DK156413B - BLOOD PUMP CONTROL UNIT - Google Patents
BLOOD PUMP CONTROL UNIT Download PDFInfo
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- DK156413B DK156413B DK485374AA DK485374A DK156413B DK 156413 B DK156413 B DK 156413B DK 485374A A DK485374A A DK 485374AA DK 485374 A DK485374 A DK 485374A DK 156413 B DK156413 B DK 156413B
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- 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
- A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
-
- 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
-
- 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
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3607—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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
- A61M60/109—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems
- A61M60/113—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems in other functional devices, e.g. dialysers or heart-lung machines
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- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
- A61M60/36—Medical purposes thereof other than the enhancement of the cardiac output for specific blood treatment; for specific therapy
- A61M60/37—Haemodialysis, haemofiltration or diafiltration
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- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/515—Regulation using real-time patient data
- A61M60/531—Regulation using real-time patient data using blood pressure data, e.g. from blood pressure sensors
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- 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
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- 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
-
- 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
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/424—Details relating to driving for positive displacement blood pumps
- A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
- A61M60/43—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic using vacuum at the blood pump, e.g. to accelerate filling
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/12—Pressure infusion
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- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Hematology (AREA)
- Animal Behavior & Ethology (AREA)
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Description
DK 156413 BDK 156413 B
Derme opfindelse angâr en blodpumpereguleringsenhed af den i krav i's indledning angivne art.This invention relates to a blood pump control unit of the kind set forth in claim 1.
Mange nyresygdomme griber sâledes ind i nyrefunktionen, at nyren holder op med at fjerne affaldsprodukter og vandoverskud fra blodet.Many kidney diseases interfere with kidney function so that the kidney stops removing waste products and excess water from the blood.
5 Nâr nyren er sâ svækket, at en stor mængde affaldsprodukter og vand ikke fjernes fra blodet, kan patientens liv ikke bevares, medmindre der tilvejebringes en mâde til kunstig udforelse af den svækkede nyres funktioner gennem ekstrakorporal hæmodialyse.5 When the kidney is so weakened that a large amount of waste products and water are not removed from the blood, the patient's life cannot be preserved unless an artificial means of performing the impaired kidney functions through extracorporeal hemodialysis is provided.
De fleste hæmodialyseapparater kræver anvendelse af en blodpumpe til 10 frembringelse af ekstra tryk i det udledte blod, sâ at det kan ledes gennem hæmodialyseeriheden. Et hovedproblem i forbindelse med blod-pumper og det tilhorende kontrolapparat er et sâdant apparats mang-lende evne til at tilvejebringe en minimal dialysetid og samtidig forhindre, at tilforselen til pumpen bliver for ringe, og at der som 15 folge heraf sker en sammenklapning af blodtilforselsledningerne.Most hemodialysis devices require the use of a blood pump to generate extra pressure in the discharged blood so that it can be passed through the hemodialysis series. A major problem in connection with blood pumps and the associated control apparatus is the failure of such an apparatus to provide a minimal dialysis time and at the same time prevent the supply to the pump from being too low, and as a consequence, the blood supply lines are collapsed .
Blodet ber udledes fra patienten med stor hastighed for at reducere dialysetiden. Nâr blodforsyningen fra patienten er utilstrækkelig til at forsyne blodpumpen, klapper blodledningerne og endog patientens blodkar imidlertid sammen, hvilket effektivt afbryder dialysen, 20 indtil en tilstrækkelig blodstrom er genoprettet. Sammenklapning af blodledningerne som résultat af utilstrækkelig blodforsyning fil en kontinuerligt arbejdende blodpumpe vil i det folgende blive kaldet "pumpestarvation". For at undgà tidsforbrugende og undertiden farlig pumpestarvation har det været nodvendigt at indstille pumpehastig-25 heden et godt stykke under optimal hastighed og pâ et niveau, der giver en bred sikkerhedsmargin til undgâelse af pumpestarvation. Selv med denne forholdsregel er det imidlertid almindeligt, at patientens blodstromshastighed varierer betydeligt under dialyseforlobet.The blood must be discharged from the patient at high speed to reduce dialysis time. When the blood supply from the patient is insufficient to supply the blood pump, the blood lines and even the patient's blood vessels collapse, effectively interrupting the dialysis until a sufficient blood flow is restored. Collapsing of the blood lines as a result of insufficient blood supply to a continuously working blood pump will be hereinafter referred to as "pump starvation". In order to avoid time-consuming and sometimes dangerous pumping, it has been necessary to set the pump speed well below optimum speed and at a level that provides a wide margin of safety to avoid pumping. However, even with this precaution, it is common for the patient's blood flow rate to vary significantly during the course of dialysis.
