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    • 专利摘要:
    The invention relates to a device (2) for impedance measurement on body segments with a current source (4), current switches (3), current electrodes (8) which can be applied to the body segments, voltage switches (10) and measuring electrodes (14). The outputs of the power source (4) are connected to inputs of the power switch (3). Each power switch (3) has several, with the input of the respective power switch (3) interconnectable outputs. The outputs of the power switch (3) are connected to electrical feed lines (5) of the current electrodes (8). The measuring electrodes (14) detect voltage signals that are used with the current supplied by the current source (4) for impedance measurement of the segments. In the feed lines (5) near the current electrodes (8) switching devices (7) are installed. The device (2) connects only two current electrodes (8) to the current source (4) by switching the current switch (3) and the switching devices (7) and disconnects all remaining current electrodes (8) by switching the switching device (7) from the feeder line (5) and the feed line (5) by switching the power switch (3) from the power source (4).
    公开号:AT516499A4
    申请号:T50317/2015
    申请日:2015-04-22
    公开日:2016-06-15
    发明作者:Falko Skrabal；Philipp Glitzner
    申请人:Skrabal Falko Dr；
    IPC主号:
    专利说明:

    Body impedance meter
    Recently, in the development of medical body impedance meters, there has been a tendency to obstruct the measurement of body compartments by means of whole-body impedance in favor of measurement of body compartments by means of segmental impedance measurements. In whole-body impedance, the human or animal body is considered to be composed of various electrically conductive body parts, and mathematical models attempt to account for the different diameters and lengths of these electrical conductors (namely, arms, legs, and torso). Since the resistance of an electrical conductor, apart from its specific resistance, depends primarily on its length and cross-section, in this method it is necessary to assume fixed ratios of body size to the diameters and cross-sections of the trunk and extremities. Standard proportions of the human body, e.g. from surveys to US Army personnel. However, these models and assumptions introduce such inaccuracies into the method that it is approximately applicable to the examination of healthy persons, but not in sick people.
    With the segmental impedance measurement of body compartments, especially when performed at several different frequencies, one can better take into account the different dimensions of the body parts and their effects on the AC conductivity. With the segmental impedance measurement it is particularly tried to distinguish between intracellular and extracellular water by means of multi-frequency measurements. Despite all the advances in the field, it has not yet been possible to introduce these methods into the routine care at the bedside. An exception is the measurement of lymphoedema on individual extremities, or the attempt to quantify over- and underhydrogenation of dialysis patients on a part of the body, namely the lower leg.
    Numerous patents have been filed for segmental impedance analysis. For example, in the impedance measuring device proposed in WO 2007/002991 (Chetham) and in US Pat. No. 8,785,551 (Chetham), the measuring current is measured and subsequently readjusted; no switching possibilities are provided. In US 8594781 (Chetham) an impedance measuring device is disclosed in which measuring electrodes are switched off in order to eliminate inductive interference. In the impedance meter according to US 2011/0087129 (Chetham), a first system determines the impedance procedure, selects instructions, a second system generates control signals according to these instructions. Chatham US 8548580 proposes two systems, the first of which selects the instructions for the measurement and transfers these instructions to a second system. The patent application US 2008/0009757 A1 (Tsoglin) discloses an impedance measuring device in which the current distortion ions in unmeasured body sections are taken into account in accordance with an electrical model, which evidently concerns the Kirchhoff rules. Cha in US 8386028 examines two segments simultaneously at two different frequencies. In US 2011/0046505 (Comish) two different body segments are compared with each other.
    WO 2008/031030 (Bartnik) discloses obtaining systolic time intervals by subtracting from a first waveform derived from an impedance signal a second waveform obtained from echocardiography or from the pulse wave or pulse oximeter. WO 2006 / 063255A2 (Bernstein) discloses determining the stroke volume from the impedance signal across the thorax or over the brachial artery. US 2013/0096448 (Brooks) describes a combined ECG (electrocardiography), ICG (impedance cardiography) and phonon electrodes on a common carrier with acoustic chamber. The specifications US 8521264 and US 2010/0324404 describe the use of a maximum of three combined ECG-ICG electrodes, all of which are placed on the thorax. US 6339722 (Heethaar) proposes to measure the thorax as a segment at two frequencies and at two different measurement distances to obtain information about cardiac activity. For a rapid and less cumbersome implementation of a multisegmental multi-frequency impedance analysis, it is necessary to measure automatically and expediently without user intervention numerous body segments. For this purpose, a multiplexer is usually provided, which is installed in the device. Multiplexers for impedance measurement are used in part in the impedance measuring devices cited above to supply current at various points of the body and, on the other hand, to measure the voltage at various points of the body.
    However, there are some, not noted in the above-cited documents difficulties. For many applications, the distance between the meter and the body being examined must be kept large, resulting in relatively long cable lengths. This can cause significant difficulties and errors in the measurement. Thus, through the cables and their shields parasitic capacitances and
    Inductors arise. Applicant's investigations have shown that, in particular, it is necessary to prevent parasitic leakage currents from flowing into the additionally applied cables by cables applied simultaneously to the body, which are not provided for the current supply at the time of use. Furthermore, it must be prevented that the combined supply and measuring cables, which lead to numerous supply and measuring points, stray impedances and stray capacitances cause a falsification of the measured signals in the individual cables.
