sealable to the first and second tubing members.
US11/626,241 2002-04-10 2007-01-23 Conductive polymer materials and applications thereof including monitoring and providing effective therapy Abandoned US20070117010A1 (en)

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130281985A1 (en) * 2010-12-15 2013-10-24 Valeria Querol Garcia Three-Lobe Drainage Hose
US20160356667A1 (en) * 2008-06-26 2016-12-08 Gambro Lundia Ab Methods and devices for monitoring the integrity of a fluid connection

Families Citing this family (35)

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Publication number Priority date Publication date Assignee Title
US6497676B1 (en) 2000-02-10 2002-12-24 Baxter International Method and apparatus for monitoring and controlling peritoneal dialysis therapy
US20030125662A1 (en) 2002-01-03 2003-07-03 Tuan Bui Method and apparatus for providing medical treatment therapy based on calculated demand
US20040254513A1 (en) 2002-04-10 2004-12-16 Sherwin Shang Conductive polymer materials and applications thereof including monitoring and providing effective therapy
US7052480B2 (en) 2002-04-10 2006-05-30 Baxter International Inc. Access disconnection systems and methods
US7022098B2 (en) 2002-04-10 2006-04-04 Baxter International Inc. Access disconnection systems and methods
US10155082B2 (en) 2002-04-10 2018-12-18 Baxter International Inc. Enhanced signal detection for access disconnection systems
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
US7530962B2 (en) * 2005-06-16 2009-05-12 Edward Allan Ross Method for detecting the disconnection of an extracorporeal device using a patient's endogenous electrical voltages
NZ593511A (en) * 2006-01-30 2012-09-28 Univ California Peritoneal dialysis methods and apparatus
US8477102B2 (en) * 2006-03-22 2013-07-02 Eastman Kodak Company Increasing conductive polymer life by reversing voltage
DE102006041265B3 (en) * 2006-09-02 2007-12-06 Fresenius Medical Care Deutschland Gmbh Vascular access e.g. butterfly cannula, creating device for extracorporeal blood treatment, has base body with electrically conductive contact component provided at lower side of fin pieces, where body is made of non-conductive material
DE102006042336A1 (en) * 2006-09-08 2008-03-27 Fresenius Medical Care Deutschland Gmbh Apparatus and method for monitoring an access to a patient, in particular a vascular access in extracorporeal blood treatment
US7731689B2 (en) 2007-02-15 2010-06-08 Baxter International Inc. Dialysis system having inductive heating
US7998115B2 (en) * 2007-02-15 2011-08-16 Baxter International Inc. Dialysis system having optical flowrate detection
US8361023B2 (en) 2007-02-15 2013-01-29 Baxter International Inc. Dialysis system with efficient battery back-up
US8558964B2 (en) 2007-02-15 2013-10-15 Baxter International Inc. Dialysis system having display with electromagnetic compliance (“EMC”) seal
US8870812B2 (en) 2007-02-15 2014-10-28 Baxter International Inc. Dialysis system having video display with ambient light adjustment
US8287724B2 (en) * 2007-07-05 2012-10-16 Baxter International Inc. Dialysis fluid measurement systems using conductive contacts
DE102007039581A1 (en) 2007-08-22 2009-02-26 Fresenius Medical Care Deutschland Gmbh Apparatus and method for monitoring an access to a patient
US7899552B2 (en) * 2007-10-15 2011-03-01 Cardiac Pacemakers, Inc. Conductive composite electrode material
US7908016B2 (en) * 2007-10-19 2011-03-15 Cardiac Pacemakers, Inc. Fibrous electrode material
DE102008001545A1 (en) * 2008-05-05 2009-11-12 Robert Bosch Gmbh Probe, fuel feed and method of manufacturing a measuring probe
DE102009060668A1 (en) 2009-12-28 2011-06-30 Fresenius Medical Care Deutschland GmbH, 61352 Apparatus and method for monitoring an extracorporeal blood treatment
DE102010007914A1 (en) 2010-02-12 2012-12-27 Fresenius Medical Care Deutschland Gmbh Apparatus and method for monitoring a vascular access for an extracorporeal blood treatment
CN102770169B (en) * 2010-02-22 2015-08-26 旭化成医疗株式会社 Medical appliances, and hollow fiber membrane type medical device
JP5555031B2 (en) * 2010-03-30 2014-07-23 旭化成メディカル株式会社 The hollow fiber membrane type medical devices
US8858185B2 (en) * 2010-06-23 2014-10-14 Hospira, Inc. Fluid flow rate compensation system using an integrated conductivity sensor to monitor tubing changes
US9861733B2 (en) 2012-03-23 2018-01-09 Nxstage Medical Inc. Peritoneal dialysis systems, devices, and methods
CA2830085A1 (en) 2011-03-23 2012-09-27 Nxstage Medical, Inc. Peritoneal dialysis systems, devices, and methods
US10022498B2 (en) 2011-12-16 2018-07-17 Icu Medical, Inc. System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy
US9662485B2 (en) * 2012-05-30 2017-05-30 Fenwal, Inc. Ensured component bonding
CN103830791B (en) * 2012-11-27 2017-02-22 深圳先进技术研究院 Automated peritoneal dialysis machine
WO2014194089A1 (en) 2013-05-29 2014-12-04 Hospira, Inc. Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system
JP2015097778A (en) * 2013-10-17 2015-05-28 セイコーエプソン株式会社 Fluid transporting device and abnormality determination method of transporting tube
US10184889B2 (en) * 2015-06-29 2019-01-22 Bitron S.P.A. Sensor device for optically detecting characteristics of a fluid

Citations (93)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3659591A (en) * 1970-08-24 1972-05-02 Doll Research Electromagnetic flowmeter
US3667475A (en) * 1971-05-10 1972-06-06 Nat Equipment Research Inc Endo-tracheal tube adaptors for use in administering gases
US3722504A (en) * 1969-12-23 1973-03-27 P Sawyer Method of screening substances for use in the treatment of circulatory system diseases
US3731685A (en) * 1971-04-01 1973-05-08 W Eidus Moisture indicating strip for diapers and surgical dressings
US3810140A (en) * 1972-10-30 1974-05-07 W Finley Apparatus for the programmed treatment of bed wetting
US3809078A (en) * 1972-07-20 1974-05-07 A Mozes Detector device for detecting unintentional urination
US3814249A (en) * 1970-05-25 1974-06-04 Eaton Medical Electronics Inc Dialysis apparatus
US3878095A (en) * 1974-05-02 1975-04-15 Advanced Medical Sciences Inc Dialysis apparatus
US3882861A (en) * 1973-09-24 1975-05-13 Vital Assists Auxiliary control for a blood pump
US3946731A (en) * 1971-01-20 1976-03-30 Lichtenstein Eric Stefan Apparatus for extracorporeal treatment of blood
US3953790A (en) * 1974-10-31 1976-04-27 Baxter Laboratories, Inc. Conductivity monitoring system
US4017190A (en) * 1975-07-18 1977-04-12 Halbert Fischel Blood leak detector comparing intensities of high absorption band and low absorption band of a single beam of light passing through a sample
US4022211A (en) * 1974-08-14 1977-05-10 Kimberly-Clark Corporation Wetness indicator for absorbent pads
US4026800A (en) * 1974-04-19 1977-05-31 National Medical Care, Inc. Dialysis apparatus
US4085047A (en) * 1976-09-16 1978-04-18 Thompson Lester E Blood leak detector
US4087185A (en) * 1975-06-19 1978-05-02 Baxter Travenol Laboratories, Inc. Blood leak detector
US4181610A (en) * 1975-07-14 1980-01-01 Takeda Chemical Industries, Ltd. Blood leak detector suitable for use with artificial kidneys
US4191950A (en) * 1978-02-09 1980-03-04 Levin Anne F Anti-bed-wetting device
US4193068A (en) * 1976-03-16 1980-03-11 Ziccardi John J Hemorrhage alarms
US4192311A (en) * 1977-12-05 1980-03-11 Felfoldi James J Disposable diaper with wetness indicator
US4324687A (en) * 1979-02-15 1982-04-13 Louderback Allan Lee Blood biochemistry control standard
US4327731A (en) * 1980-07-07 1982-05-04 Powell Nelson B Moisture indicator
US4450527A (en) * 1982-06-29 1984-05-22 Bomed Medical Mfg. Ltd. Noninvasive continuous cardiac output monitor