Folgelig mà den tj enestegorende læge vælge mellem (a) at sænke 30 pumpehastigheden for at tilpasse den til den lavest mulige blodstromshastighed som en sikkerhedsmargin og derved forlænge dialysetiden betydeligt eller (b) risikere sammenklapning af blodledningerne og for tidlig afbrydelse af dialysen pâ grund af pumpestarvation i tilfælde af et fald i patientens blodstromshastighed.Accordingly, the general practitioner must choose between (a) lowering the pump speed to adjust it to the lowest possible blood flow rate as a safety margin, thereby significantly prolonging the dialysis time, or (b) risking collapse of the blood lines and premature discontinuation of the dialysis due to pump starvation. in the event of a decrease in the patient's blood flow rate.
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22
Man har forsegt at fremstille en pumpe, der er i stand til at kompen-sere for ændringer i mængden af disponibelt blod, medens patienten dialysebehandles. Man har forsegt at anvende trinvis regulerende apparater, der kun varierer volumenet af det pumpede blod i en sérié 5 af særskilte trin og ikke muligger kontinuerligt variable forandrin-ger af volumenet af det pumpede blod. En sâdan type pumpe og kontrol-apparat kræver en ændring af tryktærskelværdien, fer nogen modsva-rende handling foretages.Attempts have been made to produce a pump capable of compensating for changes in the amount of blood available while the patient is undergoing dialysis. It has been contemplated to use stepwise regulators which only vary the volume of the pumped blood in a series of separate steps and do not allow continuously variable changes in the volume of the pumped blood. Such a type of pump and control apparatus requires a change of the pressure threshold if any corresponding action is taken.
En anden kontrolapparattype anvender specielt konstruerede pumper, 10 der er i stand til mekanisk at âge den kraft, der bringes til at pà-virke et sammentrykkeligt réservoir, for derved at ege trykket for det blod, der leveres fra reservoiret.Another type of controller uses specially designed pumps 10 capable of mechanically increasing the force caused to actuate a compressible reservoir, thereby increasing the pressure of the blood supplied from the reservoir.
En hovedmangel, der er iagttaget ved forseg pâ at lese problemet med pumpestarvationreguleringen er, at lesningen medferer udskiftning af 15 aile eksisterende pumpekontrolapparater og/eller blodpumper. Fer den foreliggende opfindelse blev gjort, var det ikke muligt kontinuerligt at variere hastigheden af en fortlebende blodstremspumpe i forhold til den disponible blodmængde under bibeholdelse af den eksisterende konventionelle blodpumpe og det eksisterende konventionelle kontrol-20 apparat.A major defect that has been observed in attempting to read the problem of pump stagnation regulation is that the reading involves the replacement of 15 all existing pump control devices and / or blood pumps. Before the present invention was made, it was not possible to continuously vary the rate of a continuous blood pump pump relative to the amount of blood available while retaining the existing conventional blood pump and the existing conventional control apparatus.
Formâlet med opfindelsen er at tilvejebringe en blodpumperegule-ringserihed, der maksimerer hæmodialysehastigheden og forhindrer pumpestarvation, og som kan benyttes i kombination med eksisterende konventionelle blodpumper og kontrolmekanismer.The object of the invention is to provide a blood pump control unit which maximizes the rate of hemodialysis and prevents pump stasis, and which can be used in combination with existing conventional blood pumps and control mechanisms.