    It is therefore the object of the present invention to provide a device which overcomes these difficulties and disadvantages of the prior art.
    The present invention achieves this object by a device having the features of claim 1. Advantageous embodiments of the invention are set forth in the subclaims.
    The impedance measuring device according to the invention on segments of a human or animal body, wherein the impedance measurement is preferably a multi-frequency impedance measurement, comprises a current source, current switch, current electrodes and measuring electrodes that can be arranged on segments of the human or animal body. Each output of the power source is connected to an input of a power switch, each power switch has a plurality of outputs and the input of the respective power switch is switchable connected to one of its outputs, the outputs of the power switch are connected to electrical feed lines of the current electrodes. The measuring electrodes detect voltage signals and the device determines from the current supplied by the current source and the detected voltage signals, the impedances of the segments of the human or animal body. In the supply lines switching devices are installed near or directly to the current electrodes, with which the current electrodes are connectable to their supply lines and separable from them. The apparatus is configured to connect only two current electrodes to the power source by switching the power switches and the switching devices, and to disconnect all remaining power electrodes from the power supply by switching the switching device and disconnecting the power line from the power source by switching the power switches.
    Preferably, voltage amplifiers or voltage followers with high input resistance are inserted into the signal lines near or directly at the measuring electrodes. For automatic measuring operations, the switching devices should be made switchable by the device. For the automatic measurement of impedances at different body segments is provided in an embodiment of the invention that signal lines of the measuring electrodes are guided to inputs of Spannungsumschaltem, wherein the voltage switch each having an output which is interconnectable with an input of the voltage switch. With this configuration, impedance measurement can be simplified by connecting the outputs of the voltage switches to inputs of a differential amplifier which detects from the voltage signals applied to its inputs a differential voltage that the device uses for impedance detection.
    High reliability and fast measurements are achieved by the current switch and / or the voltage switch are designed as relays or multiplexers. A significant improvement in the measurement results is ensured when the device according to the invention is equipped with a common-mode rejection. For this purpose, the invention provides that at least one of the current electrodes can be acted upon via a resistor with a compensating current, wherein the connection of the resistor is arranged on the current electrode between the switching device and the current electrode. Alternatively or additionally, a compensation current electrode is provided, which can be acted upon by a resistor with a compensating current.
    The handling of the device according to the invention becomes particularly easy for the examination staff when, apart from possibly existing individual measuring electrodes, in each case one current electrode and one measuring electrode are grouped into a unified electrode region. The handling of the device is further simplified in that the current electrode and the measuring electrode of the unified electrode region have jointly guided cables as a feed line and signal line, since only half the number of cables has to be handled by this measure. A further simplification of the handling results from the fact that the current electrode and the measuring electrode are arranged on a common electrode carrier. The common electrode carrier is preferably a clamp, a band, a cuff or even a pressure cuff (similar to the pressure cuffs used for blood pressure measurement). If a clamp, cuff or pressure cuff is used, a pressure sensor for pulse measurement can also be arranged on it. It is advantageous for carrying out automatic measurements when the pressure sensor has a liquid-filled bubble which communicates with a pressure transducer, wherein preferably the liquid-filled bubble can be pressed against a body part by means of a controlled, hydraulic or electromotive pressure device.
    It has been found that the accuracy of the measurements is substantially increased if the device only connects the current electrode to the current source from at most one united electrode region and uses the measuring electrode for voltage measurement. In this regard, it has been found advantageous to combine unified electrode regions for attachment to peripheral body segments and to central body segments, with possibly also a further unified electrode region being selectable for attachment to a body region to which the chest wall electrodes VI to V6 are preferred V4 to V6, an ECG are placed. In the simplest application, however, only one of the chest wall electrodes V1-V6, preferably V4 to V6, has to be used as the measuring electrode for the impedance measurement.
    Furthermore, it is expedient if the device is equipped with a differentiator for determining the change in the impedance with the heartbeat.
    In a preferred embodiment of the device according to the invention, an ECG device is integrated into the device, wherein the ECG device has at least extremity electrodes, preferably also chest wall electrodes. This makes it possible to simultaneously carry out impedance measurements and ECG recordings with the device according to the invention. In order to minimize the number of electrodes to be attached to the body, the invention also proposes that the measuring electrodes are designed as ECG electrodes by routing branch lines of the signal lines of the measuring electrodes to the ECG device.
    If the current electrodes and / or the measuring electrodes are designed as sensors and / or encoders for physical variables, in particular acceleration values, pressure, sound, temperature or light, other physical parameters and parameters can also be measured during the impedance measurements. Reliability of the measurement and easy handling is achieved by designing at least some of the current electrodes and the measuring electrodes as suction electrodes or adhesive electrodes.
    The invention will be explained in more detail by means of embodiments with reference to the drawings.
    Fig. 1 shows a schematic block diagram of the device according to the invention.
    Fig. 2 shows application examples of the device according to the invention.
