DE2348582A1 - DEVICE AND METHOD FOR REPRESENTING DATA IN THE FORM OF A VECTOR ENVELOPE - Google Patents

Description

Dt-In ₅ . Wilhelm Reiche!

pL-lng- Woligg

6 Fraakiuü a. M. I.
Pcuksirasse 13

7650 -

General Electric Company, Soheneotady, H ".Y., 7StA.

Apparatus and method for representing data in the form of a vector envelope

The invention relates to an apparatus and a method for Presentation of physiological data in the form of a vector envelope, which allows a quick and precise interpretation and it allows the necessary therapeutic steps to be carried out as quickly as possible.

In the known devices for monitoring physiological data, sensors are used that generate signals that on any way with a group of measured physiological parameters, e.g. from pulse rate, blood pressure, premature Ventricular contractions per minute, blood pH, breathing rate, partial pressure of blood gases and from others Sizes are composed, are linked. This data is usually recorded on several measuring instruments, such as dial instruments, digital instruments and analog oscillographs. Here is the time required for interpretation

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proportional to the number of parameters displayed. Since it is desirable in clinical operations to be as much physiological as possible Obtaining information and being able to constantly estimate the physiological data as it changes is satisfactory the known devices do not.

In the book by H.S. "Wolf, Biomedical Engineering, World University Library, McGraw-Hill, New York, 1970, it was proposed multiple physiological parameters on just one oscilloscope screen display in polar representation. According to this idea, individual physiological parameters, each with a special, constant polar angle shown as radial vectors, the length of which modulates proportionally to changes in the parameter values will. It has also been proposed to connect the tips of the vectors by means of an envelope, this envelope should assume a circular shape if the parameters correspond to their normal values, and where the envelope has the shape of any should assume another closed curve as soon as one or more parameter values deviate from their normal value. The idea that a circular shape can be recognized quickly and interpreted as a normal situation plays a role in this idea can, and that deviations from the circular shape are recognized just as quickly and with regard to the degree of deviations and the Influences among each other can be interpreted.

Before the present invention was made, the per se promising concept was the presentation of physiological data in the form of a vector envelope cannot be used as a clinical device. The problem that the so-called normal physiological parameters represent mean values for a healthy population and for sick patients who e.g. are under intensive care or have severe surgical procedures Having injuries or myocardial infarctions do not represent meaningful comparative values. There was also a problem although it is not difficult to keep the length of the vectors proportional modulate to change the physiological parameters,

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obtain noticeable changes in vectors or parameters with large amounts when the percentage changes the monitored parameters are relatively small. So until now there has been reasonable sensitivity in displaying changes the parameter has not yet been reached.

In addition, the problem was a representation with zero point suppression not yet solved, i.e. it was not possible to get the vectors from a non-zero origin to radiate outwards and thus the Hatred to enlarge the parameter so that part of the parameter value is the entire length of a normalized vector occupies and thereby the representation of small changes is improved.

In addition, no possibility has yet been created to selectively move vectors from the outer boundary to the origin or from To number the origin towards the outer border and thereby the changes with regard to some physiological clinical pictures to reinforce the enveloping. In addition, no method has yet been specified by means of the upper and lower limits of the range the parameters are shown in the representation of the vector envelope in order to enable visual determination, whether a parameter is within specified limits. Likewise, there was no warning device, which would indicate when the corresponding limit was exceeded Responds to the boundaries of the range.

Overall, a satisfactory method of representation was missing several different, possibly comparable at the same time '.: änderlicher physiological data in the form of a vector Eini \ _-': enveloping on a oscilloscope or as output of a **: output _printer!.

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In the following, exemplary embodiments of the invention are described in more detail with reference to the drawing.

Fig. 1 shows a front view of an oscilloscope whose screen physiological data is presented in the form of a vector envelope;

Fig. 2 shows a block diagram of a device for generating a representation of the vector envelope;

Figures 3 through 5 show some vector envelopes used under certain Requirements appear on the oscilloscope display of FIG. 1 or on another output device;

Fig. 6 shows a square pulse and further pulses that are chronologically related to the square pulse, which facilitate explaining the generation of the vector envelopes;

Fig. 7 shows a step-shaped analog voltage and a sawtooth voltage which is the integral of the step-shaped Represents analog voltage and indicates a voltage that satisfies the algorithm and boundary conditions;

Figures 8 and 9 illustrate specific vector envelopes based on the particular characteristics of which of this invention are illustrated;

10 shows a further circuit arrangement for signal processing to carry out the algorithm;

FIG. 11 shows a voltage curve analogous to FIG. 7 with gradual transitions between the individual voltage levels, as they are in the circuit shown in FIG.

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arrangement are generated; ₃

Fig. 12 shows a block diagram for generating the corresponding Reference curves in the representation of the. Vector envelopes;

FIG. 13 shows the course of the output signals of the in FIG circuit shown;

14 shows the curves provided with arrows Sequence in which the reference curves in the device for representing a vector envelope to be discribed;

Fig. 15 shows a modified embodiment of the circuit arrangement shown in Fig. 2 for generating the inverted vector envelopes;

16 shows a diagram on the basis of which the generation of a vector envelope by means of a computer is explained will;

Fig. 17 shows a vector envelope for explaining some aspects of computer operations.

Figure 1 provides an overview of the invention it shows a front view of a schematically illustrated oscilloscope 20, which is within the scope of this invention a magnetic or electrostatic Own distraction system '. An oscilloscope is an example of an arrangement that is time-varying Provides representation, which is referred to below as a soft image: The oscilloscope 20 can, for example, a phosphorescent Own screen 21. A vector envelope 22 is shown on the screen, which has circular shapes and thus -

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indicates that all physiological data have just been normalized, or that the measurement subject's conditions are stable. The vector envelope 22 is written on the screen with the electron beam of the oscilloscope 20. An oscilloscope is an example of an arrangement that provides a real-time or a time-varying representation, hereinafter referred to as soft figure is called. Instead of an oscilloscope, other devices, such as fast printers, chart recorders can be used to put the result on permanent media, such as paper, printouts and a hard illustration deliver designated representation.

From the origin of the representation of the vector envelope 22, eight reference curves 1 to 8 run radially outwards. These Reference curves subdivide the normalized circle 22 in this example into eight equal partial areas, or octants. The reference curves can e.g. on the outer surface of the oscilloscope screen 21 or as a transparent mask in front of the screen, or they can be generated electronically with their intersection at the origin of the circle 22. Will the device display more or less than eight physiological parameters, the vector envelope or the normal circle is correspondingly more or less To subdivide sub-areas. '

In the radial direction there are upper and lower limit markings 23 and 24 outside or inside the circle 22, which are illuminated and written with the electron beam of the oscilloscope 20. A couple of these boundary markers For example, 1 to 8 can be on each reference curve, in which case each pair of boundary markers for a vector and the physiological parameters represented by it apply. The boundary markings can be electronic in the radial direction Way to be shifted inward or outward, accordingly

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the permissible or desired limits of the corresponding physiological parameter.

The radial distance at which the circle 22 intersects the reference curves reflects the value of the physiological parameters represented by the vectors. In the example shown in FIG. 1, eight parameters are measured. The designations attached to the reference curves have the following meanings. HR means pulse rate, MABP means mean value of arterial blood pressure, MVBP means mean value of venous blood pressure, CO means cardiac output, pO ₂ means blood oxygen partial pressure, pC0 ₂ means carbon dioxide partial pressure, RR means breathing speed and PVC means premature ventricular contractions per minute. These measured and displayed parameters are only examples, of course they can be replaced by various other parameters. In addition, the electronics that perform the display can be designed to display two to sixteen parameter values. Based on experience so far, eight parameter values can be interpreted quickly and correctly.