25 Dette opnâs ved, at man indretter blodpumpereguleringseriheden som angivet i den kendetegnende del af krav 1.This is achieved by arranging the blood pump control series as set forth in the characterizing portion of claim 1.
Effektreguleringsorganerne kan omfatte transducerorganer, der er forbundet med en blodledning til at lede blod fra en patient til blodpumpen, og som er indrettet til at frembringe et elektrisk signal 30 rep ræs ente rende blodstremmens hastighed pâ pumpens tilgangsside, sammenligningsorganer til at sammenligne transducersignalet med et foretableret referencesignal og frembringe et proportionalt udgangs-signal, og afbryderorganer indrettet til at reagere sâledes pâ sam- 3The power regulating means may comprise transducer means connected to a blood line to direct blood from a patient to the blood pump and adapted to produce an electrical signal 30 representing the blood stream velocity on the pump side of the pump, comparison means for comparing the transducer signal with an established one. reference signal and produce a proportional output signal, and switching means adapted to respond to the same
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menligningsorganernes udgangssignal, at der frembringes en periodisk impulsfalge, hvor varigheden af hver impuls er proportional med udgangssignalet fra sammenligningsorganerne, medens blodpumpens hastighed er en direkte funktion af impulsvarigheden.the output signal of the comparator means that a periodic pulse error is produced, the duration of each pulse being proportional to the output signal of the comparator means, while the blood pump speed is a direct function of the pulse duration.
5 Transducerorganerne kan omfatte middelværdibestemmelsesorganer til middelværdibestemmelse af de systoliske og diastoliske blodtryk.The transducer means may comprise means for determining the values of systolic and diastolic blood pressure.
Blodpumpereguleringseriheden ifalge opfindelsen kan yderligere omfatte detekteringsorganer til at detektere det négative blodtryk pâ pumpens tilgangsside, og afbryderorganerne kan omfatte organer til (a) at 10 frembringe en impuls med en middelvarighed, nâr det proportionale udgangssignal er pâ et begyndelsesreferenceniveau, sont repræsenterer et forudbestemt negativt blodtryk, (b) at formindske impulsvarigheden, nâr det proportionale udgangssignal angiver en reduceret blodstrom fra patienten repræsenteret ved et foreget negativt blod-15 tryk, og til (c) at âge impulsvarigheden, nâr det proportionale udgangssignal angiver en foreget blodstram fra patienten repræsenteret ved et formindsket negativt blodtryk. Afbryderorganerne kan omfatte organer til at slutte kredslabet mellem pumpen og dens tilsvarende stramkilde i den tid, en impuls varer, 20 De ovenfor beskrevne sammenligningsorganer kan omfatte en operati-onsforstærker indskudt mellem transducerorganerne og afbryderorganerne .The blood pump control rate according to the invention may further comprise detecting means for detecting negative blood pressure on the pump side, and the switching means may comprise means for (a) generating a pulse at a medium duration when the proportional output signal is at an initial reference level at the initial reference level, , (b) decreasing the pulse duration when the proportional output signal indicates a reduced blood flow from the patient represented by an increased negative blood pressure, and (c) increasing the pulse duration when the proportional output signal indicates an increased blood flow from the patient represented by a decreased negative blood pressure. The switching means may comprise means for closing the circuit between the pump and its corresponding power source during the duration of an impulse. The comparison means described above may comprise an operational amplifier interposed between the transducer means and the switching means.
Blodpumpereguleringsapparatet kan yderligere omfatte standseorganer til at standse driften af blodpumpen, nâr blodstrammen er reduceret 25 til under et forudbestemt niveau.The blood pump control apparatus may further comprise stop means for stopping the operation of the blood pump when the blood stream is reduced to below a predetermined level.