    In the following description, reference is made to FIGS. 1 and 2. For the sake of clarity, in each of the two figures, identical parts which are shown side by side and have an identical configuration are provided only once with a reference symbol.
    1 shows a schematic block diagram of the device 2 according to the invention for measuring impedances of segments of a human or animal body. The device 2 comprises a current source 4 with two partial current sources 4a, 4c of opposite polarity, controllable by a control current Isoll, in that the control current Isoll to one of the partial current sources 4c passes through an inverter 4b before it enters this partial current source 4c. The output of each partial current source 4a, 4c is connected to the input of a current switch 3, e.g. is designed as a multiplexer. Each current switch 3 has a plurality of outputs, wherein the input is switchably connected to one of the outputs. The outputs of the power switch 3 are connected by means of electrical supply lines 5 with current electrodes 8. The current electrodes 8 are drawn with dotted area. The current electrodes 8 are applied to individual body segments of the examined animal (human or animal). The surface of the examined animal 6 is shown symbolically in FIG. 1 in a dashed border. Near the current electrodes 8 5 switching devices 7 are installed in the feed lines, with which the current electrodes 8 from the feed line 5 can be switched on and off. This serves to ensure that parasitic leakage currents do not pass from the current electrodes 8 to the device 2 during operation of the device 2, since the switching devices 7 in the switched-off state ensure separation of the current electrodes 8 from the supply lines 5. The switching devices 7 can be designed as mechanical switches (for example micro-relays), electronic switches or also as negative impedance converters. Thus, each feed line 5 is switched away on the one hand in the device 2 by the power switch 3 from the power source 4 and on the other hand additionally by the switching device 7 peripherally away from the device 2 a second time away from the current electrode 8, thereby parasitic leakage currents flowing through the body of the living being could get into the cables of the feed lines 5 from the periphery forth, be prevented. This is especially important because the cables of the
    Feed lines 5 advantageously shielded and - for an even better shielding effect - should be provided with an active shielding. This could, however, also flow over capacitances between cable and screen generated alternating current, which is prevented by the switching devices 7.
    In the embodiment of Fig. 1, six current electrodes 8 are provided. The first four current electrodes 8 are exemplary of the right leg current supply (designation RLc for right leg current), the left leg (designation LLc for left leg current), the right arm (designation RAC for right arm currrent) and the left arm ( Designation LAc for left arm current). The fifth, optionally-to-be-attached, current electrode 8 is for attachment to the upper thorax aperture, e.g. near the upper sternum, at the neck or at the head to feed the current (designation Nc for Neck current). The sixth current electrode 8 is provided for current injection at the lower end of the thorax (designation Thc), e.g. in the region where for an ECG the leads V4 to V6 or V4r to V6r are arranged.
    Each current electrode 8 is associated with a measuring electrode 14, wherein the current electrode 8 and the measuring electrode 14 are not electrically connected to each other and the combination of current electrode 8 and measuring electrode 14 is arranged on the living organism 6 in a so-called unified electrode region 1. The distance between the electrodes 8, 14 of the unified electrode region should not be less than 2 cm to 4 cm, better 3 cm to 4 cm and not exceed 20 to 30 cm. In the exemplary embodiment of FIG. 1 there are thus, for example, six united electrode regions 1 each having a current electrode 8 and a measuring electrode 14 and at least one individual additional measuring electrode 20.
    Measuring electrodes 14 are designated RLV for right leg voltage, LLV for left leg voltage, RAV for right arm voltage, LAV for left arm voltage, Nc for neck voltage, and Thv for thorax voltage. Each measuring electrode 14, together with the associated current electrode 8, may be attached to a suitable common electrode carrier, e.g. a clamping electrode, adhesive electrode, suction electrode, band electrode, sleeve electrode or pressure sleeve electrode may be arranged. Alternatively, the measuring electrodes 14 and current electrodes 8 are present as separate individual electrodes.
    The measuring electrodes 14 are connected to signal lines 19, which are led to inputs of two voltage switches 10, wherein in the signal lines 19 voltage amplifiers 9 are connected. The voltage amplifier 9 can be designed as a voltage follower with high input resistance. The voltage amplifiers 9 should be arranged as close as possible or directly to the measuring electrodes 14. The voltage switch 10 are designed for example as a relay or electronic voltage multiplexer. By means of the voltage change-over switch 10, in each case a signal of a measuring electrode 14 can be switched to the outputs of the voltage changeover switch 10, where it is then used for further processing, e.g. is passed to an input of a differential amplifier 11. The output signal UDiff of the differential amplifier is the difference of the output signals of the two voltage changeover switch 10.