US4501583A (en) * 1983-06-15 1985-02-26 Extracorporeal, Inc. Hemodialysis access monitors
US4566990A (en) * 1982-11-05 1986-01-28 General Electric Company Synergistic effect of metal flake and metal or metal coated fiber on EMI shielding effectiveness of thermoplastics
US4583546A (en) * 1983-11-18 1986-04-22 Garde Patria P Blood loss monitor
US4648869A (en) * 1985-12-04 1987-03-10 American Hospital Supply Corporation Automatic infiltration detection system and method
US4661093A (en) * 1983-06-11 1987-04-28 Walter Beck Method for aspirating secreted fluids from a wound
US4734198A (en) * 1984-02-06 1988-03-29 Minntech Corporation Dialysis solution mixing system
US4739492A (en) * 1985-02-21 1988-04-19 Cochran Michael J Dialysis machine which verifies operating parameters
US4740755A (en) * 1986-05-30 1988-04-26 Cobe Laboratories, Inc. Remote conductivity sensor having transformer coupling in fluid flow path
US4741343A (en) * 1985-05-06 1988-05-03 Massachusetts Institute Of Technology Method and apparatus for measuring oxygen partial pressure and temperature in living tissue
US4796014A (en) * 1987-03-24 1989-01-03 Chia Jack T Device for detecting urine in diapers
US4898587A (en) * 1988-11-15 1990-02-06 Mera Csaba L Intravenous line stabilizing device
US4923613A (en) * 1987-05-15 1990-05-08 Hospal Industrie Method for determining a patient's blood sodium level and artificial kidney for the application thereof
US4931051A (en) * 1987-02-06 1990-06-05 Edge Enterprises, Inc. Wetness indicator
US4981467A (en) * 1990-02-27 1991-01-01 Baxter International Inc. Apparatus and method for the detection of air in fluid delivery systems
US5004459A (en) * 1984-07-09 1991-04-02 Peabody Alan M Continuous cyclic peritoneal dialysis system and method
US5015958A (en) * 1983-06-30 1991-05-14 Raychem Corporation Elongate sensors comprising conductive polymers, and methods and apparatus using such sensors
US5024756A (en) * 1988-03-03 1991-06-18 Gambro Ab Dialysis system and method therefor
US5084026A (en) * 1989-07-14 1992-01-28 Shapiro Robert A Intravenous apparatus holder
US5088990A (en) * 1989-08-30 1992-02-18 Hivale Ronald S I.V. alert system
US5121630A (en) * 1990-12-21 1992-06-16 Calvin Noel M Material monitoring device
US5197958A (en) * 1992-04-01 1993-03-30 Howell Wesley A Wetness indicating diaper
US5202261A (en) * 1990-07-19 1993-04-13 Miles Inc. Conductive sensors and their use in diagnostic assays
US5291181A (en) * 1992-03-30 1994-03-01 Deponte Dominic A Wet bed alarm and temperature monitoring system
US5310507A (en) * 1990-06-15 1994-05-10 Spectral Sciences, Inc. Method of making a conductive polymer selective species sensor
US5314410A (en) * 1992-02-10 1994-05-24 Marks Ronald L Entry indicator device for arterial or intravenous needle
US5392032A (en) * 1993-11-23 1995-02-21 Little Acorn Ventures Apparatus for sensing wet diaper including circuit breaker
US5395358A (en) * 1994-01-21 1995-03-07 Lu; Chin B. Wetting indicator for a diaper
US5399295A (en) * 1984-06-11 1995-03-21 The Dow Chemical Company EMI shielding composites
US5416027A (en) * 1992-01-07 1995-05-16 Laboratoire Eugedia Process and apparatus for monitoring the progress of hemodialysis
US5486286A (en) * 1991-04-19 1996-01-23 Althin Medical, Inc. Apparatus for performing a self-test of kidney dialysis membrane
US5510716A (en) * 1992-09-30 1996-04-23 Cobe Laboratories, Inc. Differential conductivity recirculation monitor
US5522809A (en) * 1992-02-18 1996-06-04 Paper-Pak Products, Inc. Absorbent adult fitted briefs and pads
US5602342A (en) * 1994-01-06 1997-02-11 Pacesetter Ab Method and device for measuring the flow of an electrolytic fluid
US5603902A (en) * 1993-07-16 1997-02-18 Cobe Laboratories, Inc. Method and apparatus for cleaning a dialysate circuit downstream of a dialyzer
US5760697A (en) * 1995-10-25 1998-06-02 Hartmann & Braun A.G. Multi-channel recording device
US5760694A (en) * 1996-05-07 1998-06-02 Knox Security Engineering Corporation Moisture detecting devices such as for diapers and diapers having such devices
US5762805A (en) * 1993-02-12 1998-06-09 Cobe Laboratories, Inc. Technique for extracorporeal treatment of blood
US5766212A (en) * 1996-05-16 1998-06-16 Uni-Charm Corporation Disposable diaper
US5862804A (en) * 1997-07-08 1999-01-26 Andco Tek, Inc. Leak point wetness sensor for urological investigation
US5868723A (en) * 1997-07-15 1999-02-09 Al-Sabah; Sabah Naser Moisture sensing and audio indicating apparatus for garments and associated methods
US5885264A (en) * 1996-07-02 1999-03-23 Uni-Charm Corporation Disposable training pants
US5891398A (en) * 1995-03-27 1999-04-06 California Institute Of Technology Sensor arrays for detecting analytes in fluids
US5900726A (en) * 1992-09-30 1999-05-04 Cobe Laboratories, Inc. Differential conductivity hemodynamic monitor
US5900817A (en) * 1998-02-17 1999-05-04 Olmassakian; Vahe Child monitoring system
US5903222A (en) * 1997-04-03 1999-05-11 Zaggie, Inc. Wet garment detector
US5904671A (en) * 1997-10-03 1999-05-18 Navot; Nir Tampon wetness detection system
US5908411A (en) * 1997-11-20 1999-06-01 Nippon Koudoshi Kougyou Co., Ltd. Moisture annunciator
US6015342A (en) * 1998-06-03 2000-01-18 Carrier Corporation Louver apparatus for air conditioning unit
US6038914A (en) * 1997-02-27 2000-03-21 Bristol-Myers Squibb Company Leak detection system for liquid processing device
US6063042A (en) * 1998-09-28 2000-05-16 Navot; Nir Method for diagnosis of menorrhagia menstrual cycle disorders and their causes
US6169225B1 (en) * 1997-09-29 2001-01-02 Uni-Charm Corporation Disposable training pants having a suspended crotch covering sheet
US6171289B1 (en) * 1998-11-06 2001-01-09 Plasto Sa Safety device for colostomy having a wetness detector and alarm
US6187199B1 (en) * 1997-01-24 2001-02-13 Fresenius Medical Care Deutschland Gmbh Process and device for determining hemodialysis parameters
US6200250B1 (en) * 1996-05-07 2001-03-13 Knox Security Engineering Corporation Diapers with moisture detection and process and apparatus for making them
US6208880B1 (en) * 1997-02-27 2001-03-27 Terumo Cardiovascular Systems Corporation Blood parameter measurement device
US6210591B1 (en) * 1994-09-16 2001-04-03 Transonic Systems, Inc. Method to measure blood flow rate in hemodialysis shunts
US6217539B1 (en) * 1996-11-30 2001-04-17 Fresenius Medical Care Deutschland Gmbh Method of in-vivo determination of hemodialysis parameters and a device for carrying out the method
US20020036375A1 (en) * 2000-09-19 2002-03-28 Yasuhiro Matsuda Paper feeding apparatus
US20020042125A1 (en) * 1997-08-13 2002-04-11 Cepheid Method for separating analyte from a sample
US6372848B1 (en) * 2000-10-10 2002-04-16 Baxter International Inc. Blend of ethylene and α-olefin copolymers obtained using a metallocene catalyst for fabricating medical films and tubings
US20020055167A1 (en) * 1999-06-25 2002-05-09 Cepheid Device incorporating a microfluidic chip for separating analyte from a sample
US6387329B1 (en) * 1998-11-16 2002-05-14 California Institute Of Technology Use of an array of polymeric sensors of varying thickness for detecting analytes in fluids
US20030036719A1 (en) * 1999-12-28 2003-02-20 Sara Giacomelli Method and device for monitoring the access to the cardiovascular system of a patient
US20030075498A1 (en) * 2001-06-01 2003-04-24 Watkins Randolph H. Hemodialyzer headers
US20030083901A1 (en) * 2001-06-22 2003-05-01 Bosch Juan P. Process for providing dialysis and other treatments
US20030093069A1 (en) * 1996-01-19 2003-05-15 Ep Technologies, Inc. Expandable-collapsible electrode structures made of electrically conductive material
