Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
  • A61M1/3424—Substitution fluid path
  • A61M1/3437—Substitution fluid path downstream of the filter, e.g. post-dilution with filtrate
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1601—Control or regulation
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1601—Control or regulation
  • A61M1/1603—Regulation parameters
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1601—Control or regulation
  • A61M1/1613—Profiling or modelling of patient or predicted treatment evolution or outcome
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1601—Control or regulation
  • A61M1/1617—Control or regulation using measurements made during a temporary variation of a characteristic of the fresh dialysis fluid
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1621—Constructional aspects thereof
  • A61M1/1635—Constructional aspects thereof with volume chamber balancing devices between used and fresh dialysis fluid
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3403—Regulation parameters
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3403—Regulation parameters
  • A61M1/341—Regulation parameters by measuring the filtrate rate or volume
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3413—Diafiltration
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
  • A61M1/3424—Substitution fluid path
  • A61M1/3431—Substitution fluid path upstream of the filter
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
  • A61M1/3424—Substitution fluid path
  • A61M1/3431—Substitution fluid path upstream of the filter
  • A61M1/3434—Substitution fluid path upstream of the filter with pre-dilution and post-dilution
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
  • A61M1/3621—Extra-corporeal blood circuits
  • A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
  • A61M1/3633—Blood component filters, e.g. leukocyte filters
  • A61M1/3635—Constructional details
• • B—PERFORMING OPERATIONS; TRANSPORTING
  • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
  • B01D—SEPARATION
  • B01D61/00—Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
  • B01D61/24—Dialysis ; Membrane extraction
  • B01D61/243—Dialysis
• • B—PERFORMING OPERATIONS; TRANSPORTING
  • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
  • B01D—SEPARATION
  • B01D61/00—Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
  • B01D61/24—Dialysis ; Membrane extraction
  • B01D61/28—Apparatus therefor
• • B—PERFORMING OPERATIONS; TRANSPORTING
  • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
  • B01D—SEPARATION
  • B01D61/00—Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
  • B01D61/24—Dialysis ; Membrane extraction
  • B01D61/32—Controlling or regulating
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/33—Controlling, regulating or measuring
  • A61M2205/3327—Measuring
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M2205/00—General characteristics of the apparatus
  • A61M2205/33—Controlling, regulating or measuring
  • A61M2205/3331—Pressure; Flow
  • A61M2205/3334—Measuring or controlling the flow rate
• • B—PERFORMING OPERATIONS; TRANSPORTING
  • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
  • B01D—SEPARATION
  • B01D2311/00—Details relating to membrane separation process operations and control
  • B01D2311/14—Pressure control
• • B—PERFORMING OPERATIONS; TRANSPORTING
  • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
  • B01D—SEPARATION
  • B01D2311/00—Details relating to membrane separation process operations and control
  • B01D2311/16—Flow or flux control

Definitions

• a method of regulating the delivery of substituate in an extracorporeal blood treatment and extracorporeal blood treatment device comprising means for regulating the supply of substituate
• the invention relates to a method for regulating the supply of Substituat in an extracorporeal blood treatment with an extracorporeal blood treatment device, a through a semipermeable membrane in a blood chamber and a
• Dialysing fluid chamber divided dialyzer and means for supplying substituate are divided dialyzer and means for supplying substituate.
• the invention relates to a device for extracorporeal blood treatment with a device for regulating the supply of substituate.
• HDF Hemodiafiltration
• the amount of fluid withdrawn from the hemophiliactration (HF) or hemodiafiltration (HDF) via the semi-permeable membrane of the dialyzer is returned to the patient as a substitute during blood treatment, which is either provided ready for use or during blood treatment
• Dialysis fluid is obtained.
• the substituate is the extracorporeal
• the supply of substituate upstream of the dialyzer is used as pre-dilution and downstream of the dialyzer as Postdilution called.
• the substituate rate is that amount of substituate which is supplied to the blood flowing in the extracorporeal blood circulation in a certain period of time.
• Blood treatment devices Balancing systems Use. The balancing of fresh and used dialysis fluid ensures that no liquid or only a certain amount of liquid is supplied or withdrawn from the patient.
• the ultrafiltration rate at which fluid is withdrawn from the patient is dependent upon the transmembrane pressure TMP, which is defined as the pressure difference between the mean, blood, and the average dialysate pressure on the dialyzer.
• TMP transmembrane pressure
• Methods and apparatus for determining transmembrane pressure are well known.
• EP 0 212 127 A1 and WO 2009/080258 A1 describe a device for determining the transmembrane pressure.