    Another important prerequisite for the optimal functioning of the device 2 is the provision of a common mode rejection, since a large electromagnetic interference exists through the living being 6 being examined. Also, AC interference caused by the power supply network can cause large disturbances. Furthermore, there must be a mismatch of the various
    Cable capacitances and cable impedances of the feed lines 5 and signal lines 19 are compensated. In addition to the usual methods of optimum shielding of the cables, even using active shielding, use of special signal filtering techniques, such as adaptive filters or "notch" filters, balancing the common mode voltage by balancing current through one high resistance 12 having a resistance between 470 kOhm and 1.5 MOhm, preferably 1 MOhm, for this purpose, however, one terminal of the resistor 12 must be connected to at least one of the supply lines 5 to the current electrodes 8, between the switching device 7 and The other terminal of the resistor 12 is connected to the output of an operational amplifier 13 which supplies the equalizing current 12. The resistor 12 is advantageously placed just next to the current electrode 8 used for the injection of the compensating current 8. Each of the current electrodes 8 is for feeding the equalizing current, alternatively or additionally, a dedicated equalizing current electrode 8a may be provided which is connected through a resistor 12a (between 470 kohms and 1.5 megohms, preferably 1 megohms) to the output of an operational amplifier 13a which provides the equalizing current in a known manner.
    With the thus constructed device 2, many segments of the living organism 6 can be examined accurately. On the one hand, it is possible with the aid of the control signal Isoll and the two inverse-operated partial current sources 4a, 4c to generate alternating currents of arbitrary frequency and to conduct these by means of the two current switches 3 to freely selectable current electrodes 8. On the other hand, with the aid of the two voltage changeover switches 10, voltage signals of freely selectable measuring electrodes 14 can be selected for further processing, in particular for difference formation at the differential amplifier 11. The control of the control signal Isoll, the current switch 3, the voltage switch 10, the mathematical processing of the voltage signals detected by the measuring electrodes 14 and the control of all other functions of the device is carried out by means of a built-in device 2 CPU 23, for example in the form of a microcontroller is executed. The numerous necessary leads to the CPU 23 are not drawn in the sense of the overview.
    Thus, it is possible to automatically perform impedance measurements at different frequencies on different segments of the living organism 6 by means of the device 2. On the basis of these impedance measurements on different body segments, the device 2 also offers the possibility of impedance cardiography (KG).
    Further, the CPU 23 in the device 2 may determine the body composition of the whole body of the animal 6 and its body parts, such as those based on the impedance measurements with stored empirical equations or with predetermined mathematical models. the body water contained in body parts, the extracellular fluid, the muscle mass, the fat mass, their deviations from the target value, as well as edema or fluid accumulation in body parts calculate and the calculated results for display on a screen, for storage in a non-volatile memory or for further processing in databases output. It should be emphasized that the physician uses the device 2 to diagnose deviations in hydrogenation from the norm, e.g. Deviations in the relation between fat mass or "lean body mass" to the extracellular volume or the ratio of extracellular to intracellular volume or whole body water, make and thus better overhydration or dehydration can determine. Furthermore, arterial circulatory disorders, especially of the legs or their segments, can be detected and output. Thus, from the difference in the acceleration of the volume of the legs with the heartbeat, an "Ankle Brachial Index" (ABI), as known from the literature, can be calculated. The impedances determined by the device 2, as well as their resistance and reactive impedance components and the phase angle of the impedance serve to develop regression equations by means of multiple regressions or neural networks, to estimate the parameters of interest to the physician, and those by gold standard methods such as whole body DXA, deuterium dilution To predict sodium bromide dilution or other tracer-determined parameters.
    When the device 2 additionally differentiates the detected impedance signals and relates them to the heartbeat, the thus calculated change in impedance with the heartbeat can be used to measure the acceleration of the blood in various parts of the body. This is particularly useful when it is in a segment defined by a central unified electrode region on the one hand (eg at the neck, neck or shoulders) and a further central single electrode (selected eg from V4 to V6 or from V4r to V6r) and a peripheral united electrode region and a central and a peripheral united electrode region, on the other hand, as described in Skrabal et al, Medical Engineering & Physics 36 (2014) 896-904. It is only essential that at least one measuring electrode 14 comes to lie between two current electrodes 8. Thus, not only the cardiac output can be assessed and a heart failure diagnosed, but also in the sense of impedance rheography, the measurement of arterial and venous perfusion or the pulse wave transit time (volume lead time) done. Again, gold standard techniques such as echocardiography and other hemodynamic methods such as ankle brachial index, pulse wave transit time, augmentation index pulse wave analysis, central and peripheral compliance, and pulse curve stroke volume gold standard techniques are advantageously used to calibrate the new methods.
    An ECG device 21 can also be integrated in the device 2. This ECG device 21 may be equipped with its own ECG electrodes, which are not shown in FIG. 1 for reasons of clarity. However, as a particular advantage, the device 2 also offers the possibility of carrying out the measuring electrodes 14 as ECG electrodes, in that branch lines 22 are routed from the signal lines 19 of the measuring electrodes 14 to the ECG device 21, preferably between voltage amplifier 9 and voltage switch 10. Thus, the device 2 can serve as a multi-channel ECG device and simultaneously perform the described impedance measurements and calculations from the detected impedances during the recording of a multi-channel ECG. In that for the extraction of the templates a recording over some time, e.g. 2 to 3 minutes, a rhythm strip is automatically generated, as it is also desired for the usual ECG and is common. This also allows spectral analysis of heart intervals and changes in impedance with the heartbeat. Thus, the proportions of sympathetic and vagus heart rate control can be determined via the corresponding frequency bands, for example by means of the 0.1 Hz band and the 0.3 Hz band, which is particularly suitable for ascertaining overtraining, bumout, depression, etc. especially if it is trackable over weeks and months over time. All this is not associated with an increased amount of time compared to the usual rhythm strip for the ECG.