US20030094369A1 (en) * 2001-10-01 2003-05-22 Brigham Young University Method of simultaneously concentrating and separating analytes
US20050010157A1 (en) * 2003-06-04 2005-01-13 Gambro Lundia Ab. Joint for fluid transport lines for medical use
US7011855B2 (en) * 1994-07-01 2006-03-14 Baxter International Inc. Biochemically balanced peritoneal dialysis solutions
US7053059B2 (en) * 2003-07-25 2006-05-30 Baxter International Inc. Dialysis solutions with reduced levels of glucose degradation products

Family Cites Families (307)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3309924A (en) 1964-06-22 1967-03-21 Universtity Of California Electromagnetic flow meter
US3682162A (en) 1968-12-13 1972-08-08 Wellcome Found Combined electrode and hypodermic syringe needle
US3618602A (en) 1969-08-28 1971-11-09 Robert F Shaw Liquid infusion infiltration detection apparatus and method
US3759247A (en) 1970-08-24 1973-09-18 Doll Research Electromagnetic flowmeter
US3699960A (en) 1971-01-04 1972-10-24 Frank B Freedman Parabiotic dialysis apparatus
US3682172A (en) 1971-01-04 1972-08-08 Frank B Freedman Parabiotic dialysis apparatus
FR2120507A5 (en) 1971-01-06 1972-08-18 Rhone Poulenc Sa
US3759261A (en) 1972-03-09 1973-09-18 R Wang Yer diapers disposable diapers and disposable diapers with water proof la
US3832993A (en) 1972-09-13 1974-09-03 W Clipp Blood detecting device
US3778570A (en) 1972-10-05 1973-12-11 J Shuman Enuresis bed pad
US3832067A (en) 1972-11-24 1974-08-27 Kopf D Syst Colorimeter for detecting blood leaks in an artificial kidney machine
US3864676A (en) 1973-09-10 1975-02-04 Helene Macias Moisture detector
US3867688A (en) 1973-12-18 1975-02-18 Atomic Energy Commission Electrodeless conductance measurement device
US3900396A (en) 1974-03-22 1975-08-19 Baxter Laboratories Inc Blood leak detector
US4055496A (en) 1974-04-19 1977-10-25 National Medical Care, Inc. Dialysis apparatus
US3979665A (en) 1975-02-05 1976-09-07 Baxter Laboratories, Inc. Conductivity monitoring system
JPS5531407Y2 (en) 1975-02-19 1980-07-26
US4010749A (en) 1975-05-09 1977-03-08 Shaw Robert F Method of detecting infiltration of infused liquid by comparing altered skin temperature with skin temperature in area of infiltrated liquid
US4060485A (en) 1975-06-09 1977-11-29 I T L Technology, Inc. Dialysis apparatus
IT1048235B (en) 1975-10-13 1980-11-20 Dasco Spa Conductivity meter for concentration determination - incorporating circuit with thermistor temperature compensation
DE2636290A1 (en) 1976-08-12 1978-02-16 Fresenius Chem Pharm Ind A device for controlling and monitoring the blood flow in the blood dialysis, and -perfusion -diafiltration using only one connection point to the bloodstream of the patient (single-needle-technique)
US4366051A (en) 1976-11-19 1982-12-28 Halbert Fischel Hemodialysis system
SE403004B (en) 1976-12-03 1978-07-24 Gambro Ab pressure switch
US4167038A (en) 1977-10-17 1979-09-04 Hycel, Inc. Calculated parameter generation in a hematology parameter measurement apparatus
US4294263A (en) 1977-12-07 1981-10-13 Air Shields, Inc. System for detecting probe dislodgement
CS200909B1 (en) 1977-12-23 1980-10-31 Petr Slovak Haemodlialysation device
US4162490A (en) 1978-01-26 1979-07-24 Fu Chien Hung Toilet training device
US4166961A (en) 1978-03-22 1979-09-04 Hoechst Aktiengesellschaft Method and apparatus for detecting a blood leak in a hemodialysis system
JPS5744845Y2 (en) 1978-03-31 1982-10-04
DE2838414C2 (en) 1978-09-02 1984-10-31 Fresenius Ag, 6380 Bad Homburg, De
US4231370A (en) 1979-06-18 1980-11-04 The Procter & Gamble Company Disposable diaper type garment having wetness indicator
WO1981000295A1 (en) 1979-07-25 1981-02-05 Sabco Ltd Pressure responsive disconnecting fluid,coupling and shut-off valve
US4354504A (en) 1979-09-04 1982-10-19 Bro William J Thermal diffusion flow probe
US4295475A (en) 1979-10-26 1981-10-20 Air Shields, Inc. Probe and system for detecting probe dislodgement
CA1153580A (en) 1979-10-29 1983-09-13 Jeremy R. Hill Liquid conductivity measuring system and sample cards therefor
US4303887A (en) 1979-10-29 1981-12-01 United States Surgical Corporation Electrical liquid conductivity measuring system
JPS5847965Y2 (en) 1979-11-27 1983-11-01
DE2948768A1 (en) 1979-12-04 1981-06-11 Brehm Heide Incontinence pants incorporating acoustic bed wetting alarm - with moisture detected by bridging of conductor wires or foil strips
DE3223086C2 (en) 1981-01-22 1988-09-01 Nippon Acchakutanshi Seizo K.K., Osaka, Jp
DE3045514A1 (en) 1980-12-03 1982-07-01 Udo Petscher Nappy with electrically conducting threads to detect wetting - connected to electronic signalling circuit esp. piezoceramic oscillator
US4559496A (en) 1981-07-24 1985-12-17 General Electric Company LCD Hook-on digital ammeter
JPS649856B2 (en) 1981-08-18 1989-02-20 Toyoda Chuo Kenkyusho Kk
US4399824A (en) 1981-10-05 1983-08-23 Air-Shields, Inc. Apparatus for detecting probe dislodgement
US4399823A (en) 1981-10-05 1983-08-23 Air-Shields, Inc. Apparatus for detecting probe dislodgement
EP0089003B1 (en) 1982-03-10 1987-11-25 Kabushiki Kaisha Toyota Chuo Kenkyusho Blood purification apparatus
US4427994A (en) 1982-03-15 1984-01-24 The Bendix Corporation Color separator for a video display generator
US4539559A (en) 1982-03-29 1985-09-03 Hugh Kelly Portable, disposable warning device for detecting urine-wet undergarments
US4484573A (en) 1982-07-22 1984-11-27 Naewae Electric Co., Ltd. Alarm device for use in a baby's diaper
US5030487A (en) * 1984-04-04 1991-07-09 Raychem Corporation Heat recoverable article comprising conductive polymer compositions
EP0328163B1 (en) 1983-04-11 1991-12-18 Ivac Corporation Fault detection apparatus for parenteral infusion system and method of detecting faults in such a system
EP0328162B1 (en) 1983-04-11 1993-02-10 Ivac Corporation Fault detection apparatus for parenteral infusion system and method of detecting a fault in a parenteral infusion system
US4534756A (en) 1983-04-11 1985-08-13 Ivac Corporation Fault detection apparatus and method for parenteral infusion system
GB2145859A (en) 1983-08-30 1985-04-03 Kek How Ng Lift urine/wetting alarm system
DE3440584A1 (en) 1984-11-07 1986-05-07 Mund Andreas Alexander Device for recording moisture
CH676060A5 (en) 1985-02-12 1990-11-30 Svaetopluk Radakovic
CA1273822A (en) 1985-06-03 1990-09-11 Katsutoshi Rokuta Water content detecting device for diaper
JPS6242047A (en) * 1985-08-19 1987-02-24 Toyota Central Res & Dev Lab Inc Sulfuric acid concentration detector
US4661096A (en) 1985-09-06 1987-04-28 Edward Teeple Anti-air embolism and antiblood loss device for CVP catheter
JPS6254157U (en) 1985-09-25 1987-04-03
US5211201A (en) 1986-03-04 1993-05-18 Deka Products Limited Partnership Intravenous fluid delivery system with air elimination
US4791932A (en) 1986-03-05 1988-12-20 Cordis Corporation Extracorporeal sensing module
US4707906A (en) 1986-03-25 1987-11-24 Posey John T Method of attaching tube to a tube holder
US4710163A (en) 1986-06-06 1987-12-01 Ivac Corporation Detection of fluid flow faults in the parenteral administration of fluids
DE3626825C2 (en) 1986-08-08 1989-01-05 Gruenbeck Wasseraufbereitung Gmbh, 8884 Hoechstaedt, De
CA1300866C (en) 1986-11-17 1992-05-19 Tadao Shimomura Body fluid-absorbing article
DE3639797C1 (en) 1986-11-21 1988-02-25 Fresenius Ag Method and device for monitoring the correct composition of dialysis solution, in particular for bicarbonate dialysis
DE3640089C2 (en) 1986-11-24 1988-12-22 Fresenius Ag, 6380 Bad Homburg, De
DE3640900C2 (en) 1986-11-29 1990-10-25 Stegat, Harry, Prof. Dr.