Opfindelsen vil nu blive beskrevet under henvisning til tegningen, der viser en udfarelsesform for apparatet ifalge opfindelsen, og pâ hvilken fig. 1 er et blokdiagram, der viser en for ajeblikket foretrukken 30 udfarelsesform for opfindelsen, fig. 2 illustrerer en balgeform, der er registreret ved punkt A i fig. 1, og som specielt viser det signal, der fremkommer, nâr blod-strammen fra patienten er blevet foraget under dialysens forlab, ogThe invention will now be described with reference to the drawing, which shows an embodiment of the apparatus according to the invention, and in which fig. 1 is a block diagram showing a presently preferred embodiment of the invention; FIG. 2 illustrates a bellows shape recorded at point A of FIG. 1, and showing in particular the signal that appears when the blood stream from the patient has been dislocated during the course of the dialysis, and
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4 fig. 3 illustrerer en bolgeform, der er registreret ved punkt A i fig. 1, og som specielt viser det signal, der fremkommer, nâr blod-Stremmen fra patienten er blevet formindsket under dialysens forlob.4 FIG. 3 illustrates a waveform registered at point A of FIG. 1, and specifically showing the signal that appears when the blood stream from the patient has been decreased during the course of dialysis.
Fig. 1 viser et hjælpereguleringsapparat til en blodpumpe, hvilket 5 apparat som helhed er betegnet med 20 og er illustreret med punkte-rede linier. Et af de væsentligste træk ved apparatet ifolge opfin-delsen er, at det kan anvendes sammen med eksisterende blodpumper og tilhorende reguleringsapparater. For nemheds skyld er pumpens kraft-forsyning 35, et pumpereguleringsapparat 39 og en blodpumpe 37, der 10 ikke udgor nogen del af opfindelsen, kun vist skematisk i fig. 1.FIG. 1 shows a blood pump auxiliary control apparatus, which apparatus as a whole is designated by 20 and is illustrated by dotted lines. One of the most important features of the apparatus according to the invention is that it can be used with existing blood pumps and associated regulators. For convenience, the pump power supply 35, a pump control apparatus 39, and a blood pump 37, which forms no part of the invention, are only shown diagrammatically in FIG. First
Blodstrommen drives af blodpumpen 37 uafbrudt fra patienten til dialyseapparatet. Sâledes vil der i de blodledninger, der régnét i stromnings re tningen ligger for pumpen, eksistere et negativt tryk.The blood stream is driven by the blood pump 37 continuously from the patient to the dialysis apparatus. Thus, a negative pressure will exist in the blood lines that are in the flow direction for the pump.
Hvis blodudstromningen fra patienten skulle blive begrænset gennem 15 forsnævring, blokering, for lavt blodtryk eller en hvilken som helst anden af de mange forskellige almindelige ârsager, vil det négative tryk foran pumpen vokse proportionalt dermed. Omvendt vil det négative tryk aftage, nâr der fores mere blod til pumpen.If the blood flow from the patient were to be restricted through constriction, blockage, hypertension or any of the many common causes, the negative pressure in front of the pump would increase proportionally. Conversely, negative pressure will decrease as more blood is fed to the pump.
I overensstemmelse med en for ojeblikket foretrukken udforelsesform 20 for opfindelsen foretager en konventionel tryktransducer 22 en direk-te omdannelse af det négative tryk i en blodledning 24 til elektrisk spænding. Blodledningen 24 forbinder tryktransduceren med en ledning (ikke vist), som transporteur blod fra en patients blodkar til blodpumpen 37. Tryktransducerens elektriske karakteristik kan 25 karakteriseres som enten en variabel modstand eller en variabel spæn-dingskilde. Uanset hvilken type transducer, der anvendes, eller uanset hvilken elektrisk karakteristik, der bruges, vil den elektriske storrelse variere i takt med blodstrommen, der mâles som det négative blodtryk i ledningen 24. Det négative tryk kan fortrinsvis 30 aflæses pâ en almindelig udlæseenhed 23.In accordance with a presently preferred embodiment 20 of the invention, a conventional pressure transducer 22 performs a direct conversion of the negative pressure into a blood line 24 for electrical voltage. The blood line 24 connects the pressure transducer to a line (not shown) which transports blood from a patient's blood vessel to the blood pump 37. The electrical characteristics of the pressure transducer 25 can be characterized as either a variable resistor or a variable voltage source. Regardless of the type of transducer used or whatever electrical characteristic used, the electrical magnitude will vary with the blood flow measured as the negative blood pressure in line 24. Preferably, the negative pressure may be read on a common readout unit 23.