When monitoring a patient begins, the device will adjusted or normalized until a circular envelope 22 appears on the screen. In other words, too At the beginning, the parameter values represent a circular envelope that serves as a comparison curve. As soon as changes are made in the physiological parameters of the patient occur, the envelope shown changes its shape immediately. This change in Curve shape, i.e. the deformation of the envelope, tells the observer which parameters change to what extent to have. Typical vector envelopes, which are displayed after corresponding deviations of the parameter values from their normalized or initial values, are shown in FIGS. 3, 4 and 5.

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The oscilloscope 20 may also include a digital time display 25 which indicates the time at which the envelope was last nor was it normalized or circular, it may contain a further digital display device 26 which has been used since last normalization indicates the elapsed time.

It is an important aim of this invention to provide an algorithm to develop and use that allows normalized physiological data to be represented as circular vector envelopes and to indicate deviations from it in a clear way. The development of this algorithm will now be more precise because it provides a better understanding of the objects of this invention.

The vector envelope contains three basic pieces of information:

1. circular shape of the envelope,

2. Deviation from the circular shape of the envelope and

3. Degree of deviation from the circular shape.

The circular shape can be used as a correlation of physiological values can be used to indicate that the physiological parameters are at their normal values. The deviation from the circular shape gives the deviation from these normal values. The degree of deviation indicates a measure of the deviation from normal values. However provides a table of normal values of physiological parameters only averages of a statistically meaningful one Proportion of the population and does not need to be very meaningful with regard to a sick patient. So around To achieve a correlation, all scales of the vector parameters must be "normalized" in such a way that the physiological Normal values of the eight parameters chosen as an example are all the same Have vector magnitude from the origin and generate a circular vector envelope. Becomes a linear relationship between the vector length R (t) and the physiological parameter value P (t) are assumed, the normalization function can be

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Tuning with an even equation in which A and B are constants represent in the form

R (t) = A-P (t) + B ■ (1)

to be written. The boundary conditions for the normalization function are determined by the fact that R (t) = O when P (t) = 0, and that R (t) = R _n when P (t) = P _n , where P ^ is the physiological normal value for P. (t) and -'Rjj represent the normalized vector length for the normalized, circular vector envelope. In _{order to realize a circular vector envelope, R n} is the same for all eight parameters, P _n , on the other hand, has a different size for each parameter, t represents time, so P (t) and R (t) are functions of time.

If the boundary conditions in equation (1) are used, it follows:

A = R _n (2) and B = O (3) ⁵ S

When finally equations (2) and (3) are inserted in (1) the relationship follows

R (t) = R _w

r £ P (t) (4)

which represents the normalization function when correlating with the standard parameters.

A disadvantage of the normalization function according to equation (4) is that for a given change in the vector value P (t), the value R (t) changes only slightly (if R _N / P _{N is} small), so that the representations of the vector envelopes reacts relatively insensitive to a change in P (t).

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For the further course of consideration, the ■ deformation sensitivity is now defined as & R (t) / dP £ t).

Equation (4) gives the deformation sensitivity to dR (t) / dP (t) = R _N / P _N. For example, if P (t) represents the systolic blood pressure _{, if P n} = 120mm Hg and FL, = 5 cm, then the deformation sensitivity for this vector is dR (t) = R _M = 5 cm = 0.04 cm / mmHg (6 ) dP (t) - ■ 120 mmHg

For a change in systolic blood pressure of 10 mmHg, the vector length would change 0.4 cm, and that change the vector envelope would not deform enough to be perceived by the observer.

To solve this problem, the boundary conditions for equation (1) are redefined with regard to the deformation sensitivity. For the generalized normalization function the equation (1)

R (t) = A-P (t) + B

the boundary conditions, also called boundary values, read: P (t) = P _n , if E (t) = R _n

and dR (t) = K = deformation sensitivity dPTtT

If the boundary values are applied to equation (1), the result is

R (t) = K (P (t) - P _n ) + R _n , (8)

where K is the measured in vector units per parameter units Deformation sensitivity is,

P _{n represents} the normal value of the physiological parameter, and

R _{n is} the normalized vector length of the representation of the vector envelopes. / _> 0981 5/0840

The normalization function of equation (8) is equivalent to using a vector scale with zero point suppression. This means that the vectors can either be zero-point suppressed or not zero-point-suppressed, with the smallest number on the scale being greater or less than zero. Zero point suppression enables increased sensitivity to deformation. In addition, a scale numbering from the inside to the outside or from the outside to the inside is possible. However, equation (8) unrealistically assumes an absolute value of P ", since the physiological parameters of a sick patient cannot be correctly compared with the average values of the healthy population. In accordance with this invention, it is therefore desirable _{to be able to redefine P n} at any time during the monitoring process, ie to be able to set the normalized parameter value P _n equal to the actually present parameter value P (t) at any time. As a result, the vector envelope can be re-normalized to the circular shape, and relative changes in the parameters can thus be determined quickly and easily. The correlation algorithm thus has the form

R (t) = K (P (t) - P (T _n )) + R _n (9)

where K = deformation sensitivity
= P (t) on the normalization
= Normalized vector length.

= P (t) at the normalization times T "and

A device is provided in the device by means of which P (T _n ) can be redefined at any time and as often as desired.

Similarly, we'd use this algorithm on the boundary markings applied, as can be seen from the following equation:

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R _L (t) = K (L (t) - P (T _n )) + R _n (10)

where Ry (t) is the vector length of the boundary markers and L (t) represents the limit values.

Because it is necessary to have neighboring vectors with each other in order to generate a complete vector envelope, the envelope of the vectors and / or the limit values can be defined.

Let: R (t) = any one defined by equation (9)

vector

R ^ (t) = the vector following clockwise _{with respect to R n (t)}

A larger number of infinitesimal straight curve pieces connect the tips of the two vectors and form a curve. The amplitude of the curve is designated as E (O) depending on the angle between the two vector peaks. The value of R _n (^) decreases linearly from the value 1 to the value 0, while the angle Q increases from 0 ° to 45 °, provided that eight subranges or octants are present and eight parameters are to be measured. This behavior can be expressed by the relation R _n (t), / 45 ° - Θ ⁰ ). Similarly, the value of R _{n +} > j ("t) increases linearly from 0 to 1, while the angle β increases from θ ° to 45 °, as is expressed by the relationship R ₁ (t) / θ). The Equation for

'U ₅ ⁰ /

the envelope of the vectors and the limit values is given by the sum

C (Q) = R _n (t) / ~ 45 ° - Θ ⁰ 7 + R _{n + 1} Ct). _θ_ (11) L 45 ° J 45 °

delivered. The 45 ° angle is for a system of eight Identifying vectors or parameters. If n-vectors are displayed, where η = 4 to η = 16, the value must be 45 ° through the

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Angle 360 to be replaced,
η

In Fig. 2 is based on an embodiment, for example a Circuit arrangement shown, which is suitable for displaying a vector envelope on an oscilloscope screen.

In Fig. 2, a measurement sensor 30 for receiving the physiological information is shown schematically at the bottom left. This Measurement sensors can, for example, be a blood pressure meter or an electrocardiograph for heart rate measurements or a device for measuring the heart output or a similar device for Measurement of physiological parameters included. The measurement sensor 30 works on the functional unit 31, which in one embodiment This invention is used to store the binary representation of the measured parameters and limit values and by Trigger pulses that emit information to a data busbar 32.

The circuit arrangement shown in FIG. "2 processes accordingly Equation (9) analog or digital signals for modulating a deflection device, e.g. by an x-y oscillograph 20 is given. The corresponding equation (9) required signals can also be made with the help of a computer and for display on a line grid screen can be used.