US4862146A (en) 1987-03-27 1989-08-29 Raychem Corporation Detection apparatus
FR2614130B1 (en) * 1987-04-15 1992-01-17 Lorraine Carbone Material having a resistivity at positive temperature coefficient
GB8717235D0 (en) 1987-07-21 1987-08-26 Darling Products Ltd J E Moisture leak alarm
JPS6452473U (en) 1987-09-25 1989-03-31
US4976698A (en) 1987-10-23 1990-12-11 Stokley Manuel H Intravenous catheter and tubing stabilization device
US4846792A (en) 1988-03-08 1989-07-11 Baxter International Inc. Automatic infiltration detection system and method
US4979940A (en) 1988-03-08 1990-12-25 Baxter International Inc. Infusion system, methodology, and algorithm for identifying patient-induced pressure artifacts
JPH01250733A (en) 1988-03-30 1989-10-05 Kubota Ltd Method and apparatus for detecting deterioration of inner surface lining wall
US5026348A (en) 1988-06-06 1991-06-25 The General Hospital Corporation Apparatus and method for the detection of IV catheter obstruction and extravasation
DE3823859A1 (en) 1988-07-14 1990-01-18 Bernd Kellerberg Device for testing the degree of penetration of moisture of nappies (diapers)
US5036859A (en) 1988-07-26 1991-08-06 Travis International, Inc. Moisture detector and indicator
DE3836712A1 (en) 1988-10-28 1990-05-03 Volker Dipl Chem Genrich Highly flexible large-area sensor mat
US4881413A (en) 1988-10-31 1989-11-21 Bio-Medicus, Inc. Blood flow detection device
JPH0321257A (en) 1989-01-31 1991-01-30 Aisin Seiki Co Ltd Driving device for blood pump
US4938079A (en) 1989-03-06 1990-07-03 Ivac Corporation Thermal transit time flow measurement system
US4977906A (en) 1989-03-07 1990-12-18 Scipio William J Di Diurnal rehabilitation for incontinence trainer
DE3909548C2 (en) 1989-03-22 1991-04-18 Richard Hirschmann Gmbh & Co, 7300 Esslingen, De
US5039970A (en) 1989-05-17 1991-08-13 Minnesota Mining And Manufacturing Company Self-aligning core for induction coil
DE4000961A1 (en) 1990-01-16 1991-07-18 Adam Becker Arrangement protective dressing preventing infant or nappy dermatitis - contain rod-shaped sensor carrying moisture detector in nappy with battery, signal converter and warning device
US5139482A (en) 1990-01-18 1992-08-18 Simeon Paula S Fluid infusion line monitor
FR2658723B1 (en) 1990-02-23 1992-04-30 Hospal Ind FLOW SENSOR a substitution fluid in an extracorporeal blood circulation circuit.
US5146414A (en) 1990-04-18 1992-09-08 Interflo Medical, Inc. Method and apparatus for continuously measuring volumetric flow
DE4018953A1 (en) 1990-05-04 1992-01-23 Augustin Hans Ulrich Disposable intermediate layer with moisture sensor and mfg. process - has absorbent layer with film backing having central hole in which sensor is located and covered with film strip
DE4014572C2 (en) 1990-05-07 1992-04-30 Alexander 8021 Icking De Staeblein
US5145645A (en) 1990-06-15 1992-09-08 Spectral Sciences, Inc. Conductive polymer selective species sensor
US5250439A (en) 1990-07-19 1993-10-05 Miles Inc. Use of conductive sensors in diagnostic assays
DE4023336A1 (en) 1990-07-23 1992-02-06 Hessberg Sigfried Unit for monitoring of a catheter body fluid leaking
US5022438A (en) 1990-08-20 1991-06-11 Faraon Chaul Cesar Fluids rate of flow saving or limiting device
FR2669217A1 (en) 1990-11-26 1992-05-22 Tekung Lee Disposable diaper (nappy) comprising a wetness detection alarm
US5247434A (en) 1991-04-19 1993-09-21 Althin Medical, Inc. Method and apparatus for kidney dialysis
US5225495A (en) 1991-07-10 1993-07-06 Richard C. Stewart, II Conductive polymer film formation using initiator pretreatment
US5137033A (en) 1991-07-15 1992-08-11 Norton John L Patient monitoring device
FR2680678A1 (en) 1991-09-02 1993-03-05 Ly Joel Warning device for diapers
DE4137628C1 (en) * 1991-11-15 1992-12-03 Fresenius Ag, 6380 Bad Homburg, De
US5248934A (en) 1992-01-10 1993-09-28 Roveti Denes K Method and apparatus for converting a conventional DC multimeter to an AC impedance meter
US5454374A (en) 1992-01-17 1995-10-03 Omachi; Rodney S. Pressure-measuring method and needle system for hemodialysis
US5341127A (en) 1992-03-23 1994-08-23 Smith Robert J Self-contained bed wetting alarm
US5266928A (en) 1992-05-29 1993-11-30 Johnson Lonnie G Wet diaper detector
US5838240A (en) 1992-05-29 1998-11-17 Johnson Research & Development Company, Inc. Wet diaper detector
US5469145A (en) 1992-05-29 1995-11-21 Johnson; Lonnie Wet diaper detector
US5790036A (en) 1992-07-22 1998-08-04 Health Sense International, Inc. Sensor material for use in detection of electrically conductive fluids
EP1063624A1 (en) 1992-07-22 2000-12-27 Health Sense International, Inc. System for detection of electrically conductive fluids
US5331287A (en) * 1992-07-31 1994-07-19 Hughes Aircraft Company Device and method for sensing water and/or acid in the presence of water in non-aqueous media
IT1255495B (en) 1992-09-18 1995-11-09 Francesco Bellifemine A device for monitoring an intravenous infusion system
US5264830A (en) 1992-09-18 1993-11-23 Little Acorn Ventures, Inc. Apparatus for sensing wet diaper
DE4239937C2 (en) 1992-11-27 1995-08-24 Fresenius Ag Procedure for determining the operability of a partial device of a hemodialysis machine, and device for carrying out this method
CA2130833C (en) 1993-01-19 2002-06-18 Patrick Balteau Multiple chamber container
US5350357A (en) 1993-03-03 1994-09-27 Deka Products Limited Partnership Peritoneal dialysis systems employing a liquid distribution and pumping cassette that emulates gravity flow
EP0614652B1 (en) 1993-03-10 2001-07-18 Nichiban Co. Ltd. Sticking material for hemostasis
TW266380B (en) * 1993-03-29 1995-12-21 Seikosya Kk
US5468236A (en) 1993-06-09 1995-11-21 Kimberly-Clark Corporation Disposable absorbent product incorporating chemically reactive substance
WO1995002164A1 (en) 1993-07-07 1995-01-19 Ic Sensors, Inc. Pulsed thermal flow sensor system
US5354289A (en) 1993-07-23 1994-10-11 Principle Business Enterprises Inc. Absorbent product including super absorbent material and a fluid absorption capacity monitor
US5802814A (en) 1993-08-20 1998-09-08 Nissho Corporation Method of wrapping a bundle of fiber
US5435010A (en) 1993-10-18 1995-07-25 May; Robert E. Moisture sensitive article of clothing and method of manufacturing the same
CA2175903A1 (en) 1993-11-05 1995-05-11 Stanley Robert Elsdon Automatic shut-off valve arrangement
CA2102569A1 (en) 1993-11-05 1995-05-06 Stanley Robert Elsdon Automatic shut-off valve arrangement
US5813432A (en) 1993-11-05 1998-09-29 Emco Wheaton Fleet Fueling Corp. Automatic shut-off valve arrangement
EP0683926A4 (en) 1993-12-14 1996-05-15 Plc Medical Systems Inc Unitary ecg monitor lead and needle electrode system.
FR2713937B1 (en) 1993-12-17 1996-05-31 Hospal Ind A method of determining a parameter indicative of the progress of an extracorporeal blood treatment.
WO1995022828A1 (en) 1994-02-17 1995-08-24 Interlink Electronics, Inc. Layered pressure sensitive transducer and method for making same
JP3410818B2 (en) 1994-06-20 2003-05-26 愛知時計電機株式会社 Electromagnetic flow meter and a flow tube section
US5702377A (en) 1994-09-01 1997-12-30 Kimberly-Clark Worldwide, Inc. Wet liner for child toilet training aid
EP0705611A3 (en) 1994-09-07 1996-05-01 Medisystems Technology Corp
US5685989A (en) 1994-09-16 1997-11-11 Transonic Systems, Inc. Method and apparatus to measure blood flow and recirculation in hemodialysis shunts
US5568128A (en) 1994-11-14 1996-10-22 Nair; Rajesh M. Self learning diaper wetness detector and toilet trainer
IT1271099B (en) 1994-11-25 1997-05-26 Francesco Bellifemine A device for monitoring and controlling an intravenous infusion system improved
US5649914A (en) 1994-12-22 1997-07-22 Kimberly-Clark Corporation Toilet training aid
US5681298A (en) 1994-12-22 1997-10-28 Kimberly-Clark Worldwide, Inc. Toilet training aid creating a temperature change
US5932110A (en) 1995-02-13 1999-08-03 Aksys, Ltd. Dialysate conductivity adjustment in a batch dialysate preparation system
US5591344A (en) 1995-02-13 1997-01-07 Aksys, Ltd. Hot water disinfection of dialysis machines, including the extracorporeal circuit thereof
NL9500338A (en) 1995-02-22 1996-10-01 Wilhelmus Theodorus Franciscus An assembly for detecting and signaling of moisture.