Tryktransducerens elektriske udgangssignal ledes til et middelværdi-bestemmende kredslob 28, der kan være en hvilken som helst af et stort antal kendte særskilte eller integrerede kredslob, hvoraf det mest simplificerede blot kan være en kondensator forbundet paralleltThe electrical output of the pressure transducer is fed to a mean-determining circuit 28 which may be any of a large number of known separate or integrated circuits, the simplest of which may simply be a capacitor connected in parallel.
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5 med transducerens udgangsledninger, og tjener til at foretage en middelværdibestemmelse af det systoliske og diastoliske tryksignal fra transduceren 22.5 with the transducer output lines, and serves to average the systolic and diastolic pressure signal from the transducer 22.
Visse transducertyper, der har et blodreservoir og mekanisk mâler 5 ekspansion og kontraktion af et kammer, vil ikke beheve det middel-værdibestemmende kredslob, da udgangssignalet fra denne transducer-type middelværdibestemmes mekanisk.Certain transducer types which have a blood reservoir and mechanically measure expansion and contraction of a chamber will not interfere with the mean value circuit as the output of this transducer type is mean value mechanically.
Det middelværdibestemte transducersignal fores sâ frem til en af ind-gangene pâ en konventionel operationsforstærker 31, der udgor en del 10 af en sammenligningsenhed 30. En begyndelsesreferencekontrol 32 frembringer et referencesignal pâ operationsforstærkeren 31's anden sammenlignende indgang. Begyndelsesreferencekontrollen kan være enten en fast eller variabel spændingsdeler, der frembringer et for-etableret signalniveau pâ det ene af mindst to operationsforstærker-15 indgange.The averaged transducer signal is then forwarded to one of the inputs of a conventional operational amplifier 31 constituting part 10 of a comparison unit 30. An initial reference check 32 generates a reference signal of the second comparative input of the operational amplifier 31. The initial reference control may be either a fixed or variable voltage divider producing a pre-established signal level at one of at least two operational amplifier inputs.
Sammenligningsenheden 30's operationsforstærkerdel 31 anvendes pâ summationsmâden, ved hvilken de to indgange adderes for at danne et udgangssignal til en elektronisk afbryder 36, hvis udgangssignal er proportionalt med summen af indgangssignalerne. Den elektroniske af-20 bryder 36 omfatter fortrinsvis et konventionelt tærskelvsrditrigger-kredslob, der er i stand til at omdanne udgangssignalet fra operati-onsforstærkeren 31 til impulser med en varighed, der er propcrtional med amplituden af operationsforstærkerens udgangssignal. En almînde-lig, let tilgængelig komponent til udforelse af den elektroniske 25 afbryders funktion kan være enhver passende type stroffistyret str®a-kilde, f.eks. en unijunction-transistor med en ydre basis-tîl-emittersynkroniseringskapacitet, der anvendes til at affyre en triac eller lignende.The operation amplifier portion 31 of the comparator 30 is used in the summation method by which the two inputs are added to form an output of an electronic switch 36, the output of which is proportional to the sum of the input signals. The electronic switch 36 preferably comprises a conventional threshold detector trigger circuit capable of converting the output of the operational amplifier 31 to pulses of a duration proportional to the amplitude of the output of the operational amplifier. A common, easily accessible component for carrying out the operation of the electronic switch can be any suitable type of power-controlled power source, e.g. a unijunction transistor having an external base-tlil emitter synchronization capability used to fire a triac or the like.
Effektforsyningen til sammenligningsenhedens operationsforstærkerdel 30 er en impulsgenerator 34, der frembringer et sædvanligt firkantbolge-spændingssignal, der bevirker, at operationsforstærkerens udgangssignal afbryder og slutter med konstant hastighed. En hvilken som helst passende konventionel impulsgenerator, der har tilstrækkelig udgangsspænding til at drive operationsforstærkeren, er acceptabel.The power supply to the comparator operation amplifier portion 30 is an impulse generator 34 which produces a conventional square bolt voltage signal which causes the output amplifier output to interrupt and terminate at a constant rate. Any suitable conventional pulse generator having sufficient output voltage to operate the operational amplifier is acceptable.