    The invention also provides that sensors or actuators are attached to the current electrodes 8 or measuring electrodes 14, e.g. Accelerometers, pressure sensors, or light sensors, LEDS or pressure pumps. In FIG. 1, a measuring transducer / transmitter 17 is schematically drawn lying directly below an electrode (current or measuring electrode can be used), which optionally can also be embodied as a measuring sensor and / or sensor 17a lying next to the electrode. The measured variable sensor 7 and / or encoder 17, 17a is controlled by an evaluation unit 18, which in this case also acts as a generator for the measured quantity to be impressed, eg. generates a pressure signal. The pickup / encoder 17, 17a is connected to an input of the evaluation unit 18, which records the recorded measured variable, e.g. a pressure signal, acceleration signal, temperature signal, etc. evaluates. With such described sensors, the device 2 at the same time for impedance measurement and ECG recording other circulatory parameters, such as the circulatory times, pulse wave analysis including heartbeat volume, pulse oximetry, etc., with corresponding methods in the document WO 2004/030535 Al (Skrabal) and EP 2319411 A2 are disclosed in detail. The pulse wave analysis can then also be used to calculate other parameters, such as vessel stiffness, augmentation index, central aortic pressure, slough volume, and so on. Also, the possible attachment of blood pressure cuffs, including on the lower limb for the determination of the ankle brachial index and venous occlusion plethysmography, is provided.
    Thus, the device 2 is a measuring device that in the full expansion stage not only performs the impedance measurement on multiple body segments of a human or animal body at multiple or multiple impedance frequencies but optionally also a differentiator (which may be integrated with the CPU 23) for detection includes the impedance change with the heartbeat. The heartbeat can be accurately detected from the ECG, so that thereafter a time window can be set to search for the impedance change with the heartbeat. Templates are generated from the different segments for impedance cardiography and impedance rheography. If necessary, the measuring device is also a (multi-channel) ECG device, and serves as an analyzer for further physical variables, provided that the corresponding sensors and actuators are installed in the electrodes.
    Fig. 2 shows, by means of four examples A, B, C, D, the application of the principle of partial or complete separation of the combined electrode regions 1 for current injection (C for current) through the current electrodes 8 and voltage measurement (V for voltage) through the measuring electrodes 14 of the device 2. As can be seen in these examples, the unified electrode regions 1 for the power supply on the one hand and the voltage measurement on the other hand partially or even completely different uses. The current electrodes are here with dotted area, the measuring electrodes drawn white. If a pair of electrodes is anatomically out of the circuit, it is also shifted in the drawing and drawn outside the circuit.
    In one embodiment of the invention, the device determines the impedance and a change in impedance with the heartbeat in at least two body segments, the segments being defined as follows. a) On the one hand, the central segment with respect to the power supply is defined by the current electrodes 8 of a central (Z) combined electrode region 1 and a peripheral (P) unified electrode region 1, the measuring path on the other hand is defined by the measuring electrode 14 of the central unified electrode region 1 and by a Measuring electrode 20, which is also used to derive the chest wall ECG. (FIG. 2-A, continuous measuring path V.) Here, too, a further central combined electrode region 1 could be used with less ease, the measuring electrode 14 of which is used to measure the impedance and whose current electrode 8 is used to supply the current (not shown). Alternatively, with the same feed as above, the measuring path V could be defined by the measuring electrode 14 of the central unified electrode region and by the measuring electrode 14 of a unified electrode region which is not within the circuit (e.g., positioned on the contralateral leg). B) On the other hand, the peripheral body segment in the current feed is defined by the current electrodes 8 of two peripheral united electrode regions (eg attached to both legs), whereas the measuring path is defined by a measuring electrode outside of the circuit (eg, the ECG electrode 20 overlying the chest wall) and the measuring electrode 14 of the unified electrode region 1, which was also used for current injection (Figure 2-B, solid circle). Alternatively, with the same supply, the measuring circuit could be located by a measuring electrode 14 located outside of this circuit of a central united electrode region and by the measuring electrode 14 of FIG
    Stromeinspeisung be used electrode region defined (Fig. 2-B, dashed measuring path). Analogous to these embodiments, another segment between the central single electrode 20, which could correspond to an ECG chest wall electrode, and the measuring electrode 14 of a unified electrode region, which is not flowed through by the current, can also be analyzed (dashed line with Vv). It could be e.g. to act around the abdomen segment. c) Fig. 2-C shows a similar Messanordung as Fig. 2-B, with which a further peripheral body segment can be measured. For example, this could be the arms. This figure illustrates how many different measuring points can be used as long as they are outside the circuit. This of course also applies to the other figures 2-A, 2-B, 2-C, where this is not shown there for reasons of clarity. However, the power supply should be such that not two body segments with pulsatile change in volume flow through together electrically and measured together, because the pulsatile components would mingle. It would then be possible, but laborious, to calculate the pulsatile components of two sections. d) Fig. 2-D shows a measuring arrangement, with the partial segments of a peripheral body segment can be measured when additional single electrodes 14a are mounted between peripheral and central electrode pairs. The illustrated measurement segment V is used to measure the entire segment, the illustrated measurement segment V 'serves for the measurement of the proximal part and the segment with the hatched line of the measurement of the peripheral body segment.