US5788833A (en) 1995-03-27 1998-08-04 California Institute Of Technology Sensors for detecting analytes in fluids
US5571401A (en) 1995-03-27 1996-11-05 California Institute Of Technology Sensor arrays for detecting analytes in fluids
US5579765A (en) 1995-05-30 1996-12-03 Cox; Danny L. Monitor to detect bleeding
US5657000A (en) 1995-06-02 1997-08-12 Cobe Laboratories, Inc. Peristaltic pump occlusion detector and adjuster
US5718692A (en) 1995-06-06 1998-02-17 Twineath, L.L.C. Self-retaining single insertion double catheter assembly and method for making double catheter systems
US5954691A (en) 1995-06-07 1999-09-21 Biolink Corporation Hemodialysis access apparatus
US6206851B1 (en) 1995-06-07 2001-03-27 Biolink Corporation Hemodialysis access apparatus
IT1276468B1 (en) 1995-07-04 1997-10-31 Hospal Dasco Spa Method and automatic dialysis equipment
US6183437B1 (en) 1995-07-10 2001-02-06 Frank J. Walker Electronic control unit and tubing assembly system for automatically controlling urinary irrigation
IL114616A (en) 1995-07-17 1999-07-14 Ophir Michael Safety valve for infusion apparatus
US5542932A (en) 1995-07-20 1996-08-06 Daugherty; Charles W. Bloodless flashback vent
US5779657A (en) 1995-07-21 1998-07-14 Daneshvar; Yousef Nonstretchable wound cover and protector
FR2737124B1 (en) 1995-07-24 1997-11-14 Hospal Ind Device for detection of accidental withdrawal of a tube plunges into a cavity or a body conduit of a patient
US5790035A (en) 1995-08-02 1998-08-04 Ho; Geng Kaung Reusable temperature and wetness alarm device for the diaper
SE508374C2 (en) 1995-09-12 1998-09-28 Gambro Med Tech Ab Method and apparatus for detecting the condition of a blood vessel access
FR2739780B1 (en) 1995-10-12 1997-11-14 Hospal Ag A collection of a dialysis liquid sample uses
US5570082A (en) 1995-10-13 1996-10-29 Mahgerefteh; Nasser Remote wetness sensor for diapers
US5674752A (en) 1995-10-16 1997-10-07 The United States Of America As Represented By The Secretary Of The Navy Conductive polymer coated fabrics for chemical sensing
JP3310842B2 (en) 1995-11-29 2002-08-05 ユニ・チャーム株式会社 Disposable diapers
US5803915A (en) 1995-12-07 1998-09-08 Ohmeda Inc. System for detection of probe dislodgement
US5959535A (en) 1995-12-20 1999-09-28 Remsburg; Ralph Electrogalvanic-powered diaper wetness sensor
US6013058A (en) 1996-06-12 2000-01-11 Biolink Corporation Device for subcutaneous accessibility
SE510126C2 (en) 1996-06-13 1999-04-19 Althin Medical Ab Dialysis machine with control panel movable
JPH1033662A (en) 1996-07-25 1998-02-10 Kanegafuchi Chem Ind Co Ltd Ex vivo blood circulating device
US5938038A (en) 1996-08-02 1999-08-17 Dial Tool Industries, Inc. Parts carrier strip and apparatus for assembling parts in such a strip
US5842998A (en) 1996-08-21 1998-12-01 Cleveland Clinic Foundation Apparatus for determining the conductivity of blood
US5845644A (en) 1996-08-26 1998-12-08 Hughes; Charles B. Bladder and bowel training system
ZA9708002B (en) 1996-09-11 1998-03-02 Baxter Int Containers and methods for storing and admixing medical solutions.
US5730418A (en) 1996-09-30 1998-03-24 The Kipp Group Minimum fluid displacement medical connector
US6117099A (en) 1996-10-23 2000-09-12 In-Line Diagnostics Corporation System and method for noninvasive hemodynamic measurements in hemodialysis shunts
US5796345A (en) 1997-01-13 1998-08-18 Leventis; Nicholas Apparatus for detecting moisture in garments
US5931801A (en) 1997-01-21 1999-08-03 Vasca, Inc. Valve port assembly with interlock
US7056316B1 (en) 1997-01-21 2006-06-06 Vasca, Inc. Valve port and method for vascular access
JPH10211278A (en) 1997-01-30 1998-08-11 Nippon Kanko Kk Drip leak detection and alarm device
US6595943B1 (en) 1997-02-14 2003-07-22 Nxstage Medical, Inc. Systems and methods for controlling blood flow and waste fluid removal during hemofiltration
US5817076A (en) 1997-02-25 1998-10-06 Fard; Safieh Bahramian Toilet training diapers
US6015387A (en) 1997-03-20 2000-01-18 Medivas, Llc Implantation devices for monitoring and regulating blood flow
US6402207B1 (en) 1997-06-09 2002-06-11 Qd Enterprises, Llc Safety indexed medical connectors
DE19728031A1 (en) 1997-07-01 1999-01-07 Bernd Horst Dr Meier Moving liquid flow and volume measuring method
DE19734002C1 (en) 1997-08-06 1998-09-17 Fresenius Medical Care De Gmbh Blood dialysis process with process monitoring system on dialysis machine
US5941248A (en) 1997-08-20 1999-08-24 Wheeler; Alton D. Monitoring of patient bedding zones
FR2767478B1 (en) 1997-08-21 1999-10-01 Hospal Ind Device and method for adjusting the sodium concentration in a dialysis fluid for a prescription
FR2767477B1 (en) 1997-08-21 1999-10-08 Hospal Ind dialysis apparatus for controlling, independent of way, the concentration of at least two ionic substances inside the body of a patient
DE19739099C1 (en) * 1997-09-06 1999-01-28 Fresenius Medical Care De Gmbh Monitoring of a blood container inlet during external blood treatment
SE510286C2 (en) 1997-09-22 1999-05-10 Gambro Med Tech Ab Method and device for monitoring the infusion pump in a hemodialysis or hemodiafiltreringsmaskin
US6075178A (en) 1997-09-29 2000-06-13 Kimberly-Clark Worldwide, Inc. Absorbent article with wetness indicator
DE19746377C1 (en) 1997-10-21 1999-07-01 Fresenius Medical Care De Gmbh Blood treatment device with a device for continuous monitoring of the patient's blood pressure
WO1999024145A1 (en) 1997-11-07 1999-05-20 Aksys, Ltd. Blood line separation warning device for extracorporeal circuits
US6189388B1 (en) 1997-11-12 2001-02-20 Gambro, Inc. Access flow monitoring using reversal of normal blood flow
DE69727986T2 (en) 1997-11-26 2005-01-05 E-Z-Em, Inc. Detection of extravasation
CH692570A5 (en) * 1997-12-05 2002-08-15 Peter F Meier Apparatus for monitoring a catheter device.
DE19757523C1 (en) 1997-12-23 1999-04-22 Fresenius Medical Care De Gmbh Method of monitoring functioning of blood distributing machine for dialysis
DE19801768C2 (en) 1998-01-19 2001-04-19 Fresenius Medical Care De Gmbh Method and apparatus for providing operative dialysis
US5947943A (en) 1998-02-02 1999-09-07 Lee; Frances Meiling Diaper visual indicator
GB9803299D0 (en) 1998-02-18 1998-04-08 Gallagher George Improved method and apparatus for monitoring intravenous drips
JPH11299889A (en) 1998-02-20 1999-11-02 Matsumoto Seisakusho:Kk Alarming device for drip infusion and alarming device for urine storage
DE19809945C2 (en) 1998-03-07 2002-02-21 Fresenius Medical Care De Gmbh Device for preparation of dialysing fluid with a means for monitoring selected parameters of the dialysis solution and method for monitoring selected parameters of the dialysis liquid in dialysis treatment
US6015386A (en) 1998-05-07 2000-01-18 Bpm Devices, Inc. System including an implantable device and methods of use for determining blood pressure and other blood parameters of a living being
WO1999062041A1 (en) 1998-05-28 1999-12-02 Safieh Bahramian Fard Wetness awareness training device
DE19823836C2 (en) 1998-05-28 2000-05-04 Fresenius Medical Care De Gmbh Apparatus and method for contactless measurement of the conductivity of a liquid in a flow channel
US6093869A (en) 1998-06-29 2000-07-25 The Procter & Gamble Company Disposable article having a responsive system including a feedback control loop
US6160198A (en) 1998-06-29 2000-12-12 The Procter & Gamble Company Disposable article having a discontinuous responsive system
US6149636A (en) 1998-06-29 2000-11-21 The Procter & Gamble Company Disposable article having proactive sensors
US6044691A (en) 1998-08-26 2000-04-04 Aksys, Ltd. Blood tubing set integrity tests for extracorporeal circuits
SE513522C2 (en) 1998-09-10 2000-09-25 Gambro Ab Device for monitoring a fluid pipe
US6575927B1 (en) 1998-09-25 2003-06-10 The Regents Of The University Of Michigan System and method for determining blood flow rate in a vessel
US6167765B1 (en) 1998-09-25 2001-01-02 The Regents Of The University Of Michigan System and method for determining the flow rate of blood in a vessel using doppler frequency signals
DE19848235C1 (en) 1998-10-20 2000-03-16 Fresenius Medical Care De Gmbh Method for monitoring supply to vessel and extra-corporeal blood treatment device for monitoring supply to vessel; inputs blood circulation pressure to computer to calculate values to identify errors in supply during dialysis
JP2000131286A (en) 1998-10-27 2000-05-12 Iwaki:Kk Non-polar conductivity sensor and its calibration method, disconnection detection method and failure diagnosis method