DK 156413 BDK 156413 B
66
Det bemærkes, at signalet fra operationsforstærkeren er en periodisk impuls, der har en amplitude, soin er proportional med summen af be-gyndelsesreferencesignalet og det middelværdibestemmende transducer-signal. Jo hojere udgangssignalet fra sammenligningsenheden er, des 5 storre er det tidsinterval, i hvilket afbryderen 36 er sluttet, og omvendt er det tidsinterval, i hvilket afbryderen er âben, jo mindre, des mindre signalet fra sammenligningsenheden er.It is noted that the signal from the operational amplifier is a periodic pulse having an amplitude soin proportional to the sum of the initial reference signal and the mean value transducer signal. The higher the output of the comparator, the greater the time interval in which the switch 36 is connected and, conversely, the time interval in which the switch is open, the smaller the signal from the comparator.
Som vist i fig. 1 fores den regulære effektforsyningsledning til den konventionelle blodpumpe og reguleringsapparatet gennem den elektro-10 niske afbryder 36. De bolgeformer, der er vist i fig. 2 og 3, er régis treret ved punkt A i det i fig. 1 vis te diagram, idet det antages, at der er taie om en vekselstromsforsyning som den, der er til râdig-hed ved en standardstikkontakt. Den skraverede del af bolgeformerne repræsenterer den del af bolgeformen, ved hvilken den elektroniske 15 afbryder 36 er âben. Nâr afbryderen 36 sluttes, forbliver den sluttet, indtil vekselstromskurven gâr gennem nul. Da afbryderen 36 er âben eller afbrudt under storstedelen af den i fig. 3 viste veksel-stromsperiode, er den energi, der fores fra pumpens effektforsyning 35 til pumpekontrolapparatet 39, relativ lille. Derfor arbejder blod-20 pumpen 37 langsomt. Omvendt, nâr afbryderen 36 er sluttet under det meste af vekselstromsperioden (se fig. 2), er den energi, der fores til reguleringsapparatet 39, relativ stor, og blodpumpen 37 vil ar-bejde forholdsvis hurtigt.As shown in FIG. 1, the regular power supply line is fed to the conventional blood pump and regulator through the electronic switch 36. The waveforms shown in FIG. 2 and 3 are reported at point A of the embodiment shown in FIG. 1 shows a diagram assuming that there is no AC power supply such as that available at a standard outlet. The shaded portion of the waveforms represents the portion of the waveform at which the electronic switch 36 is open. When the switch 36 is closed, it remains closed until the AC curve goes through zero. Since the switch 36 is open or disconnected during the majority of the embodiment shown in FIG. 3, the energy supplied from the pump power supply 35 to the pump control apparatus 39 is relatively small. Therefore, the blood-20 pump 37 operates slowly. Conversely, when the switch 36 is closed during most of the AC period (see Fig. 2), the energy supplied to the regulator 39 is relatively large and the blood pump 37 will operate relatively quickly.
De eksisterende blodpumpereguleringsapparater er fortsat anvendelige 25 til at sætte ovre grænser for blodpumpens hastighed. Ved hjælp af apparatet ifolge opfindelsen frembringes imidlertid ojeblikkelig og kontinuerlig kompensation for blodpumpens hastighed som folge af aen-dringer i blodstrommen fra patienten. Nâr blodstrommen formindskes, vil udgangssignalet fra sammenligningsenheden 30 blive reduceret, og 30 derfor tillader den elektroniske afbryder 36 en mindre del af pumpens effektforsyningssignal at blive fort til blodpumpen (se fig. 3).The existing blood pump regulators continue to be useful for setting upper limits on the blood pump speed. However, by means of the apparatus according to the invention, immediate and continuous compensation for the speed of the blood pump is produced as a result of changes in the blood stream from the patient. As the blood flow decreases, the output of the comparator 30 will be reduced, and therefore the electronic switch 36 allows a smaller portion of the pump power supply signal to be fed to the blood pump (see Fig. 3).