In the circuit arrangement shown in Fig. 2 are of Functional units, such as the unit 31, derive binary signals for the physiological parameter values. With everyone Functional unit is connected to a manually operated device (not shown) for generating digital signals, e.g. fed. The limit signals can also be generated independently

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and are fed directly, i.e. not via the busbar, to their point of use within the circuit arrangement. In In the example under consideration, eight parameter values and two limit values for each parameter value are digitally coded. The previous one Processing of these signals will be discussed later. In order to be able to show how the algorithm that applies to equation (9) · is executed and the information is displayed, it is currently assumed that the parameter values and the limit values can be entered into a RAM memory 33 located in the center of FIG. The limit values L (t) only change on command. The time-varying parameter values P (t) change as a result of physiological changes.

In a further RAM memory 34, only the parameter values P (t) are entered and stored _{during the normalization times or the starting time T n.} This writing process only takes place when a command decoder 35 is operated manually. As already mentioned, normalization or resetting to the initial value has the consequence that the vector envelope 22 'assumes a circular shape. The parameter values written into the RAM memory 34 at the times T _n remain there until a new normalization takes place. This makes it possible to subtract the normalized values P (T _n ) from the time-variable parameter values P (t) or limit values L (t) so that changes in the vector can be represented in an enveloping manner. T _n appears as renunciation time on the display panel 25 in FIG. 1 and allows the operating personnel to indicate the rate of change of the parameters from the deformation of the vector envelopes taking place during a predetermined time.

The eight time-variable parameter values P (t) and the sixteen limit values L (t) are simultaneously forwarded from the RAM 33 to a binary adder 36, which also receives the stored initial values of the parameters P (T _n ) from the

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RAM memory 34 are supplied. The RAIi memory 34 operates according to the number of lower limit values, the normal values and the upper limit values, at three times the clock speed of the RAM memory 33. A complete adder is used to convert the binary P (T _n ) values from the binary Subtract P (t) and L (t) values. The adder 36 constantly receives data from the RAM memory 33 in a chronologically correct sequence. The adder therefore constantly subtracts P (T _n ) from P (t) and L (t). The parameter values written into the RAM memory 33 can change over time, while the adder requires a finite time to carry out the subtraction. It is therefore necessary, when reading out from the adder 36, to ensure that the parameter values and the limit values are read out if they do not change, and also to ensure that these values are read out in the correct order for the electron beam writing in the oscilloscope 20 or to control a corresponding recording device from octant to octant in a repeatable order. A synchronization circuit 37 is used for this purpose. The synchronization circuit is controlled by the RAM 33 synchronously. In the embodiment shown, the reading and writing is carried out with a clock signal of the frequency 8.192 KHz 38, the period duration of which is 122 microseconds, as shown in FIG. Reading always takes place during the first half of a clock signal. At the beginning of the read cycle, a short pulse 39 with a pulse duration of about one microsecond is generated by a circuit which is not shown. No information is read into the RAM 33 at this point in time. The read start pulse 39 only resets the synchronization circuit 37 and causes the currently existing value of P (t) - P (T _n ) for a parameter to be read at the onset of the leading edge of the pulse ". During the next read cycle, the values following the adder supplied parameters

L 0 9 R 1 5/0 8 4 0

(t) and P (T _{n + 1} ) are read into the synchronization circuit 37. This process continues until all eight values P (t) P (T _n ) have been read. This process is then repeated for the limit values. The sequence followed in this example is: lower limit values, normal values and upper limit values. As will be explained in more detail below, the limit markings are the result of selective masking.

The digital signals, which represent the parameters and limit values read one after the other, are sent to a digital-to-analog converter supplied, which emits an analog signal at its output 41. The analog signal is of the general type indicated at 42 in FIG Shape. Each voltage level in the voltage curve 42 corresponds a parameter and the corresponding limit value at the time of the readout process, in which the factor K and R ^ of the algorithm have already been introduced, as will be explained in more detail.

The analog signals are fed to an operational amplifier 43 in which each parameter and its corresponding limit values are multiplied by one and the same deformation sensitivity factor K. A switching device 44 is used for this. The switching device is clocked with binary pulses resulting from an addition of signals with the frequency of 1.2 kHz and 4 kHz and generated in a timer circuit 46 in such a way that a single binary number for each parameter and its corresponding limit values is given. In this way, resistors are switched into the input of the operational amplifier 43 in a certain order, which change the input resistance and thus the gain for each parameter. The output of the operational amplifier 43 is therefore given by K (P (t) ■ - P (T _n )).

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The output signals of the operational amplifier are fed to a summing amplifier 47. With an adjustable voltage source 48, the diameter of the circular initial envelope is set at the time of a normalization process and normally does not need to be changed any longer. In amplifier 47, R _{n is} added and the vector length is normalized, so that the addition of K (P (t) - P (T _n )) to each vector at the time of normalization also generates a circle "if the zero point of the vectors is suppressed or their scales are expanded by the K-factor.

The analog output signal K (P (t) - P (T _n )) +% ^d © s amplifier 47 and the limit values K (L (t) - ^p ( ^T jj)) ⁺ Rjj of all parameter values and limit values is indicated by the ¹ in Fig. 7 with 42 designated step-shaped voltage signal given. If this discontinuous voltage function were used to control the oscilloscope 20 or another recording device, the representation of the vector envelopes would be meaningless. In order to obtain a meaningful representation, a sawtooth curve (denoted by 50 in FIG. 7) is required, which is obtained by integrating the step-shaped voltage curve. A conventional first order integrator 51 is used for this purpose. The integrator 51 has two inputs 52 and 53. A sampling memory 54 is located in one of the input connections of the integrator to store a group of 24 signals and to feed the existing group together with the previous group to the integrator 51. The new or currently existing group ″ is shown in FIG. 7 by the voltage curve 42. The old or stored group is characterized in FIG The integrator 51 integrates the

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Curves 5δ and 52 simultaneously, i.e. it integrates in each case starting from the old value up to the new value and connects the values with straight lines, like the curve 50 of Fig. 7 shows. The integrator causes the vectors to be connected to one another by an envelope, as in FIG Equation (11) is given.

The integrated signal is fed to a limiting amplifier 60,

shown in Fig. 2, supplied. This amplifier limits the peak values of the curve 50 and prevents them become negative or exceptionally positive. Its effect on the representation of the vector envelope can be the 4, in which the tip 70 of the vector envelope 22 is in the octant intended for the heartbeat (HR) is flattened. This flattening would occur when the heartbeat is significantly above the upper limit, because in In this case, the peak value of the voltage curve is limited by the limiting amplifier. Without this limitation it would the flattened area 70 degenerates into a point and the observer would have no way of determining whether this The peak of the envelope would be limited by the limit of the dynamic range of the amplifier or whether this peak actually did indicates the heartbeat. In the same way, it is not "desirable" for parameters to take on negative values, and thereby themselves the vector envelope is deformed through its origin and leads to misinterpretations. Hence are negative values of the parameters are not permitted, see area 71 in FIG. 4, such values are limited to 0 and will be not negative.

The integrated voltage waveform 50 of FIG. 7 becomes two multipliers 61 and 62, one with χ and one with y have designated output, via which the oscilloscope or an analog recording device deflection signals to the deflection circuits are fed. In addition, the cultural

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Zierer 61 and 62 still have a sinusoidal signal and a cosine signal Signal input from generators $ 6 and $ 63. In practical embodiments, these are generators very stable and are synchronized by clock pulses from a suitable clock source. The sinusoidal and cosinusoidal The well-known Lissajo figures on the oscilloscope call for tension 20 when no further signals are supplied by the limiting amplifier 60. As soon as a physiological one The signal characterizing the parameter vector and the corresponding limit values are present, the envelope is disturbed depending on the parameter value, and those shown in FIGS. 3, 4 and 5 then arise Curves.