JP2000140092A (en) 1998-11-06 2000-05-23 Health & Safety System Lab Kk Method and device for monitoring medium
US6383158B1 (en) 1998-12-01 2002-05-07 Dsu Medical Corporation Dialysis pressure monitoring with clot suppression
US6794981B2 (en) 1998-12-07 2004-09-21 Honeywell International Inc. Integratable-fluid flow and property microsensor assembly
DE59914211D1 (en) 1998-12-24 2007-04-05 Fresenius Medical Care De Gmbh Apparatus for determining the distribution volume of a blood constituent during a blood treatment
US6397661B1 (en) 1998-12-30 2002-06-04 University Of Kentucky Research Foundation Remote magneto-elastic analyte, viscosity and temperature sensing apparatus and associated methods of sensing
DE19901078C1 (en) 1999-01-14 2000-02-17 Polaschegg Hans Dietrich Monitoring system for fistula or graft has instruments to detect pulse from patient's heart or external blood circulation pump
US6166639A (en) 1999-03-12 2000-12-26 Advanced Marketing Systems Corporation Personal emergency response system
DE19917197C1 (en) 1999-04-16 2000-07-27 Fresenius Medical Care De Gmbh Method to determine blood flow in vessel entrance of haemodialysis unit; involves measuring arterial and venous pressures when vessel entrance is open to allow blood flow and closed to prevent blood flow
US6113577A (en) 1999-04-23 2000-09-05 Canox International, Ltd. Intravascular access device positioning system
US6292102B1 (en) 1999-07-22 2001-09-18 Bed-Check Corporation Apparatus for detecting enuresis in a patient
DE19940624C5 (en) 1999-08-27 2006-11-16 Fresenius Medical Care Deutschland Gmbh Safety device for a blood treatment apparatus and method for increasing the safety of a blood treatment device
US6255396B1 (en) 1999-09-09 2001-07-03 Baxter International Inc. Cycloolefin blends and method for solvent bonding polyolefins
US6309673B1 (en) 1999-09-10 2001-10-30 Baxter International Inc. Bicarbonate-based solution in two parts for peritoneal dialysis or substitution in continuous renal replacement therapy
DE19947826B4 (en) 1999-10-05 2006-06-08 Disetronic Licensing Ag Device for the metered administration of an injectable product,
US6691040B2 (en) 1999-12-02 2004-02-10 Hospal Ag Method for determining a parameter indicative of the progress of an extracorporeal blood treatment
US6386050B1 (en) 1999-12-21 2002-05-14 Agilent Technologies, Inc. Non-invasive fluid flow sensing based on injected heat tracers and indirect temperature monitoring
US6500154B1 (en) 2000-01-11 2002-12-31 Canox International Ltd. Intravascular access device positioning system
JP3861193B2 (en) 2000-01-26 2006-12-20 株式会社鷺宮製作所 Electrical conductivity sensor
US6461329B1 (en) 2000-03-13 2002-10-08 Medtronic Minimed, Inc. Infusion site leak detection system and method of using the same
IT1320024B1 (en) 2000-04-07 2003-11-12 Gambro Dasco Spa Method for adjusting the infusion in a dialysis machine and the dialysis machine for the application of the aforementioned method.
US6890315B1 (en) 2000-05-23 2005-05-10 Chf Solutions, Inc. Method and apparatus for vein fluid removal in heart failure
US6595944B2 (en) 2000-06-17 2003-07-22 Fresenius Medical Care Deutschland Gmbh Dialysis machine and method of operating a dialysis machine
DE10032616A1 (en) 2000-07-08 2002-01-24 Mhm Harzbecher Medizintechnik System element for transducer connection in pressure-monitoring sets for extracorporeal circuits, e.g. in open-heart surgery, has a measuring chamber with a membrane which fits in a special channel in the housing
US6406460B1 (en) 2000-07-21 2002-06-18 Agecom, Inc. System and method for automatic needle change warning
US6445304B1 (en) 2000-08-11 2002-09-03 John J. Bandeian, Jr. Medical alarm system
US6585675B1 (en) 2000-11-02 2003-07-01 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
DE10100146B4 (en) 2001-01-03 2004-11-25 Fresenius Medical Care Deutschland Gmbh Dialysis apparatus and method for operating the same
EP1399193B1 (en) 2001-02-16 2014-01-08 Piedmont Renal Clinics, P.A. Automated peritoneal dialysis system and process with in-line sterilization of dialysate
US7422586B2 (en) 2001-02-28 2008-09-09 Angiodynamics, Inc. Tissue surface treatment apparatus and method
US6749567B2 (en) 2001-05-09 2004-06-15 Hemonix, Inc. Noninvasive method of measuring physiologic parameters
EP1401321A4 (en) 2001-05-17 2005-08-24 Thermal Technologies Inc Blood flow monitor for shock and resuscitation
US6623638B2 (en) 2001-06-01 2003-09-23 Baxter International Inc. Hemodialyzer having improved dialysate perfusion
ITTO20010583A1 (en) 2001-06-15 2002-12-16 Gambro Dasco Spa Circuit of circulation of blood to a dialysis machine and relative dialysis machine.
ITTO20010582A1 (en) 2001-06-15 2002-12-16 Gambro Dasco Spa A method and device of venous needle of detachment detection by a patient during an extracorporeal blood treatment in a mach
US6582397B2 (en) 2001-06-19 2003-06-24 Portex, Inc. Needle safety device with antiremoval protection
US7147615B2 (en) 2001-06-22 2006-12-12 Baxter International Inc. Needle dislodgement detection
ITMI20011395A1 (en) 2001-06-29 2002-12-30 Gambro Dasco Spa A method and device of venous needle of detachment detection by a patient during an extracorporeal blood treatment in a mach
US6572576B2 (en) 2001-07-07 2003-06-03 Nxstage Medical, Inc. Method and apparatus for leak detection in a fluid line
US20030128125A1 (en) 2002-01-04 2003-07-10 Burbank Jeffrey H. Method and apparatus for machine error detection by combining multiple sensor inputs
US20030128126A1 (en) 2002-01-04 2003-07-10 Burbank Jeffrey H. Method and apparatus for error warning with multiple alarm levels and types
US7040142B2 (en) 2002-01-04 2006-05-09 Nxstage Medical, Inc. Method and apparatus for leak detection in blood circuits combining external fluid detection and air infiltration detection
US7122210B2 (en) 2002-01-11 2006-10-17 Baxter International Inc. Bicarbonate-based solutions for dialysis therapies
DE10201109C1 (en) 2002-01-15 2003-01-23 Fresenius Medical Care De Gmbh Detecting leak in liquid system of blood treatment system involves deriving leakage rate from change in pressure in defined intervals, driving leakage volume from leakage rate
US6796955B2 (en) 2002-02-14 2004-09-28 Chf Solutions, Inc. Method to control blood and filtrate flowing through an extracorporeal device
US6779396B2 (en) 2002-04-08 2004-08-24 Takao Tsuda Method for measuring flow within an open tube
US7022098B2 (en) 2002-04-10 2006-04-04 Baxter International Inc. Access disconnection systems and methods
US7052480B2 (en) 2002-04-10 2006-05-30 Baxter International Inc. Access disconnection systems and methods
US10155082B2 (en) 2002-04-10 2018-12-18 Baxter International Inc. Enhanced signal detection for access disconnection systems
US20040254513A1 (en) 2002-04-10 2004-12-16 Sherwin Shang Conductive polymer materials and applications thereof including monitoring and providing effective therapy
US7138088B2 (en) 2002-04-10 2006-11-21 Baxter International Inc. Access disconnection system and methods
US6947131B2 (en) 2002-05-07 2005-09-20 Chf Solutions, Inc. Blood leak detector for extracorporeal treatment system
US6801041B2 (en) 2002-05-14 2004-10-05 Abbott Laboratories Sensor having electrode for determining the rate of flow of a fluid
US6683679B2 (en) 2002-05-23 2004-01-27 Trex Enterprises Corporation Optical flow monitor
US7176344B2 (en) 2002-09-06 2007-02-13 Sca Hygiene Products Ab Sensoring absorbing article
US6962580B2 (en) 2002-09-17 2005-11-08 Transoma Medical, Inc. Vascular access port with needle detector
US7070591B2 (en) 2002-09-17 2006-07-04 Transoma Medical, Inc. Vascular access port with physiological sensor
AU2004208554B2 (en) 2003-01-28 2008-11-06 Gambro Lundia Ab An apparatus and method for monitoring a vascular access of a patient
JP4008361B2 (en) 2003-01-31 2007-11-14 理想科学工業株式会社 The power supply device
US20040185709A1 (en) 2003-03-19 2004-09-23 Williams Robert C. Electrical connector apparatus, system and method for use with medical devices
US20040186415A1 (en) 2003-03-20 2004-09-23 Burbank Jeffrey H. Blood circuit with leak-safe features
US7053781B1 (en) 2003-05-19 2006-05-30 Glen Haire Apparatus for incontinence detection and notification
JP4600280B2 (en) 2003-06-02 2010-12-15 ニプロ株式会社 Chemical supply control device and the chemical solution administration set using the device
ITMO20030165A1 (en) * 2003-06-04 2004-12-05 Gambro Lundia Ab A joint for fluid transport lines for medical use.