Ogsâ hvis blodstrommen fra patienten skulle stige under dialysens forlob, vil den mængde effekt, der tilfores blodpumpen, stige, hvorved pumpens hastighed vil stige (se fig. 2). Derfor vil 35 "pumpestarvation" som folge af en vakuumforârsaget sammenklapning af 7Also, if the blood flow from the patient should increase during the course of the dialysis, the amount of power supplied to the blood pump will increase, thereby increasing the pump speed (see Fig. 2). Therefore, 35 "pump starvation" will result from a vacuum-caused collapse of 7
DK 156413 BDK 156413 B
blodledningerne og af blodkar blive undgâet, fordi pumpen 37 kun vil arbejde med maksimal hastighed, nâr deime passer til den disponible blodforsyning.the blood lines and blood vessels are avoided because the pump 37 will only operate at maximum speed when it fits the available blood supply.
Ved brug af apparatet ifolge opfindelsenrer patienten forbundet til 5 dialyseapparatet pà konventionel mâde, idet forsyningsledningen 24 normalt er i direkte forbindelse med diâlyseapparatets blodkredslob for pumpen regnet i stromningsretningen. -Ved en foretrukken anven-delsesmetode bliver hj ælpereguleringsappanatet 20 forst afbrudt for ikke at hâve nogen virkning pâ den effekç,<der fra forsyningen 35 10 tilfores pumpereguleringsapparatet 39. -Jinaanden mulighed er, at hjælpereguleringsapparatet 20 kan forblive tændt, men at begyndel-sesreferencekontrollen 32 indstilles pâ iètnmaksimum for ikke at influere pâ indstillingen af en onsket màksimal stromningshas tighed pâ reguleringsapparatet 39.When using the apparatus according to the invention, the patient is connected to the dialysis apparatus in a conventional manner, the supply line 24 being normally in direct communication with the blood circulation circuit of the dialysis apparatus of the pump in the flow direction. -In a preferred method of use, the auxiliary controller 20 is first disconnected so as to have no effect on the power supplied to the pump controller 39 from the supply 35 10. 32 is set to a maximum, so as not to affect the setting of a desired maximum flow rate on the controller 39.
15 iDerefter fores der strom til blodpumpen'i37, og blodpumpens hastighed .foroges ved indstilling af pumpereguleringsapparatet 39 til den on-.skede maksimale blodstrom. Man kan forvisse.sig om, at den onskede maksimale blodstrom copnâs ved, at man holder oje med den négative trykudlæseerihed 23 qg lader bla’dpiaippens hastighed s tige, indtil det 20 négative tryk nâr det;niveau, der oer foreskrevet af den tilstedevæ- rende læge. Alternafivt kan den onskede maksimale strom opnâs ved, at man lader pumpehastigheden stige, .indtil blodledningen eller den tilhorende akkumulator klapper sammen, og derefter reducerer blodpumpens hastighed gennem reguleringsapparatet 39 en lille smule, 25 indtil fuld strom er opnâet.Thereafter, current is supplied to the blood pump 37 and the speed of the blood pump is increased by adjusting the pump control apparatus 39 to the desired maximum blood flow. It can be assured that the desired maximum blood flow is copied by keeping an eye on the negative pressure readout 23 qg and let the speed of the bladder drop until the negative pressure reaches the level prescribed by the presence. running doctor. Alternatively, the desired maximum current can be obtained by increasing the pump speed until the blood line or associated accumulator collapses, and then reducing the blood pump speed through the regulator 39 slightly until full flow is achieved.