Has the algorithm described voltage waveform corners, such as in the voltage waveform 50 of Figure 7 _f -. Then the vector length changed and generated each time the envelope crosses a reference line, a corner in the course of the envelope. This means that the envelope and also the boundary markings do not necessarily have to intersect the reference lines at right angles. The cutting angle depends on the previous and following values on the reference lines. An example of a corner in the course of the envelope is shown in FIG. 8, in which the boundary markings are entered and the corner is denoted by 72. Using a different method, the boundary markings can be generated as straight lines and the envelope can be made to intersect each reference line at right angles. A corner 72 in FIG. 8 is then smoothed and intersects the reference line at right angles, as shown in FIG.

The condition for the vector envelope to be the reference lines intersects at right angles is given by the following equation. The individual terms of the equation are entered in FIG.

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C (θ) = R _n (t) Cos 2Θ + R _{n + 1} Ct) - Sin 2Θ (12)

Herein, C (θ) = any one point of the envelope

between R _n (^) and ^ η + 1 ^^ * Compare also equation (12). R _n (t) = the n-th vector, given by equation (9) and represented by curve 42 in FIG. 7.

Cos 2Θ = amount of the cosine function Sin 2Θ = amount of the sine function 2Θ = twice the angular frequency.

Equation (12) is implemented in the circuit arrangement shown in FIG. This circuit arrangement does not use the first-order integrator shown in FIG. Rather, the value R _n (^), corresponding to FIG. These multipliers are known, analog 4-quadrant multipliers. In the multiplier 79, R _n (^) is multiplied by JCos 20 {, where 2θ represents twice the angular frequency of the signals input into the multipliers 61 and 62 for generating the Lissajo figures. R _{n +} -J (^) is multiplied by sin 2Θ in multiplier 80. The output signals of the two multipliers 79 and 80 are added up at the connection point 81, which represents the input connection for the limiter amplifier 60. The output signal of the amplifier 60 is multiplied by sine and cose in the multipliers 61 and 62 and the resulting output voltages of the multipliers 61 and 62, which are phase-shifted by 90, are used to control the oscilloscope or any other recording device. The curve of the algorithm voltage at the summation point 81 and the curve of the output voltage of the amplifier 60 both have, compared with the kink transitions of the algorithm voltage

50 _x gradual transitions, as in the voltage curve 82 in FIG. 11

!, 0 9 8 1 S / 0 8 k 0

is shown.

As already mentioned, various methods can be used, to get an analog or digital representation of physiological parameter values and their upper and lower limit values, which can be used to execute the algorithm given in equation (9). In the embodiment described, these were Values first in a RAM memory 33 of the Pig. 2 registered. A method for generating this will now be based on FIG Signals are given. For those skilled in the art of digital and analog circuit technology, there are more Production methods obvious.

In the circuit arrangement shown in FIG. 2, all work steps are in fixed temporal relationships with one another executed, clock pulses are therefore required in the circuit arrangement for timing control. These clock pulses are on data bus 32 and at various other locations in the assembly. In a commercially built version the clock pulses are generated by a clock generator (not shown) every 0.25 seconds. A defined time interval after each clock pulse, the functional units 31 automatically output the digitally coded data or limit values in a predetermined manner Sequence to the data busbar. Some of the measured value sensors 30 and the functional units 31 are at certain times not switched on, they do not generate any data and the part of the vector envelope assigned to them is missing. on the way in which the absence of a vector is indicated in the vector diagram will be explained later. The pulses from the busbar contain e.g. command signals, pulses to control the curve shapes, vector pulses, etc., in the correct order. Every The circuit device has a pulse decoder which selects the correct information for this circuit device and does not pick up the rest of the information. This procedure is

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known in the field of data processing.

In the circuit arrangement shown, the existing ones appear Parameter values every quarter of a second and limit values every two seconds. Because of the size of the data, the parameters values divided into two words, which are given in two data blocks that follow each other with an interval of two milliseconds. A word has eight bits for the parameter status, the parameter value, the limit values, command signals, alarm signals, etc. One block has 16 words with 8 bits each, each word has an address.

In the lower left part of FIG. 2, three storage units 90 to 92 are shown. The storage unit 90 receives the first word of the parameter data after receiving a command signal and the storage unit 92 receives the other half of the parameter data after a corresponding command signal. While the storage unit 92 is recording its data, the data of the storage unit 90 are transferred to the storage unit 91. This procedure avoids problems in the processing of the time-shifted data in the RAM memories 33 and 34. The data of the storage units 91 and 92 are accessible to the RAM memory, but they are only written into this memory when a gate circuit 93 is open. The individual groups of the eight lower limit values, eight parameter values and eight upper limit values all have individual addresses, whereby they are written into the RAM memory in an orderly and predetermined order, regardless of the order in which these data are available. The reading unit 37 can therefore be prompted with a reading start pulse 39 to _{read out the parameters and limit values P (t) -P (T W} ) in a repeatable sequence.

Since the writing of "information in the RAH memory 33 destroys the previously existing data corresponding addresses, it is unfavorable to enter the RAM memory 33 during a read process also to enroll. Because of this, the clock pulse is for everyone

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Vector of the vector envelope as shown in Fig. 6 is divided into a reading interval and a writing interval. The frequency of the square-wave pulse shown in FIG. 6 is 8.192 kHz or 122 microseconds in the commercially manufactured version. Starting with the reading start pulse 39, half a period of the rectangular pulse is available for reading for each octant, starting with a three microsecond writing start pulse 94, the remaining half of the remaining pulse is available for writing for the corresponding octant, with the writing start pulse 94 appearing as soon as the RAM memory and the adders are ready to be controlled again. Read and write start pulses are generated in the timer circuit 46 as well as the clock pulse. The arrival of a read start pulse 39 causes the reading unit 37 to read all lower limit values at intervals of 122 microseconds, then to read the parameter values in the same way and finally to read the upper limit values. This reading process only takes place, however, when no data is being written into the RAM memory 33, so that only stable and valid data are taken from the adder 36 during the reading process.

In the upper left part of FIG. 2 there are two comparators 95 and 96. A comparator 95 compares one address with the limit value addresses of the busbar 32, the other comparator compares a timer address with a data address of the parameters on bus 32. These comparators are used by a ROM address memory 107 which only selects the parameters and limit values that can be used for display. If the Limit values with the data addresses of the parameter values in the ROM address memory 107 matches, the limit values are transferred via line 37 and the parameter values via line 98 to the RAM memory 33 written, provided that read start pulses open the gate circuit 93 have opened. Since the address on the busbar does not necessarily match the address of the vector position, a rearrangement must be carried out. This rearrangement

/, 09815/08 ^ 0

is carried out in the code converter 99. If the code converter 99 perceives a parameter, such as the lower limit of the mean arterial blood pressure (MABP), which is in the second octant the vector display is on the oscilloscope screen, but can be given on the busbar by the 33rd parameter, the code converter 99 thus generates a signal which corresponds to address 2 in the RAM memory 33, so that the parameter value at open gate 93 can be registered.

In addition, there is a two-to-one in the circuit arrangement Multiplexer 101 containing an electronic switch that allows reading and writing almost simultaneously. The multiplexer 101 switches continuously with a cycle amounting to approximately 8 kHz switch between reading and writing. Write start pulses can occur at any time. If, for example, the heartbeat changes or the blood pressure, a write start pulse occurs and new data is written into the RAM 33. As soon as there is new data on the busbar, the gate 93 is opened and a write start pulse is generated. The timer circuit 46 generates a sequence of read pulses which, together with the data from the code converter 99, provide the correct address for the in represent data inputted to the RAM 33.