• the longitudinal flow resistance along the hollow fibers of the semipermeable membrane of the dialyzer on the blood side is of importance for extracorporeal blood treatment
• the invention has for its object to provide a method with which the
• the method according to the invention and the device according to the invention are based on the fact that the regulation of the supply of substituate in the case of extracorporeal blood treatment is effected as a function of the theological load on the dialyzer. It should be noted that the substituate rate is not an independent quantity that is only available in
• the substituate rate is related to the ultrafiltration rate.
• the method according to the invention and the device according to the invention are therefore based on starting from a predetermined substituate rate, with which the patient is supplied with substituate taking into account a specific ultrafiltration rate, wherein the predetermined substituate rate is increased or decreased in dependence on the theological load of the dialyzer.
• the theological burden of the dialyzer is determined to control the supply of substituate during extracorporeal blood treatment and the substituate rate
• the rheological burden of the dialyzer is preferably determined based on transmembrane pressure or a variable correlated with transmembrane pressure and flow resistance or a variable correlating with flow resistance, with transmembrane pressure or magnitude correlating with transmembrane pressure and flow resistance correlating with flow resistance Size during extracorporeal blood treatment. It is irrelevant how the transmembrane pressure and the flow resistance are measured. The only decisive factor is that the transmembrane pressure and the
• Flow resistance or derived from the transmembrane pressure and flow resistance variables for further evaluation are available to the supply of Substituate depending on transmembrane pressure and flow resistance to be able to regulate.
• Transmembrane pressure or correlate with the Transmembran horrinsky size determining a first evaluation size and to assess the flow resistance or the correlating with the flow resistance size to determine a second evaluation variable.
• Both determined evaluation variables then form a valuation pair that is characteristic for the rheological load of the dialyzer.
• transmembrane pressure and flow resistance are evaluated within a 0-100% rating range. The evaluation pair completely describes the rheology at the dialyzer.
• the rating of the dialyzer within the scoring frame is input to a 2-dimensional matrix, which assigns a value to each scoring pair (priority pair) that is required
• Each pair of evaluation of a plurality of evaluation pairs characterizing the rheological load of the dialyzer is assigned a specific value for the amount by which the substituate rate is increased or decreased from a predetermined value. This assignment of the evaluation pair and the amount of the change in the substituate rate can be stored in a memory. This stands for the
• Dialysers are generated and measured downstream of the dialyzer, and that the pressure signal measured downstream of the dialyzer is spectrally decomposed into a fundamental and at least one harmonic.
• the flow resistance or the with the Flow resistance correlating magnitude is then determined based on the ratio of the fundamental and the at least one harmonic.
• the measured pressure signal is decomposed into a fundamental and two harmonics.
• the method according to the invention and the device according to the invention can make use of the sensors which are generally present in an extracorporeal blood treatment device anyway.
• the evaluation of the data can be done in the central control and processing unit, which is already present in the extracorporeal blood treatment device. Therefore, the device according to the invention and the
• Fig. 2 is a matrix, each for the rheological load of the dialyzer
• characteristic pair of valuation assigns a value corresponding to the required change in substituate rate.
• Fig. 1 shows the essential components of the invention
• a blood treatment device which is a hemodialysis device comprising a dialyzer (filter) 1 separated by a semipermeable membrane 2 into a blood chamber 3 and a dialysis fluid chamber 4.
• the inlet of the Blood chamber 3 is connected to one end of a blood supply line 5, into which a blood pump 6, in particular a roller pump generating pressure pulses, is connected, while the outlet of the blood chamber is connected to one end of a blood discharge line 7 into which a drip chamber 8 is connected.
• Blood supply and discharge line 5, 7 form with the blood chamber 3 of the dialyzer the extracorporeal blood circulation 9 of the
• the blood supply and discharge line 5, 7 are hose lines of a tubing set inserted in the hemodiafiltration device (disposable).
• the dialysis fluid system 10 of the hemodiafiltration device comprises a device 11 for providing dialysis fluid, which is connected via the first section of a dialysis fluid supply line 12 to the inlet of the first balance chamber half 35a of a balancing device 35.
• the second section of the dialysis fluid supply line 12 is connected via the first section of a dialysis fluid supply line 12 to the inlet of the first balance chamber half 35a of a balancing device 35.
• Dialysis fluid supply line 12 connects the outlet of the first balance chamber half 35a to the inlet of the dialysis fluid chamber 4. The outlet of the
• Dialysis fluid chamber 4 is over the first section of a
• Dialysing fluid discharge line 13 connected to the inlet of the second balancing chamber half 35b.