    In all the illustrations in FIG. 2, in the sense of the invention, alternatively, only one measuring path is ever enabled by the voltage changeover switch 10, and the feed is always advantageously carried out only in the segment which is being examined. All other segments are replaced by the additional switching devices 7 and Power switch 3 switched off.
    Thus, with a minimum of current switching, any body segment can be measured for both impedance and change in impedance with the heartbeat. It will also be apparent to one of ordinary skill in the art that only a fraction of the possible alternatives offered by this switching system are shown, and the application is not limited to the power and voltage circuits shown in the drawings.
    The essence of the impedance measurements of the device 2 is that of all the combined electrode regions 1, only the maximum of one combined electrode region, both the current electrode 8 for current injection and the measuring electrode 14 is used for voltage measurement. In all other united electrode regions, either only one of the two electrodes 8, 14 or none of the two electrodes 8, 14 is used.
    As far as the realization of the electrodes 8, 14 is concerned, it is advantageous for handling if at least some of them are designed as suction electrodes, clamping electrodes adhesive electrodes, band electrodes, sleeve electrodes or pressure sleeve electrodes. These can be configured as sputter electrodes, band electrodes or even double-band electrodes, wherein it has proved to be favorable in the case of double-band electrodes if they are not implemented in parallel but at different angles to one another. The electrodes, especially the adhesive electrodes, which are typically disposable electrodes, may also be used to be identified by, for example, RFID or other means. This makes it possible in terms of accuracy of the measurement results to allow only electrodes for use, with which the device was originally calibrated and in which therefore the necessary corresponding quality and configuration is guaranteed.
    In summary, the device 2 of the invention allows an impedance measurement of body segments at multiple frequencies, if appropriate, using a Cole-Cole plot, for the determination of intracellular water (or muscle mass and fat mass) and extracellular water, further the impedance measurement with division of the body in its different segments, eg Arms and legs (or even segments of the arms and legs), in the trunk and its parts, namely the thorax and abdomen (as they have a very different composition and thus different specific resistances). This is possible using as few feeder lines 5 to the body and as few electrodes 8, 14 on the body of the living organism 6. The present device 2 may employ the so-called 4-point method with external or adjacent current electrodes 8 and internal or adjacent measuring electrodes 14.
    The united electrode regions 1 are provided for attachment to different body parts, so that a distinction can be made between peripheral electrode regions (at the ends of the extremities of living bodies) and central electrode regions (lying on the trunk, neck, head region).
    Peripheral joint electrode regions are applied to: a) Fingers, hands, forearms for current injection and voltage measurement (eg supply of finger, hand or hand and forearm to measure the voltage on the left and right upper extremities b) Toes, feet, lower legs for power supply resp Feet and lower legs to measure the tension on the left and right lower limbs.
    Central united electrode regions are applied to: c) head, neck, upper thorax for current supply or voltage measurement. In this area, possibly only one electrode is sufficient for voltage measurement. d) Lower thorax for current supply and voltage measurement, in which area possibly only electrodes are sufficient for the voltage measurement.
    Other regions of the body that can be subjected to a similar measurement approach, e.g. also localized body regions, such as parts of the skull, neck, chest, abdomen, or breast, may also be selected for attachment of unified electrode regions.
    From the above descriptions, it is clear how complex and diverse the device 2 is built and functioning. Therefore, the design of the power switch 3 and voltage switch 10 has proven itself as a multiplexer. The use of an FPGA for circuit design also brings a great deal of simplification. In order to integrate a multi-channel ECG into the measurements, the CPU 23 must have a large computing capacity and therefore be designed as a fast processor, whereby the data memories also have to be sufficiently large and fast. To visualize the measurement results, a large screen should be available to display the numerous synchronized data and curves. Interfaces to existing physician systems may also be provided. The data should be used for scientific analysis in appropriate data formats, e.g. Excel, or other database formats are provided. A data memory has proven very useful, with the aid of which over the course of time a change in the body composition, body functions and also the changes of the ECG for the individual patient is registered numerically and / or graphically and graphically output. For example, empirical formulas based on standard gold methods (such as echocardiography, biochemical parameters such as NTpro-BNP or its derivatives or other biochemical parameters that alter heart failure, ergometry, spiroergometry, thresholds of oxygen uptake, lactate measurement, adhesion) may be used. Brachial Index, arteriography, whole body DXA, deuterium and sodium bromide determination) for the detection of body functions and composition, such as Cardiac output, fiber distension of the heart, maximum performance, thresholds thereof, arterial and venous perfusion, muscle mass, fat mass, whole body water, extracellular space, and their deviations from normal, by adjusting the above parameters e.g. using multiple regression equations, which may contain anthropometric data and all impedance data, can be estimated using standard gold methods. For the determination of over- or underhydrogenation or also of sarcopenia the calculation of the deviation of TBW or ECW or ICW or ECW / ICW ratio from the one between FM / kg body weight and TBW / kg body weight or ECW / kg proves itself Body weight or ECW / ICW in healthy individuals. For the determination of sarcopenia, especially the output of the "appendicular muscle mass", as it is internationally standard, that is the muscle mass of the shoulder and arms on the one hand, respectively of the hip and legs on the other hand, and how they are excellently detected by the segmental impedance spectroscopy can be. The correction of the mathematically determined muscle mass by means of the correction for a possibly disturbed ratio (eg quotient) between extracellular space on the one hand and intracellular space or whole body water on the other hand has also proven successful. Thus, the presence of a sarcopenia and the grading of the same compared to a standard collective can be spent.