The other RAM memory 34 stores the parameter values only at time T _n , that is, when normalization of the vector envelope is required. It should be remembered once again that normalization of the representation means that the parameter values present at the moment of normalization should form a circular vector envelope which is deformed by subsequent changes in the parameter values. The P (T _n ) - "values are stored in RAM memory 34 and are supplied to adder 36 until new values are available for renewed normalization. As long as there is no command for renewed normalization, the parameter values are passed through the gate circuit 103 prevented from reaching the RAM memory 34. The gate circuit is controlled by a standard

L, 0-9 8 1 5/0840

mation command opened., so that the values over the line 98 can be given into the RAM memory 34 and by means of a time-synchronously operating code converter 102 to their correct address.

In addition, there is also a reset circuit 104 in the circuit arrangement of FIG Emptying the RAM memory 33 during the time in which normalization or re-normalization or the measurements are being started. Located does not contain a parameter value in a special address this address is invalid data. The RAM memory must be emptied manually. The reset circuit works with three electronic switches 105, 109 and 123 together and grounds thus the input lines of the RAM memories 33 and 34, the RAM memories are coupled during the write process and emptied these memories while all RAM addresses are traversed and new data apply to both RAM memories 33 and 34 during the normalization time. This step only takes a fraction of the normalization time.

In the circuit arrangement of FIG. 2 there is also a monitoring device 110 provided for the vectors. Is that missing Parameters for one or more octants of the display, it makes sense to show this fact to the observer. If, for example, as shown in Fig. 5, the vector of the 5th and 6th octant is missing, this is indicated by the dashed line Curve section 111 is displayed. If all non-existent parameters have been determined, the monitoring device gives 110, which contains an AND element, a pulse that is stored in the memory 112 is stored and fed to a further AND element 113 will. A relatively high frequency is applied to a second input 114 of this AND element, so that when the memory 112 is synchronous is controlled with the vector-free octant, the output signal of the AND gate 113, the oscilloscope beam with the at the input 114 applied frequency interrupts and in the corresponding

409815/0840

Octant generates a dashed curve area. See the area 111 of FIG. 5. In this case, ¹ appreciate the skilled man that lack of vectors can be used in a corresponding manner, also indicated by interruptions in the radial reference lines on which the vectors are, or also by a change in the corresponding parameter labeling can be displayed.

In the circuit arrangement shown in FIG. 2 there is also a RAM alarm memory 115, which is controlled via the comparator is connected to the data bus 32. So if a signal is given by the data bus, which is an alarm condition indicates a signal in the RAM alarm memory 115 generated, which is stored in the memory 117, which in turn by synchronizing signals from the timer circuit is operated. The output signal of the memory 117 is scanned via an AND gate 118, at the second input 119 of which is a low-frequency key signal is applied. The output signal of AND gate 118 thus switches the boundary markings and the relevant octants of the vector envelope on and off and shows the operator that a limit has been exceeded. Again it is obvious to the expert to operate the radial reference lines or the parameter identification in touch mode, if the corresponding limit values are exceeded.

FIG. 2 also shows a vector and boundary marking decoder 120 shown. The boundary markings are actually created as part of a three-turn spiral that rollover can be made from three circles and the superimposed parameter values. The boundary markings, e.g. the markings 23 and 24 of FIG. 1, show only small excerpts therefrom in order not to be confusing but rather easily recognizable. The temporal synchronously operated boundary marking decoder 120 switches the boundary markings on the display screen and thereby generates

Δ0981 5/0840

on each reference line outside and inside the circular vector envelope a marking, as shown in Fig. 1 with 22 and 23 is designated.

The blinking signal generated by the RAM alarm memory 115, the periodic interrupt signal generated by the monitoring device 110 and the boundary marking signals generated in the decoder 120 are fed to an OR circuit 121 containing four terminals, the output signal of which is the composite vector key signal represents, which is indicated in Fig. 2 at the top right.

The output signal of the decoder 122 can also be fed to an input of the OR circuit 121. This decoder will operated synchronously and receives digital information for Generation of the eight reference lines on the oscilloscope screen and for generating the parameter identification, e.g. from abbreviations the name of the physiological parameter or the serial number of the reference line (see Fig. 1).

In Fig.12 a block diagram of a circuit is shown, in which the reference lines are generated which, in the example described here, have eight parameters in the display area in Subdivide octants and serve as axes for the representation of the vector envelope. The curve foria of the generation The deflection signals used in the reference lines are shown in FIG. The reference lines 0 to 7 are around each other Shifted 45 °. In Fig. 14, the thin arrows indicate the path of the electron beam or another Recording device used to produce a hard image.

9815/0840

In Fig. 12, a square wave pulse having a frequency of 16 kHz is taken from the timer circuit 46 and one with the factor 16 reducing counter 130 supplied. The output signal given by the counter is a 4 kHz square pulse. In this example the integrator 131 is supplied. The pulse can lag behind the 4 kHz, 2 kHz and 1 kHz square-wave pulses by 90 °, which exceed the Line 133 are fed to a decoding logic 132. The integrator converts the input pulse into a triangular voltage in a known manner. The triangular voltage is switched optionally, to generate the deflection voltages for two reference line lengths, a length equal to 1 at 0 ° and 90 and a length corresponding to 0.707 at 45 °. The triangular voltage of the integrator output 131 becomes a controllable Amplifier 134 supplied. The 4 kHz, 2 kHz and 1 kHz pulses control the decoding logic 132 in such a way that the controllable Amplifier via line 135 is switched synchronously between gain 1 and 0.707. The output of the amplifier 134 is also fed to an inverter 136. By selective Switching the triangular voltage from the gain 134 and the corresponding voltage inverted in the inverter I36 is the curve shown in Fig. 13 is generated.

This selective switching mechanism is shown in FIG. 12 by the three analog switches 137, 138 and 139 made, for example Field effect transistors can contain. These switches are controlled via the connections 140, 141 and 142, via the switching signals from the decoding logic 132 are supplied. The analog switch is at the input of an amplifier 143, which is used to deflect in x. direction required deflection voltages the oscilloscope or a other recording device available. The analog switches 138 and 139 are at the input of the amplifier 144, which supplies the deflection voltages for the x-direction. The amplifiers and 144 thus operate synchronously and periodically generate the signals indicated by 145 and 146 in FIG.

A 0 9 8 1 B / 0 8 U 0

- '29 -

The person skilled in the art can now use the time shown in FIG Detect the course of the deflection voltages in which way these deflection voltages must be added in order to obtain the values shown in FIG. to be able to generate paths of the electron beam marked with an arrow. For example, has the deflection voltage for the x-direction in the time intervals denoted by 0 and 1 in FIG. 13, the value 0 and the deflection voltage for the x-direction decreases from 0 to its negative limit value, increases on again, crosses the O-line, rises to the positive maximum value and then falls back to the value 0. In Fig. 14 the corresponding path of the electron beam between the digits 0 and 1 is covered. In time interval 2 the x-voltage its positive maximum value and the y-voltage its negative maximum value. This causes the electron beam to run off Origin at the point marked with the number 2. The remaining paths of the electron beam can also be carried out in a similar manner to construct.

Of the reference lines of FIG. 14, any line can by means of a properly synchronized key signal, the key signal, for example, from the gate circuit 121 of Fig. 2 can be derived, periodically switched on and off or completely suppressed. In addition, in the manner already described for a curve area of the vector envelope, an alarm condition can also be indicated by reference lines which are operated as a flashing signal.