• a dialysis fluid pump 14 is connected in the first section of the Dialysierwhikeitsabschreib Arthur 13 .
• the outlet of the second balancing chamber half 35b is connected to an outlet 15 via the second section of the dialysis fluid outlet line 13.
• Upstream of the dialysis fluid pump 14 branches off from the dialysis fluid discharge line 13 from an ultrafiltrate 16, which also leads to the outlet 15.
• an ultrafiltration pump 17 is connected.
• the balancing device 35 consists of commercially available devices from two parallel balancing chambers, which are operated anti-cyclically. For reasons of simplification, only one balance chamber is shown here.
• the blood chamber 3 of the patient's blood and the dialyzer fluid chamber 4 of the dialyzer are removed from the dialysis fluid
• the balancing device 35 ensures that only as much dialysis fluid can flow through the dialysis fluid supply line as dialysis fluid can flow away via the dialysis fluid discharge line.
• the ultrafiltration pump 17 For example, a predetermined amount of fluid (ultrafiltrate) can be withdrawn from the patient at a predetermined ultrafiltration rate.
• the ultrafiltration pump 17 is thus part of a device for withdrawing liquid from the extracorporeal
• Ultrafiltration device 18 is designated.
• Substitution fluid can be supplied to the blood flowing through the arterial branch 20 (pre-dilution) and / or the venous branch 21 (post-dilution) of the extracorporeal blood circulation 9.
• the substitution device 19 has a device 37 for providing substituate, of which a first substituate line 36, into which a first substituate pump 22 is connected, to the section of FIG.
• Blood supply line 5 between blood pump 6 and blood chamber 3 leads. A second
• Substituate line 23 into which a second substituate pump 24 is connected leads from the means 37 for providing substituate to the drip chamber 8. If the
• the hemodiafiltration device has a central control and
• Arithmetic unit 25 which is connected via control lines 6 ', 14', 17 ', 22', 24 'to the blood pump 6, the dialysis fluid pump 14, the ultrafiltration pump 17 and the first and second substituate pump 22, 24.
• the extracorporeal blood treatment device has a device 26 for regulating the supply of substituate, which is shown in dashed lines in FIG. 1.
• the means for controlling the supply of substituate is shown in Fig. 1 as separate
• the device 26 for regulating the supply of substituate is connected to the central control and arithmetic unit 25 via a data line 26 ', so that the control device can exchange data with the control unit, in particular the Substituatpumpen 22, 24 for adjusting the Substituatrate Q can control accordingly.
• Substituent supply control means 26 comprises means 27 for determining the theological burden of the dialyzer and means 28 for controlling the substitution rate.
• the means 27 for determining the theological load of the dialyzer in turn have means 29 for determining the transmembrane pressure at the dialyzer or a correlated with the Transmembran horrs size and means 30 for determining the flow resistance of the dialyzer or a correlating with the flow resistance size.
• the flow resistance of the dialyzer means the longitudinal flow resistance along the hollow fiber of the semipermeable membrane 2 of the dialyzer 1 on the blood side.
• the means 29 for determining the transmembrane pressure may be designed differently.
• the measuring device described in EP 0 212 127 A1 can be used.
• the means 27 for determining the transmembrane pressure comprise one in the dialysis fluid supply line 12 upstream of
• Dialysing fluid chamber 4 of the dialyzer 1 arranged first pressure sensor 31, one in the dialysis fluid discharge line 16 downstream of the
• Dialysing fluid chamber of the dialyzer arranged second pressure sensor 32 and disposed in the blood return line 21 downstream of the blood chamber 3 of the dialyzer 1 third pressure sensor 33.
• the pressure sensors 31, 32, 33 are over
• the means 29 for determining the transmembrane pressure TMP have a suitable computing unit which calculates the transmembrane pressure according to the following equation:
• TMP P, - ⁇ - ⁇
• the determined value for the transmembrane pressure TMP is evaluated as follows.
• a first evaluation parameter HEMO is calculated according to the following equation from the measured value for the transmembrane pressure TMP and a predetermined lower limit value for the transmembrane pressure TMPLIMIT_LOWER and a predetermined upper limit value for the transmembrane pressure TMPLIMIT_UPPER and a predetermined value range for the transmembrane pressure TMPLIMIT_RAN G E Priority calculated.
• the parameters TMPLIMIT_LOWER, TMPLI WITH _UPPER and TMPLI IT RANGE are determined empirically.