WO2005004950A1 (en) 2003-07-10 2005-01-20 Nikkiso Co., Ltd. Pulse count measuring method, blood pressure measuring method, and blood vessel access monitoring method, and medical device using them
US6979306B2 (en) 2003-08-13 2005-12-27 Moll Family Trust Method and device for monitoring loss of body fluid and dislodgment of medical instrument from body
US6924733B1 (en) 2003-08-21 2005-08-02 Mctier Supply Company Hose separation transmitter system and methods
US7762977B2 (en) 2003-10-08 2010-07-27 Hemosphere, Inc. Device and method for vascular access
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
WO2005046439A2 (en) 2003-11-07 2005-05-26 Nxstage Medical, Inc. Improved methods and apparatus for leak detection in blood processing systems
WO2005105200A1 (en) 2004-04-22 2005-11-10 Medtronic, Inc. Branching catheter systems with diagnostic components
US7217251B2 (en) 2004-04-22 2007-05-15 Medtronic, Inc. Pressure relief methods in a medical catheter system
US7654980B2 (en) 2004-05-14 2010-02-02 Boston Scientific Scimed, Inc. Method for percutaneously implanting a medical catheter and medical catheter implanting assembly
SE0401632D0 (en) 2004-06-24 2004-06-24 Innovation Team Ab Means and method for detecting blood leakage from wounds
JP2006055588A (en) 2004-08-20 2006-03-02 Tadashi Oshima Blood leakage sensing sensor for withdrawal of needle in dialysis
JP4260092B2 (en) 2004-10-15 2009-04-30 日機装株式会社 Hemodialysis apparatus
US7993276B2 (en) 2004-10-15 2011-08-09 Pulse Tracer, Inc. Motion cancellation of optical input signals for physiological pulse measurement
JP4290106B2 (en) 2004-10-15 2009-07-01 日機装株式会社 Blood purification apparatus
US20060130591A1 (en) 2004-12-21 2006-06-22 Perkins, Corban Enterprises Venous needle dislodgement sensor
US7530962B2 (en) 2005-06-16 2009-05-12 Edward Allan Ross Method for detecting the disconnection of an extracorporeal device using a patient's endogenous electrical voltages
US20070004996A1 (en) 2005-06-20 2007-01-04 Lovejoy David A Needle disengagement sensing mechanism
US20070010779A1 (en) 2005-07-07 2007-01-11 Utterberg David S Blood leak monitoring method and apparatus
JP4301518B2 (en) 2005-07-14 2009-07-22 日機装株式会社 Puncture of the monitoring device
US8372025B2 (en) 2005-09-22 2013-02-12 Baxter International Inc. Automation and optimization of CRRT treatment using regional citrate anticoagulation
US8152751B2 (en) 2007-02-09 2012-04-10 Baxter International Inc. Acoustic access disconnection systems and methods
US8376978B2 (en) 2007-02-09 2013-02-19 Baxter International Inc. Optical access disconnection systems and methods
US8187184B2 (en) 2007-09-21 2012-05-29 Baxter International, Inc. Access disconnect system with optical and other sensors
US8221320B2 (en) 2007-09-21 2012-07-17 Baxter International Inc. Access disconnect detection system
US8197431B2 (en) 2007-09-21 2012-06-12 Baxter International Inc. Acoustic access disconnect detection system
US7755488B2 (en) 2007-09-21 2010-07-13 Baxter International Inc. Access disconnection detection system
US7995816B2 (en) 2007-09-24 2011-08-09 Baxter International Inc. Detecting access disconnect by pattern recognition
US7874999B2 (en) 2007-09-24 2011-01-25 Baxter International, Inc. Detecting access disconnect using needle sleeve
US8083677B2 (en) 2007-09-24 2011-12-27 Baxter International Inc. Access disconnect detection using glucose
US9011334B2 (en) 2007-09-27 2015-04-21 Baxter International Inc. Access disconnect detection
US8360977B2 (en) 2007-09-27 2013-01-29 Baxter International Inc. Continuity circuits for detecting access disconnection
US7938792B2 (en) 2007-10-01 2011-05-10 Baxter International Inc. Adaptive algorithm for access disconnect detection
US8070262B2 (en) 2008-05-08 2011-12-06 Canon Kabushiki Kaisha Print element substrate, printhead, and printing apparatus
US8114043B2 (en) 2008-07-25 2012-02-14 Baxter International Inc. Electromagnetic induction access disconnect sensor
US8192388B2 (en) 2008-07-25 2012-06-05 Baxter International Inc. System and method for detecting access disconnection

Patent Citations (99)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3722504A (en) * 1969-12-23 1973-03-27 P Sawyer Method of screening substances for use in the treatment of circulatory system diseases
US3814249A (en) * 1970-05-25 1974-06-04 Eaton Medical Electronics Inc Dialysis apparatus
US3659591A (en) * 1970-08-24 1972-05-02 Doll Research Electromagnetic flowmeter
US3946731A (en) * 1971-01-20 1976-03-30 Lichtenstein Eric Stefan Apparatus for extracorporeal treatment of blood
US3731685A (en) * 1971-04-01 1973-05-08 W Eidus Moisture indicating strip for diapers and surgical dressings
US3667475A (en) * 1971-05-10 1972-06-06 Nat Equipment Research Inc Endo-tracheal tube adaptors for use in administering gases
US3809078A (en) * 1972-07-20 1974-05-07 A Mozes Detector device for detecting unintentional urination
US3810140A (en) * 1972-10-30 1974-05-07 W Finley Apparatus for the programmed treatment of bed wetting
US3882861A (en) * 1973-09-24 1975-05-13 Vital Assists Auxiliary control for a blood pump
US4026800A (en) * 1974-04-19 1977-05-31 National Medical Care, Inc. Dialysis apparatus
US3878095A (en) * 1974-05-02 1975-04-15 Advanced Medical Sciences Inc Dialysis apparatus
US4022211A (en) * 1974-08-14 1977-05-10 Kimberly-Clark Corporation Wetness indicator for absorbent pads
US3953790A (en) * 1974-10-31 1976-04-27 Baxter Laboratories, Inc. Conductivity monitoring system
US4087185A (en) * 1975-06-19 1978-05-02 Baxter Travenol Laboratories, Inc. Blood leak detector
US4181610A (en) * 1975-07-14 1980-01-01 Takeda Chemical Industries, Ltd. Blood leak detector suitable for use with artificial kidneys
US4017190A (en) * 1975-07-18 1977-04-12 Halbert Fischel Blood leak detector comparing intensities of high absorption band and low absorption band of a single beam of light passing through a sample
US4193068A (en) * 1976-03-16 1980-03-11 Ziccardi John J Hemorrhage alarms
US4085047A (en) * 1976-09-16 1978-04-18 Thompson Lester E Blood leak detector
US4192311A (en) * 1977-12-05 1980-03-11 Felfoldi James J Disposable diaper with wetness indicator
US4191950A (en) * 1978-02-09 1980-03-04 Levin Anne F Anti-bed-wetting device
US4324687A (en) * 1979-02-15 1982-04-13 Louderback Allan Lee Blood biochemistry control standard
US4327731A (en) * 1980-07-07 1982-05-04 Powell Nelson B Moisture indicator
US4450527A (en) * 1982-06-29 1984-05-22 Bomed Medical Mfg. Ltd. Noninvasive continuous cardiac output monitor
US4566990A (en) * 1982-11-05 1986-01-28 General Electric Company Synergistic effect of metal flake and metal or metal coated fiber on EMI shielding effectiveness of thermoplastics
US4936834A (en) * 1983-06-11 1990-06-26 Walter Beck Apparatus for aspirating secreted fluids from a wound
US4661093A (en) * 1983-06-11 1987-04-28 Walter Beck Method for aspirating secreted fluids from a wound
US4501583A (en) * 1983-06-15 1985-02-26 Extracorporeal, Inc. Hemodialysis access monitors
US5015958A (en) * 1983-06-30 1991-05-14 Raychem Corporation Elongate sensors comprising conductive polymers, and methods and apparatus using such sensors
US4583546A (en) * 1983-11-18 1986-04-22 Garde Patria P Blood loss monitor
US4734198A (en) * 1984-02-06 1988-03-29 Minntech Corporation Dialysis solution mixing system
US5399295A (en) * 1984-06-11 1995-03-21 The Dow Chemical Company EMI shielding composites
US5004459A (en) * 1984-07-09 1991-04-02 Peabody Alan M Continuous cyclic peritoneal dialysis system and method
US4739492A (en) * 1985-02-21 1988-04-19 Cochran Michael J Dialysis machine which verifies operating parameters
US4741343A (en) * 1985-05-06 1988-05-03 Massachusetts Institute Of Technology Method and apparatus for measuring oxygen partial pressure and temperature in living tissue