In the device described so far, the vector envelope forms a circle at the points in time in which the measured physiological parameter values by means of a normalization command are considered normal values. In the process, new values are also entered in the RAM memory 34. If so, then any physiological parameter deviates from the initial values, the original circular vector envelope and is deformed

40981B / 0840

deviates from the circular shape. The device can, however, also work in the opposite way, that is to say it can be designed in such a way that the vector envelope does not deviate from the normal circular shape, but rather strives towards this circular shape. This reversed device requires the doctor to decide what the ideal parameters for a patient should look like in the particular situation. These parameter values can be entered into the device, but they do not necessarily have to be reached during the monitoring time. At the beginning of the monitoring time, the vector envelope then has any shape that corresponds to the physiological parameter values actually present in the patient. In the course of time, various physiological parameter values can then change in a corresponding manner either suddenly or as a result of the therapy carried out by the doctor. This change can serve as a criterion for the doctor to either start a special treatment for the patient or to discontinue a previously carried out treatment. For example, the doctor can administer a drug to increase or decrease the heart rate, or supply oxygen to change the pO ₂ or the pCOp of the blood. These parameters and the corresponding vectors can then change in such a way that there is no longer any difference between the specified parameters and the parameters used to record the vector envelopes. Thus, if a circular shape of the vector envelope is achieved with regard to the physiological parameters of this device, which operates in reverse, then the desired state of the patient is indicated.

15 is a block diagram of part of the circuit arrangement shown, which is used to generate this inverse behavior of the device. In this picture the individual circuit parts have the same reference numerals

15/0840

and are also constructed in the same way as in the circuit arrangement shown in FIG. 2, in which they are used for normalization became. The ideal or desired physiological values are generated outside of the circuit shown in FIG and are fed from bus 32 via line 150 to RAM memory 34. In addition, the limits of Entered manually or on command into the other RAM memory 33. The boundary markings designated 24 in FIG. 1 change only if the doctor manually gives them a different value. All other circuit parts of the device are connected to the in Fig. 2 shown circuit parts are identical and operate in the same way.

The reverse operating device has the same algorithms based on the normal working device. The voltage values indicating the parameter values are generated on the Basis of the equation:

R (t) = K (P (t) - P (ideal)) + "R _n (9 ')

The representation of the limit values is given by the relationship R _L (t) = K (L (t) - P (ideal)) + R _n , .. (10 »)

where P (ideal) is the given parameter value or values that the doctor would like to receive from the patient. The remaining terms of the equations are already defined.

The representation of the vector envelope can be carried out by various devices once those in the equations (9) and (10) are calculated for a group of physiological parameters. The physiological data can z.3. can be processed in a computer and the results of the computer can be used to produce a hard figure or a soft figure can be used on an oscilloscope screen.

L 0 9 8 15 / 08A0

FIG. 16 is a schematic diagram of a mixture of Computer units and flow chart, which is used, to explain the calculator method in more detail.

In the arrangement of FIG. 16, the vector envelope becomes 200 recorded on a phosphorescent base plate 201 of an oscilloscope 202. The oscilloscope can be used to produce a Be equipped line screen image and may contain magnetic or electrostatic deflection devices. The electron beam the oscilloscope can have an origin. Describe rays 203 which are at the same angular distance from one another own. For example, the rays are rotated by 45 ° against each other when 8 physiological parameters are processed. In an embodiment with a line raster image there are 777 image elements on one horizontal line and 777 horizontal lines are parallel to each other, so that the sum of all picture elements is given by the square of that number.

In a raster imaging system, there is vector envelope 200 and reference lines 203 and any other data presented from points of light that are generated by switching the electron beam on and off, while it is horizontal in a known manner and is deflected vertically. The output device 204 connects the computer to the oscilloscope 202 or to another Recording devices which can be used to produce a hard or a soft image. Data signals over the connecting line 205 are fed to the oscilloscope, turn on the electron beam as the scanning progresses and off so that the vector envelope and other data are written point by point and appear as lines because the points can be generated in very rapid succession.

40981 5 / 08A0

The computer shown in Fig. 16 processes the physiological Data and generates a vector envelope from them, which is shown in FIG. 17, for example. The calculator continues to work the program indicated schematically with 210, it has a ' Control unit 211 and a central data processing unit 212. To simplify the illustration, there are several registers and memory of these units not shown.

Several physical parameters are entered into the computer in the form of electrical signals, which are displayed in visible form should be. In the present example 8 parameters are processed. The calculator performs with the entered Data periodically the algorithm

where the terms of this equation have the same meaning as in equation (9). The index η denotes that Parameter for which a vector is currently being calculated in this way.

As in the example described first, the initial values of the parameters P ^ (T _n -) to Pq (Tjj) used for normalization are read in and stored as electrical signals in the memory 213 '. The time-variable values P ^ (t) to P ₈ (t) of the parameters are read periodically and stored in memory 214. Deformation sensitivity factors K ^ to K _Q are continuously stored in memory 215. Thus, all of the information required to calculate the algorithm given in equation (11) is in the computer and is available.

FIG. 17 will now be used to explain how the vector envelope is being developed. The computer program takes the values of a given parameter and calculates the difference between these values

4 0 9 8 15/0840

and the selected norinal value. These differences appear as a change in the radius of a circle or a differently shaped vector envelope, which in the example of FIG. 17 is defined by 8 reference lines. The points of intersection of the vector envelope with the brightly lit reference lines represent the first group of normal _{values R 1} (t) to R _Q (t) for the corresponding parameters. These parameters are calculated according to the algorithm of equation (11) and are converted within a few microseconds in Shown in the form of points of light. Originally, each reference line or each vector R _n Ct) is calculated in the form of its polar coordinates and then converted into Cartesian coordinates in order to determine the position of the reference lines 1 to 8. The first normal values R ^ (t) to R _Q (t) are stored in a memory 219 each time they are calculated.

The first values are interrelated by a series of points of light connected, which represent linearly interpolated circular arcs unti are referred to as filling points. Overall are There are 225 fill points for each octant, 0.2 ° apart. These fill points are determined by the computer according to the equation

0 (8) = R ₀ Ct) + (R _n VJ <t) - R _n Ct)) u (12)

is calculated, in which C (Q) represents an envelope curve value in polar coordinates which is angularly removed from the first value preceding it in the clockwise direction; R _n Ct) represents the vector value of the η-th vector; R _{n +} ^ Ct) represents the value of the (n + 1) th vector; u specifies the index angle of the individual filling points, which in this example is 0.2. Like the first envelope curve values, the filling points are calculated in polar coordinates and then converted into Cartesian coordinates. The conversion is performed using a sine-cosine table which is stored in a register or memory 216. Sin fill point is displayed on the screen every time the angle u is indexed

4 0 9 8 1 5/0 8 U 0

will. The calculator is programmed in such a way that the filling points of each octant are calculated and displayed. At the end of each octant the computer decides whether to move on to the next octant or to return to the output of the octant that has just been calculated target.

• According to its program, the computer first writes the eight dotted reference lines and then calculates and displays the first envelope curve values and envelope points. Before or after these work steps, the computer can control the writing beam or another recording device used so that corresponding labels or identifiers are written at the end of the reference lines, such as HR as an abbreviation for heartbeat and corresponding other abbreviations for the other parameters. Although the vector envelope and other data are written on your screen in the form of dots and several passes, the calculation of the position of the individual dots and their time deviation is carried out so quickly that the eyes see a stationary and complete image on the screen. The normal values P ^ (T ₁ ^) to Ps ^ ^T N ^ can be re-entered into the memory at any time, if a renewed adjustment of a circular shape is desired. With increasing time, provided that there are no more changes in the physiological parameters, the circle will keep its shape or it will continue to deform with a corresponding change in the physiological data.