    Of particular interest is also the output and / or graphical representation of the time course of the determined parameters, not only after individual interventions such as e.g. Ergometry, pacemaker adjustments, pharmacological and physiological interventions, not only in a single examination, but especially in repeated investigations at longer intervals. Here, for example, only time courses can be selected automatically in which the measured or calculated parameters have changed significantly and clinically relevant since the last recording. For example, changes in parameters that result from the known standard range, such as the PQ time, the formation of an AV block, the QT duration above or below the frequency-adapted standard range, ST lowering or raising beyond the known standard range, changes in the cardiac vector, Amplutude and direction of the T
    Wave, sudden changes of the heart rate, the sympathicovagal balance, the power of the 0.1 and 0.3 Hz band, or from the ratio of the 0.1 and 0.3 Hz band of heart rate variability, suddenly calculates differences between the segments, the volume wave in the legs or increases in the ECF / ICF or ECF / TBW ratios in individual body segments etc .. Thus, confusing history printouts are prevented.
    权利要求:
    Claims (26)
    [1]
    claims:
    Device (2) for impedance measurement on segments of a human or animal body, wherein the impedance measurement is preferably a multi-frequency impedance measurement, the device (2) a current source (4), current switch (3), to segments of the human or animal body (6) disposable current electrodes (8), voltage switches (10) and measuring electrodes (14), each output of the current source (4) being connected to an input of a current switch (3), each current switch (3) having a plurality of outputs and the input of the respective current switch (3) switchable with one of its outputs is interconnected, wherein the outputs of the power switch (3) with electrical feed lines (5) of the current electrodes (8) are connected, wherein the measuring electrodes (14) detect voltage signals and the Device (2) from the current supplied by the current source (4) and the detected voltage signals, the impedances of the segments of Human or animal body (6), characterized in that in the feed lines (5) near or directly to the current electrodes (8) switching devices (7) are installed, with which the current electrodes (8) with their feed lines (5) connectable and are separable from them, wherein the device (2) is configured to connect only two current electrodes (8) to the current source (4) by switching the current switch (3) and the switching devices (7) and all other current electrodes (8 ) by switching the switching device (7) from the feed line (5) to separate and the feed line (5) by switching the power switch (3) from the power source (4).
    [2]
    2. Apparatus according to claim 1, characterized in that close to or directly to the measuring electrodes (14) voltage amplifier (9) or voltage follower with a high input resistance (9) in the signal lines (19) are inserted.
    [3]
    3. Apparatus according to claim 1 or 2, characterized in that the switching devices (7) of the device (2) are switchable.
    [4]
    4. Device according to one of claims 1 to 3, characterized in that signal lines (19) of the measuring electrodes (14) are guided to inputs of Spannungsumschaltem (10), wherein the voltage switch (10) each having an output which is connected to an input of the Voltage switch (10) is interconnectable.
    [5]
    5. The device according to claim 4, characterized in that the outputs of the voltage switch (10) are connected to inputs of a differential amplifier (11) which determines from the voltage signals applied to its inputs a differential voltage (Udiff), the device (2) for uses the impedance detection.
    [6]
    6. Device according to one of the preceding claims, characterized in that the current switch (3) and / or the voltage changeover switch (10) are designed as relays or multiplexers.
    [7]
    7. Device according to one of the preceding claims, characterized in that at least one of the current electrodes (8) or an additional electrode (8a) via a resistor (12) can be acted upon with a compensating current, wherein the connection of the resistor (12) to the current electrode (8) between the switching device (7) and the current electrode (8) is arranged.
    [8]
    8. Device according to one of the preceding claims, characterized in that a compensating current electrode (8a) is provided which can be acted upon via a resistor (12a) with a compensating current.
    [9]
    9. Device according to one of the preceding claims, characterized in that in each case a current electrode (8) and a measuring electrode (14) to a unified electrode region (1) are grouped.
    [10]
    10. The device according to claim 9, characterized in that the current electrode (8) and the measuring electrode (14) of the unified electrode region (1) jointly guided cable as a feed line (5) and signal line (19).
    [11]
    11. The device according to claim 9 or 10, characterized in that the current electrode (8) and the measuring electrode (14) are arranged on a common electrode carrier.