US4648869A (en) * 1985-12-04 1987-03-10 American Hospital Supply Corporation Automatic infiltration detection system and method
US4740755A (en) * 1986-05-30 1988-04-26 Cobe Laboratories, Inc. Remote conductivity sensor having transformer coupling in fluid flow path
US4931051A (en) * 1987-02-06 1990-06-05 Edge Enterprises, Inc. Wetness indicator
US4796014A (en) * 1987-03-24 1989-01-03 Chia Jack T Device for detecting urine in diapers
US4923613A (en) * 1987-05-15 1990-05-08 Hospal Industrie Method for determining a patient's blood sodium level and artificial kidney for the application thereof
US5024756A (en) * 1988-03-03 1991-06-18 Gambro Ab Dialysis system and method therefor
US4898587A (en) * 1988-11-15 1990-02-06 Mera Csaba L Intravenous line stabilizing device
US5084026A (en) * 1989-07-14 1992-01-28 Shapiro Robert A Intravenous apparatus holder
US5088990A (en) * 1989-08-30 1992-02-18 Hivale Ronald S I.V. alert system
US4981467A (en) * 1990-02-27 1991-01-01 Baxter International Inc. Apparatus and method for the detection of air in fluid delivery systems
US5310507A (en) * 1990-06-15 1994-05-10 Spectral Sciences, Inc. Method of making a conductive polymer selective species sensor
US5202261A (en) * 1990-07-19 1993-04-13 Miles Inc. Conductive sensors and their use in diagnostic assays
US5121630A (en) * 1990-12-21 1992-06-16 Calvin Noel M Material monitoring device
US5487827A (en) * 1991-04-19 1996-01-30 Althin Medical, Inc. Method and apparatus for kidney dialysis
US5486286A (en) * 1991-04-19 1996-01-23 Althin Medical, Inc. Apparatus for performing a self-test of kidney dialysis membrane
US5744027A (en) * 1991-04-19 1998-04-28 Althin Medical, Inc. Apparatus for kidney dialysis
US5416027A (en) * 1992-01-07 1995-05-16 Laboratoire Eugedia Process and apparatus for monitoring the progress of hemodialysis
US5314410A (en) * 1992-02-10 1994-05-24 Marks Ronald L Entry indicator device for arterial or intravenous needle
US5522809A (en) * 1992-02-18 1996-06-04 Paper-Pak Products, Inc. Absorbent adult fitted briefs and pads
US5291181A (en) * 1992-03-30 1994-03-01 Deponte Dominic A Wet bed alarm and temperature monitoring system
US5389093A (en) * 1992-04-01 1995-02-14 Howell; Wesley A. Wetness indicating diaper
US5197958A (en) * 1992-04-01 1993-03-30 Howell Wesley A Wetness indicating diaper
US20030016002A1 (en) * 1992-09-30 2003-01-23 Brugger James M. Differential conductivity hemodynamic monitor
US5510716A (en) * 1992-09-30 1996-04-23 Cobe Laboratories, Inc. Differential conductivity recirculation monitor
US5510717A (en) * 1992-09-30 1996-04-23 Cobe Laboratories, Inc. Differential conductivity recirculation monitor
US5900726A (en) * 1992-09-30 1999-05-04 Cobe Laboratories, Inc. Differential conductivity hemodynamic monitor
US5762805A (en) * 1993-02-12 1998-06-09 Cobe Laboratories, Inc. Technique for extracorporeal treatment of blood
US5603902A (en) * 1993-07-16 1997-02-18 Cobe Laboratories, Inc. Method and apparatus for cleaning a dialysate circuit downstream of a dialyzer
US5392032A (en) * 1993-11-23 1995-02-21 Little Acorn Ventures Apparatus for sensing wet diaper including circuit breaker
US5602342A (en) * 1994-01-06 1997-02-11 Pacesetter Ab Method and device for measuring the flow of an electrolytic fluid
US5395358A (en) * 1994-01-21 1995-03-07 Lu; Chin B. Wetting indicator for a diaper
US7011855B2 (en) * 1994-07-01 2006-03-14 Baxter International Inc. Biochemically balanced peritoneal dialysis solutions
US6210591B1 (en) * 1994-09-16 2001-04-03 Transonic Systems, Inc. Method to measure blood flow rate in hemodialysis shunts
US5891398A (en) * 1995-03-27 1999-04-06 California Institute Of Technology Sensor arrays for detecting analytes in fluids
US5760697A (en) * 1995-10-25 1998-06-02 Hartmann & Braun A.G. Multi-channel recording device
US20030093069A1 (en) * 1996-01-19 2003-05-15 Ep Technologies, Inc. Expandable-collapsible electrode structures made of electrically conductive material
US5760694A (en) * 1996-05-07 1998-06-02 Knox Security Engineering Corporation Moisture detecting devices such as for diapers and diapers having such devices
US6200250B1 (en) * 1996-05-07 2001-03-13 Knox Security Engineering Corporation Diapers with moisture detection and process and apparatus for making them
US5766212A (en) * 1996-05-16 1998-06-16 Uni-Charm Corporation Disposable diaper
US5885264A (en) * 1996-07-02 1999-03-23 Uni-Charm Corporation Disposable training pants
US6217539B1 (en) * 1996-11-30 2001-04-17 Fresenius Medical Care Deutschland Gmbh Method of in-vivo determination of hemodialysis parameters and a device for carrying out the method
US6187199B1 (en) * 1997-01-24 2001-02-13 Fresenius Medical Care Deutschland Gmbh Process and device for determining hemodialysis parameters
US6208880B1 (en) * 1997-02-27 2001-03-27 Terumo Cardiovascular Systems Corporation Blood parameter measurement device
US6038914A (en) * 1997-02-27 2000-03-21 Bristol-Myers Squibb Company Leak detection system for liquid processing device
US5903222A (en) * 1997-04-03 1999-05-11 Zaggie, Inc. Wet garment detector
US5862804A (en) * 1997-07-08 1999-01-26 Andco Tek, Inc. Leak point wetness sensor for urological investigation
US5868723A (en) * 1997-07-15 1999-02-09 Al-Sabah; Sabah Naser Moisture sensing and audio indicating apparatus for garments and associated methods
US20020042125A1 (en) * 1997-08-13 2002-04-11 Cepheid Method for separating analyte from a sample
US6169225B1 (en) * 1997-09-29 2001-01-02 Uni-Charm Corporation Disposable training pants having a suspended crotch covering sheet
US5904671A (en) * 1997-10-03 1999-05-18 Navot; Nir Tampon wetness detection system
US5908411A (en) * 1997-11-20 1999-06-01 Nippon Koudoshi Kougyou Co., Ltd. Moisture annunciator
US5900817A (en) * 1998-02-17 1999-05-04 Olmassakian; Vahe Child monitoring system
US6015342A (en) * 1998-06-03 2000-01-18 Carrier Corporation Louver apparatus for air conditioning unit
US6063042A (en) * 1998-09-28 2000-05-16 Navot; Nir Method for diagnosis of menorrhagia menstrual cycle disorders and their causes
US6171289B1 (en) * 1998-11-06 2001-01-09 Plasto Sa Safety device for colostomy having a wetness detector and alarm
US6387329B1 (en) * 1998-11-16 2002-05-14 California Institute Of Technology Use of an array of polymeric sensors of varying thickness for detecting analytes in fluids
US20020055167A1 (en) * 1999-06-25 2002-05-09 Cepheid Device incorporating a microfluidic chip for separating analyte from a sample
US20030036719A1 (en) * 1999-12-28 2003-02-20 Sara Giacomelli Method and device for monitoring the access to the cardiovascular system of a patient
US20020036375A1 (en) * 2000-09-19 2002-03-28 Yasuhiro Matsuda Paper feeding apparatus
US6372848B1 (en) * 2000-10-10 2002-04-16 Baxter International Inc. Blend of ethylene and α-olefin copolymers obtained using a metallocene catalyst for fabricating medical films and tubings
US20030075498A1 (en) * 2001-06-01 2003-04-24 Watkins Randolph H. Hemodialyzer headers
US20030083901A1 (en) * 2001-06-22 2003-05-01 Bosch Juan P. Process for providing dialysis and other treatments
US20030094369A1 (en) * 2001-10-01 2003-05-22 Brigham Young University Method of simultaneously concentrating and separating analytes
US20050010157A1 (en) * 2003-06-04 2005-01-13 Gambro Lundia Ab. Joint for fluid transport lines for medical use
US7053059B2 (en) * 2003-07-25 2006-05-30 Baxter International Inc. Dialysis solutions with reduced levels of glucose degradation products

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20160356667A1 (en) * 2008-06-26 2016-12-08 Gambro Lundia Ab Methods and devices for monitoring the integrity of a fluid connection
US20130281985A1 (en) * 2010-12-15 2013-10-24 Valeria Querol Garcia Three-Lobe Drainage Hose
US9724498B2 (en) * 2010-12-15 2017-08-08 Valeria Querol Garcia Three-lobe drainage hose

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