• HEMO_Priority ((TMP - TMP L IMIT_LOWER) / TMP L1 WITH _ RA N G E) * 100% where TMPLIMIT_RANGE - TMPLMITJJPPER - TMPLIMIT_LOWER
• the flow resistance of the dialyzer is determined to determine the rheological load of the dialyzer 1.
• the flow resistance determining means 30 has means for measuring pressure pulses which propagate in the longitudinal direction across the hollow fibers of the semipermeable membrane of the dialyzer on the blood side.
• the pressure pulses are generated by the blood pump 6, which is an occlusive
• Hose pump in particular roller pump is.
• roller pump is.
• the pressure sensor 33 arranged downstream of the blood chamber 3 in the Blutriick gleich Gustav 21 for measuring the pressure pulses generated by the blood pump 6 is used. Therefore, a second data line 33 "leads from the pressure sensor 33 to the means 30 for determining the flow resistance Flow resistance, the measured pressure signal with the pressure sensor 33 spectrally in a fundamental vibration G 0 and the first and second harmonics Hj and H 2 decomposed, since the attenuation of the pressure pulses along the hollow fibers in the ratio of the amplitudes of the spectral components of the first and second harmonics H ⁇ H 2 related to the fundamental vibration Go.
• the theoretical context is in the WO
• the flow resistance is also evaluated as follows. According to the following equation, from the fundamental vibration G 0 and the first and second harmonics Hi and H 2 and the empirically determined parameters K 1 2 , M lj2 and ⁇ is calculated according to the following equation
• the first and second evaluation variables form a valuation pair
• the frequency of the fundamental oscillation of the pressure pulses results from the control of the blood pump 6.
• the frequencies of the first and second harmonics of the fundamental are known.
• the decomposition of the continuous pressure signal into its spectral components preferably takes place with a Fourier transformation, particularly preferably by digitizing the measured values of the pressure sensor 33 with a more discrete one
• Transmembrane pressure as well as the flow resistance is determined, the measurement of Transmembran horrs with only two or three pressure sensors instead of the known measurement with four pressure sensors is sufficient, although the two- and three-point measurement of transmembrane pressure in practice have not always proven to be reliable, since there may be a discontinuous behavior in the range of particularly high Transmembrandschreibe in the two- and three-point measurement.
• the transmembrane pressure and the flow resistance are evaluated such that the evaluation values scale within a rating range of 0 to 100%.
• Dialyzer can be fully described as a point in a two-dimensional coordinate system.
• the regulation of the substituate rate is based on keeping the rheological stress within a target area of the matrix.
• the regulation is independent of whether there is a post or pre-dilution.
• Fig. 2 shows the two-dimensional matrix which assigns a value to each evaluation pair (priority pair) which corresponds to the required change in the substituate rate. Consequently, each value pair stored in the matrix is assigned a specific value for the amount of change in the given substituate rate.
• a reference line value range
• This reference line is a line that is mathematically composed of the connection of a line running linearly to the priorities and a circle extending around the priority pair (0,0) composed. If the priority pair lies on the target line, the substituate rate remains unchanged.
• the reference line (value range) is marked in FIG. 1 as a non-hatched area.
• the amount of change of the substituate rate is shown in Fig. 1 by the density of the hatching.
• the scale on the right in FIG. 1 assigns the hatched areas in the coordinate system on the left to corresponding changes in the substituate rate.
• the rule objective here is the non-hatched area (0%), which is equivalent to unchanged substitution.
• the required substituate change ⁇ is determined from the matrix.
• the newly set substituate Qsub, new is calculated as follows:
• the central control and computing unit 25 prescribes a specific substituate rate.
• This Substituatrate is then dimensioned such that the extracorporeal blood circulation less substituate is supplied, as over the membrane 2 of the dialyzer 1 with the ultrafiltration 18 liquid is withdrawn.
• This predetermined substituate rate is increased or decreased by the means for regulating the supply of substituate according to the method described above.
• the extracorporeal blood treatment is performed under optimal conditions for the dialyzer.
• substituent control provides not only a change in substituate rate, but also a distribution of the supply of substituate upstream and downstream of the dialyzer (pre-dilution and post-dilution).
• the total amount of dilution is changed to post- and predilution as specified by the matrix.
• the change in the total dilution quantity is determined by the distance of the value pair in the dialyzer that is characteristic for the theological load
• Substituant supply control means 26 then adjusts the flow rates of substituate pumps 22 and 30, respectively, together with central control and computation unit 25 in accordance with the determined distance and angle.

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• 2010
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