    [12]
    12. The device according to claim 9 to 11, characterized in that the power supply always with two current electrodes (8), which are each grouped on a unified electrode region (1), takes place, that for the voltage measurement, however, only a maximum of one measuring electrode (14) which is located on one of the two united electrode regions (1) is used.
    [13]
    13. Device according to one of claims 9 to 12, characterized in that the device (2) interconnects the current electrode (8) with the current source (4) only from a maximum of one united electrode region (1) and uses the measuring electrode (14) for voltage measurement ,
    [14]
    14. Device according to one of claims 8 to 13, characterized in that unified electrode regions (1) are selectable for attachment to peripheral body segments and central body segments, wherein preferably a further unified electrode region (1) is selectable for attachment to a body region, at which the chest wall electrodes V1 to V6, preferably V4 to V6, of an ECG are placed.
    [15]
    15. Device according to one of claims 11 to 14, characterized in that the common electrode carrier is a clamp, band, sleeve or pressure cuff.
    [16]
    16. The apparatus according to claim 15, characterized in that a pressure sensor for pulse measurement is arranged on the common electrode carrier.
    [17]
    17. The apparatus according to claim 16, characterized in that the pressure sensor comprises a liquid-filled bubble which communicates with a pressure transducer, wherein preferably the liquid-filled bubble can be pressed against a body part by means of a controlled, hydraulic or electromotive pressing device.
    [18]
    18. Device according to one of the preceding claims, characterized in that it determines the impedance and a change of impedance with the heartbeat in at least two segments, wherein the segments are defined by a) with respect to the feed on the one hand by two at a central (Z) Body part and a peripheral (P) body part can be applied united electrode regions (1), and with respect to the voltage measurement by a at the central (Z) body part can be applied unified unified electrode region (1) and a centrally located single electrode (20); b) on the other hand with respect to the current feed by two unified electrode regions (1) which can be applied to peripheral (P) body parts and with respect to the voltage measurement by the peripheral (P) combined electrode region (1) and a central measuring electrode, either as a single electrode (20) or as a measuring electrode ( 14) of a central (Z) united electrode region; wherein c) as an alternative to b) the second body segment is also defined in terms of current injection by a central (Z) and a peripheral united electrode region (1) and with respect to voltage measurement by two peripheral (P) unified electrode regions, one of which does not flow through the current is.
    [19]
    19. Device according to one of the preceding claims, characterized in that a differentiator is provided for determining the change of impedance with the heartbeat.
    [20]
    20. Device according to one of the preceding claims, characterized in that an ECG device (21) in the device (2) is integrated, wherein the ECG device (21) comprises at least limb electrodes, preferably also chest wall electrodes.
    [21]
    21. The device according to claim 20, characterized in that the measuring electrodes (14) are designed as ECG electrodes by branch lines (22) of the signal lines (19) of the measuring electrodes (14) are guided to the ECG device (21).
    [22]
    22. Device according to one of the preceding claims, characterized in that the current electrodes (8) and / or the measuring electrodes (14) as Meßgrößenaufnehmer / encoder (17, 17a) for physical quantities, in particular acceleration values, pressure, sound, temperature or light, are formed.
    [23]
    23. Device according to one of the preceding claims, characterized in that at least some of the current electrodes (8) and the measuring electrodes (14) are formed as suction electrodes or adhesive electrodes.
    [24]
    24. Device according to one of the preceding claims, characterized in that it comprises a CPU (23) by means of multiple regression equations or mathematical models parameters for body functions and composition, such as cardiac output, biochemical parameters thereof, for the maximum physical power, for the aerobic and anaerobic thresholds, for the blood circulation of the body parts, for arterial and venous function, eg the ankle-brachial index, arterial and venous thromboses, arterial embolisms, the body compartments, whole body water, extracellular space, muscle mass, fat mass, ratio of extracellular space to intracellular space or whole body water in the whole body and the individual body parts and all their deviations from the norm.
    [25]
    25. Device according to one of the preceding claims, characterized in that it outputs graphically and / or digital time courses of the measured or calculated parameters of time differently performed measurements.
    [26]
    26. The device according to claim 25, characterized in that it compares the measured and calculated parameters with the parameters carried out at a different time and only outputs time profiles from the parameters if the parameters have changed significantly and clinically relevant over the course of time.
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    同族专利:
    公开号 | 公开日
    WO2016168873A1|2016-10-27|
    US10709350B2|2020-07-14|
    EP3285643A1|2018-02-28|
    US20180153432A1|2018-06-07|
    AT516499B1|2016-06-15|
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    ATA50317/2015A|AT516499B1|2015-04-22|2015-04-22|Body impedance meter|ATA50317/2015A| AT516499B1|2015-04-22|2015-04-22|Body impedance meter|
    PCT/AT2016/050054| WO2016168873A1|2015-04-22|2016-03-10|Body impedance measuring device|
    EP16711509.6A| EP3285643A1|2015-04-22|2016-03-10|Body impedance measuring device|
    US15/568,333| US10709350B2|2015-04-22|2016-03-10|Body impedance measuring device|
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