Sà snart den onskede maksimale strom er etableret i blodpumpen 37, aktiveres hjælpereguleringsapparatet 20 ved indstilling af begyndel-sesreferencekontrollen 32, i det mindste indtil det af udlæseenheden 23 for negativt tryk fremgâr,, at hjælpereguleringsapparatet 20 frem-30 bringer en blodstrom, der i det væsentlige er den pâ pumpereguleringsapparatet 39 indstillede unaksimale hastighed. Man har ofte fundet det onskeligt at indstille begyndelsesreferencekontrollen pâ en specifik negativ trykaflæsning, der repræsenterer en onsket blod-s tromningshas tighed.As soon as the desired maximum current is established in the blood pump 37, the auxiliary regulator 20 is activated by setting the initial reference check 32, at least until the negative pressure readout unit 23 states that the auxiliary regulator 20 produces a blood stream which essential is the unmaximum speed set on the pump controller 39. It has often been found desirable to set the initial reference control to a specific negative pressure reading representing a desired blood-flow rate.
Claims (7)
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US399904A US3882861A (en) | 1973-09-24 | 1973-09-24 | Auxiliary control for a blood pump |
| US39990473 | 1973-09-24 |
Publications (3)
| Publication Number | Publication Date |
|---|---|
| DK485374A DK485374A (en) | 1975-05-20 |
| DK156413B true DK156413B (en) | 1989-08-21 |
| DK156413C DK156413C (en) | 1990-01-22 |
Family
ID=23581426
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| DK485374A DK156413C (en) | 1973-09-24 | 1974-09-16 | BLOOD PUMP CONTROL UNIT |
Country Status (12)
| Country | Link |
|---|---|
| US (1) | US3882861A (en) |
| JP (1) | JPS6231949B2 (en) |
| BE (1) | BE820223A (en) |
| CH (1) | CH582519A5 (en) |
| DD (1) | DD115038A5 (en) |
| DE (1) | DE2445403C2 (en) |
| DK (1) | DK156413C (en) |
| FR (1) | FR2244546B1 (en) |
| GB (1) | GB1487242A (en) |
| IT (1) | IT1022226B (en) |
| NL (1) | NL7412448A (en) |
| SE (1) | SE411704B (en) |
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- 1973-09-24 US US399904A patent/US3882861A/en not_active Expired - Lifetime
-
1974
- 1974-09-13 CH CH1247274A patent/CH582519A5/xx not_active IP Right Cessation
- 1974-09-16 DK DK485374A patent/DK156413C/en not_active IP Right Cessation
- 1974-09-17 SE SE7411684A patent/SE411704B/en not_active IP Right Cessation
- 1974-09-20 GB GB41134/74A patent/GB1487242A/en not_active Expired
- 1974-09-20 NL NL7412448A patent/NL7412448A/en not_active Application Discontinuation
- 1974-09-20 JP JP49107859A patent/JPS6231949B2/ja not_active Expired
- 1974-09-20 FR FR7431876A patent/FR2244546B1/fr not_active Expired
- 1974-09-23 DE DE2445403A patent/DE2445403C2/en not_active Expired
- 1974-09-23 BE BE148793A patent/BE820223A/en not_active IP Right Cessation
- 1974-09-23 IT IT27602/74A patent/IT1022226B/en active
- 1974-09-23 DD DD181245A patent/DD115038A5/xx unknown
Also Published As
| Publication number | Publication date |
|---|---|
| FR2244546B1 (en) | 1978-04-28 |
| JPS5063790A (en) | 1975-05-30 |
| BE820223A (en) | 1975-01-16 |
| US3882861A (en) | 1975-05-13 |
| DK156413C (en) | 1990-01-22 |
| SE7411684L (en) | 1975-03-25 |
| DD115038A5 (en) | 1975-09-12 |
| DE2445403A1 (en) | 1975-04-03 |
| NL7412448A (en) | 1975-03-26 |
| CH582519A5 (en) | 1976-12-15 |
| DE2445403C2 (en) | 1983-09-01 |
| FR2244546A1 (en) | 1975-04-18 |
| IT1022226B (en) | 1978-03-20 |
| GB1487242A (en) | 1977-09-28 |
| JPS6231949B2 (en) | 1987-07-11 |
| DK485374A (en) | 1975-05-20 |
| SE411704B (en) | 1980-02-04 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PBP | Patent lapsed |