Λ 0 9 8 1 B / 0 8 U 0

Claims (29)

Claims Device for displaying physiological data in the form a vector envelope in which several measured parameter values are compared with parameter values specified at the beginning will, characterized in that a first RAM memory (33) is provided for receiving a group of electrical signals, each of which corresponds to an instantaneous value P (t) of a measured parameter value, and that a second RAM memory (34) for receiving and storing this group of signals is provided at so-called normalization or start times, such a signal of any special parameter being designated by P ("T, j), that an adder (36) is provided, which in the first RAM memory (33) and receives signals stored in the second RAM memory (34), subtracts them from one another in the correct order and outputs an output signal P (t) -P (T _N ) to identify each parameter that in a summing amplifier (47) each, one parameter Characteristic signal, a selectable constant R ^ is added, which corresponds to a predetermined vector length and is used to normalize the vector envelope to a circular shape, the G group of output signals is given by (P (t) - P (T _n ) + R _n and the actual, time-variable value R (t) of the actual, time-variable value R (t) of the signal in the form of a signal group for all Parameters shown, and that a display device (20) is provided which receives these signals R (t) to generate a visible representation and thereby records the parameters as straight lines through a common point of intersection. U 0 S 8 1 5/0 8 U 0 2. "Device according to claim 1, characterized in that an operational amplifier (43) is provided for multiplying the difference _{signal (P (t) - P (T n} )) with a predetermined sensitivity factor K, which generates a group of signals at its output in which each parameter is represented by K ( P (t) - P (T _n )) is detected, and that by adding the constants R _n in the adder (47) finally a group of signals with the values K (P (t) - P (T _n )) + 'R _{n is} provided. 3. Device according to claim 1, characterized in that a device is provided for generating electrical signals which correspond to the predetermined limit values of the parameter values, that these limit value signals are entered into the first RAM memory (33) and are denoted by L (t), that of the limit value signals in the adder ( 37) one after the other the normal _{values P (T n} ) of the corresponding parameters are subtracted and differential signals of the form (L (t) P (T _{n )) are generated, and that a selectable constant R n is} added to each of these signals in the summing amplifier (47) and a group (L (t) - P (T _n )) + R _n of _{signals designated R L} (t) is generated which successively reproduces the instantaneous limit value for each parameter and essentially together with the signals R ( t) is displayed. 4. Apparatus according to claim 3 ,. characterized in that. the difference signals (L (t) - P (T _n )) are multiplied in the operational amplifier (43) by a predetermined sensitivity factor K and a group of limit value signals of the form K (L (t) - P (T _n )) is generated, and that L 09815/0840 after adding R _n in the Sumnii erver stronger (47) finally a group of limit value signals of the form K (L (t))) + R _{n is} produced. 5. Apparatus according to claim 1, characterized in that a gate circuit (103) is provided via which optionally in the second RAM memory (34) the normal values of the parameters characterizing signals P (T ") or cannot be fed. 6. Apparatus according to claim 3, characterized in that the display device (20) contains a recordable deflection system which is responsive to the parameter and limit value signals, and also has a screen (21) for the visual representation that the group of signals R _L (t) and R (t) two multipliers (79, 80) connected to the display device (20) are supplied, that a cosine generator is connected to a further multiplier (61) and a sine generator is connected to a further multiplier (62), both of which have the angular frequency θ, that the groups of the signals Rj. (t) and R (t) are fed to the multipliers (61, 62) and output voltages are generated which control the deflection system of the recording device, and that a Lissajou circuit is recorded by the cosine and sine generators in the recording device as long as the Parameter signals and the limit value signals are the same, and deviations from the circular shape occur as soon as any parameter signal of the signal group deviates from the corresponding limit value. £ 0981 5 / OSAO 7. Apparatus according to claim 6, characterized, that the display device (20) contains an oscilloscope. 8. Apparatus according to claim 1, characterized in that "that a reading unit (37) for reading out the difference signals in a predetermined order at the output of the adder (36) is provided, and that storage units (90, 91, 92) the writing of new parameter values in the second RAM memory (3A-) during a read-out operation of the reading unit (37) prevent. 9. Apparatus according to claim 1, characterized in that the RAM memories (33, 34) for storing digital Signals and the adder (36) for processing digital signals -designed that the reading unit (37) as an output signal a digital difference signal from the adder (36) reads that the reading unit (37) when reading out the Time-variable differential signals from the adder (36) are controlled periodically by a reading start pulse is, and that a digital-to-analog converter (40) receives the digital output signals of the reading unit (37) and into a Group of analog signals converts. 10. Device according to claim 9 » characterized in that a first order integrator (51) is connected to the summing amplifier (47), which has a selectable constant I ^ -an each Difference signal is added, connected and the step-shaped analog signals in a continuous waveform converts. / 109R1B / Q8A0 11. The device according to claim 6, characterized in that the adder (36) processes digital signals in that a digital-to-analog converter and a circuit for generating read start pulses is provided that the reading unit (37) responds to a reading start pulse signal and the digital Forwards difference signals in a predetermined order to the digital-to-analog converter, which transmits a sequence of the difference signals outputs corresponding analog signals that a third multiplier (80) and a fourth multiplier (79) are provided that in the third multiplier (80) a new sequence of signals with sin 2Θ and in the fourth Multiplier (79) a previous sequence of signals is multiplied by cos 2Θ, where 2θ is double Angular frequency is that a limiting amplifier (60) for adding the output signals of the third and fourth Multiplier is provided, and that the output signal of the limiting amplifier (60) simultaneously and together with sine and cosine signals of frequency θ from the Sine and cosine generator a first multiplier (61) and a second multiplier (62). is fed. 12. The device according to claim 1, characterized in that a circuit is provided for generating reference lines which divides the image plane of the display device (20) into several partial areas, the reference lines radiate outwards from an origin point and have the same angle of distance from one another, that this circuit for generating the reference lines devices (130 to 144) for generating two control signals which are shown in time intervals, the index number of which corresponds to the index number of the reference lines, and that these control signals are simultaneously applied to the deflection system of the display device (20) and for display h 09 8 1 h / 0 8 U 0 of the reference lines are used. 13. The device according to claim 1, characterized in that a first RAM memory (33) is provided for receiving a group of electrical signals, each of which corresponds to an instantaneous value P (t) of a measured parameter value; Group of signals is provided which correspond to the expected values of the parameters and are denoted by P (ideal), that an adder C56) is provided which the signals stored in the first RAM memory (33) and in the second RAM memory (34) which subtracts these signals from each other in the correct order and emits an output signal P (t) -P (ideal) to indicate for each parameter that a selectable constant R ^ is added to each parameter characterizing signal in a summing amplifier (47) , which corresponds to a predetermined vector length and is used to normalize the vector envelope to a circular shape, the group of output signals du rch (P (t) - P (ideal)) + R _{n is} given and represents the actual, time-variable value R (t) of the signal of the individual parameters, and that a display device (20) is provided which displays these signals R ( t) processed to generate a visible representation and thereby records the parameters as straight lines through a common point of intersection. 14. Apparatus according to claim 1, characterized in that an integrator (51) of the first order is provided, at one input there is a currently existing group K (P (t) - P (T ^)) + R ^ of signals and at the other 4 0981B / 0840 Input a corresponding, preceding group of signals is present that the integrator (51) the momentary existing and previous signal groups are integrated and at its output a piece-wise smooth, emits an electrical signal whose smooth curve areas each correspond to a parameter that two multipliers (61, 62) are provided, at one input at the same time the piece-wise smooth electrical signal is present that a .Sine generator (63) is provided "which the other input of one of the two multipliers controls that a cosine generator (64) is provided which controls the other input of the other multiplier, and that the output signals of these multipliers are fed to the deflection system of the display device (20) will. 15. Apparatus according to claim 1, characterized in that a -sine generator and a C o sine generator with the frequency θ are provided, that an input of a multiplier (62) is controlled by the sine signal and an input of another multiplier (61) is controlled by the C. o sine signal, that a sine generator and a cosine generator with the frequency 2 θ are provided that two further multipliers (79, 80) are provided with at least two inputs each, that one input of the multiplier (80) from the sine signal of the frequency 2Θ and the corresponding input of the other multiplier ( 79) is controlled by the cosine signal of the frequency 2 θ that the multiplier (80) receives the signal group FL, (t) that has just preceded it at a further input, that the multiplier (79) receives the currently existing signal group ^ _{n + at a further input} -] (t ') is supplied, 409815/08 that a limiting amplifier (60) adds the output signals of the multipliers (79, 80), and that this summation signal is simultaneously fed to the multipliers (61, 62) and a group of continuous electrical signals for modulating the display device (20) are generated. 16. The device according to claim 1,
characterized, that a monitoring device (110) is provided, which responds to missing signals in the signal group and thus the absence of the corresponding parameter and that devices (112, 113, 121) are connected to the monitoring device (110), which, as a result of a non-existent signal, interrupt the visible reproduction on the display device. 17. The device according to claim 1,
characterized, that a monitoring device (110) is provided, which responds to the absence of a signal of the signal group and thus the absence of the corresponding one Parameters identifies and that devices (112, 113 »121) are connected to the monitoring device (110) which interrupt the visible reproduction of the reference line at the point of the absent parameter is located. 18. Apparatus according to claim 3, characterized in that a RAM alarm memory (115) is provided which responds when a parameter value exceeds a predetermined limit, and that devices (117, 118, 121) are connected to the RAM alarm memory (115), which are in L 0 9 8 1 5/0 8 U 0 Deflection system periodically interrupt the visible reproduction of the signal that corresponds to the parameter, who exceeds the limits set for him. 19. A method for displaying data in the form of a vector envelope, in which several measured parameter values are compared with initially specified parameter values, characterized in that a first group of electrical signals is generated, each of which has a parameter value (P (t)). at the time of generation corresponds to the fact that a second group of signals is selectively measured or specified in the starting time and corresponds to the parameter values P (T "), that the signals of the second group are subtracted from the signals of the first group, which characterize the same parameter values, and one group is generated by difference signals, in which a difference signal (P (t) P (T _n )) is included for each parameter and the difference signals are generated in periodic order that these difference signals each with a sensitivity factor K-. to K _{n are} multiplied and a group of signals K (P (t) - P (T ,,)) produce that a constant R ^ is added to each signal of the last-mentioned signal group and the signal group ,, in which a signal for each parameter of the form K (P (t) P (Tt \ t)) + RM is contained in such a way that, by means of a control device, the display device displays a circular vector envelope in the absence of signals of the last-mentioned signal group, the control device in temporal relationship to the corresponding signals of the last-mentioned signal group brings a corresponding section of a circle to the display, and that the signals of the last-mentioned signal group are passed on to the display device that they generate a circular vector envelope when the difference between the instantaneous and the initial values L 0 9 8 1 B / Π 8 U 0 the parameter is O, and that it is a non-circular Generate vector envelopes if this difference differs from O. 20. The method according to claim 19, characterized in that electrical signals L (t) are generated at the same time, which correspond to the predetermined limit values of the parameters, that the corresponding initial electrical value signals P (Tjj) are subtracted from these electrical limit values L (t) and the result of each subtraction is subtracted with the corresponding sensitivity factor K ^ to K is multiplied so that the constant R ^ is added to the signal generated in this way and thus finally a final group of limit signals is generated in which each individual parameter is characterized by R, - (t) and by K ( L (t) - P (T _n )) + R ^ is given, and that this final group of limit value signals is processed further together with the final group of the signals characterizing the parameter values. -o ¹ 21. The method according to claim 19, characterized, that in response to the absence of a parameter signal in the final group of parameters characterizing Signals an electrical signal generated and used to control the display device in such a way that the areas in which a parameter signal is missing are identified. 409815/0840 22. The method according to claim 19, characterized in that electrical signals are generated which one the Contain information identifying parameters and from the display device in the vicinity of corresponding reference lines for identifying the corresponding parameters and of the areas of the vector envelopes contained in the final group of parameter signals are indicated will. 23. The method of claim 19, wherein the shape of the vector envelopes is determined by the parameter values compared with comparison values, characterized in that a first group of electrical signals is generated, whose values correspond to the instantaneous values of the measured parameter values that of this first signal group the Parameter values, a second, earlier set group of signals with normal values is subtracted, and a periodically repeatable group of signals is generated, the amplitude of which is a measure of the difference between corresponding parameter values and reference values represent that for each signal from the group of difference signals a predetermined signal value is added that a display device is controlled with modulation signals and a repeatable sequence of curve segments is generated which correspond in time with the final group of signals form a circular envelope, and that the operation of the display device is changed by constantly adding the final group of parameter signals is added and thereby the radii of the curve areas according to the Amplitudes of the respective signals of the group are modulated, whereby a non-circular envelope is generated is when the amplitudes of the signals in the group of £ 09815/0840 Parameter signals are not all of the same size. 24. The method according to claim 23, characterized in that the signals are multiplied in the group of parameter signals m ±% of a sequence of individual sensitivity factors K and equal to each other, wherein the number of the factors K corresponds to the number of signals in the group of parameter signals. 25. The method according to claim 23, with a program-controlled computer, characterized in that in a first program step the electrical signals P ₁ Ct) to P (t) _{corresponding to the measured instantaneous values of the parameters from the stored electrical signals P 1} (T _n ) to ^p _n (% j)> those measured ^{at the beginning} Corresponding parameter values, are subtracted and a group of difference signals is generated that in a second program step each of the difference _{signals is multiplied by a sensitivity factor K 1} to K _n and thereby a group of electrical signals of the form K _n (P _n (^) - ^p _n (%)), where η runs from 1 to the total number of parameters that in a third program step an electrical signal with a constant value IL is added to each signal of the last-mentioned signal group and one with R ₁ (t) to R _n (t) designated group of signals is generated, which corresponds to the length of the main vectors, that in a fourth program step the signals corresponding to the vector lengths correspond echenden reference lines are assigned, which intersect at a point and have a predetermined angular distance from each other and corresponding main vectors are assigned that in a fifth program step L 0 9 R 1 R / Π 8 U 0 43 - Signals "are calculated, the two neighboring main vectors Identify lying intermediate vectors whose vector length corresponds to the relevant angular distance from the two adjacent main vectors is interpolated, and that in a sixth program step the output signals of the computer to the input of the display device, which is based on the fourth and fifth program step "responds to the calculated signals and generates a curve determined by the length and the intermediate angles of the vectors. 26. The method according to claim 25, characterized in that the program-controlled computer uses the polar coordinates the main vectors are determined and the amplitudes of the signals of the fourth program step are determined, as well as the polar coordinates, which defines the signal amplitudes characterizing the intermediate vectors, then the two groups of Converts polar coordinate signals into groups of signals of corresponding Cartesian coordinates and to the display device forwards. 27. The method according to claim 25, characterized in that electrical signals in the program-controlled computer are generated which correspond to points of the reference lines, and that also the signals indicative of the reference lines are fed to the display device and both the reference lines and the vector envelope in the display device being represented. 0 9 8 1 5/0 8 U 0 28. The method according to claim 25 , characterized in that signals stored in the computer for identification of the reference lines are present, that these identification signals are assigned to the reference lines via the coordinates of the reference lines, and that these identification signals are fed to the display device. 29. The method according to claim 25, with an oscilloscope as the display device, through this . characterized in that the oscilloscope enables a line grid display, and that the output signals of the computer switch the electron beam of the oscilloscope on or off depending on the presence or absence of these output signals, thereby generating the vector envelope by means of points of light on the oscilloscope screen. ReRb / Pi. 15/0840