Method and apparatus for determining absolute concentration values ​​of components, blood flow or blood volume in tissue of an organ

Abstract

The method and device for determining the absolute concentration value, blood flow and / or blood volume of a component in tissue of an organ comprises irradiating the tissue with radiation having at least one wavelength in the near infrared spectrum, detecting the emerging radiation using near infrared spectroscopy to generate a measurement signal, converting using an evaluation algorithm, converting the time change in the detection intensity of the emerging radiation into absolute concentration values ​​of the component using a system matrix and a programmed evaluation unit, introducing an indicator having an absorption peak in the near infrared spectrum into the tissue, and determining the time course of the concentration values ​​of the indicator in the tissue.Furthermore, a mean transit time mtt is derived from the time course of the concentration values ​​of the indicator, and the blood volume is determined from the time course of the concentration values ​​of the indicator or a parameter derived therefrom using at least one transport function g(t) characterizing the blood flow in the tissue.

Description

[Technical Field]

[0001] The present invention relates to a method and apparatus for measuring within tissue, and in particular to a method and apparatus for non-invasively determining absolute concentration values ​​of constituents and / or blood flow and / or volume within organs using injectable indicators. [Background technology]

[0002] Known methods for determining concentration values ​​of constituents, blood flow and blood volume in organs or organ tissues generally consist of non-invasive measurements, although this does not exclude the injection of tracer substances.

[0003] However, known noninvasive measurement methods for determining the concentration of components in a measured volume of an organ often cannot determine absolute concentration values, but can only detect relative concentration values, i.e., changes in the concentration of one or more components. Near-infrared spectroscopy (NIRS) is one such noninvasive optical spectroscopic technique, particularly used for continuous monitoring of oxygen saturation in living tissue. NIRS is based on the principle that light in the near-infrared wavelength range penetrates living tissue and is differentially absorbed and scattered by hemoglobin, myoglobin, and / or other congeners in deoxygenated and oxygenated states, allowing a sensor to detect the optical attenuation of the transmitted and / or scattered light compared to the light irradiated by the tissue. Using appropriate algorithms and certain assumptions, changes in the concentration of tissue components, such as oxygenated or deoxygenated hemoglobin, can be calculated from the detected measurement signal. Generally, the evaluation of measurement signals in living tissue is based on a model that follows the diffusion equation and the Beer-Lambert law. Beer-Lambert's law describes the attenuation of the initial intensity of radiation as it passes through a medium containing absorbing material as a function of the concentration and thickness of the absorbing material.

[0004] In contrast, noninvasive determination of absolute concentration values ​​of components based on the modified Beer-Lambert law is difficult, and such values ​​can only be approximated under simplifying assumptions. Generally, in NIRS measurements in biological tissues, neither the actual absolute value of absorption nor the actual path length traveled per defined period is known. Therefore, this model cannot determine absolute concentration values ​​of chromophores.

[0005] U.S. Patent No. 6,456,862 describes the noninvasive measurement of blood oxygen saturation in tissue using a near-infrared spectrophotometric sensor, which allows the determination of absolute concentrations of oxyhemoglobin and deoxyhemoglobin. The sensor irradiates the tissue with optical signals at first, second, and third wavelengths and detects the optical signal after passing through the tissue. The attenuation of the optical signal is described as the sum of attenuation due to deoxyhemoglobin and oxyhemoglobin components and scattering within the tissue. This method requires calibration of the sensor to the target tissue to account for attenuation due to optical scattering, attenuation due to absorption by solid tissue components such as bone and / or water, and / or attenuation due to changes in sensor characteristics during evaluation. Calibration can be based on empirical data, or arterial oxygen saturation can be determined using pulse oximetry as a reference sensor for determining venous oxygen saturation.

[0006] In addition to relative or absolute concentration changes of components in organ tissues, blood flow and / or blood volume can be considered diagnostic parameters that contain information about blood perfusion and the functionality of target tissues. Near-infrared spectroscopy (NIRS) has also long been used to noninvasively determine these diagnostic parameters. By measuring changes in the concentrations of components in organ tissues, NIRS can draw conclusions about the area of ​​oxygen metabolism. The use of NIRS is known for monitoring cerebral blood flow (CBF) and cerebral oxygenation patterns, i.e., measuring the static and dynamic characteristics of cerebral blood and blood flow, respectively.

[0007] A method combining noninvasive measurement with intravenous injection of a tracer substance is known for measuring and monitoring cerebral blood flow. The tracer substance can be, for example, indocyanine green (ICG), which is largely inert and whose distribution is largely confined to the intravascular compartment. Indocyanine green has an absorption peak at approximately 805 nm, which lies in the near-infrared spectrum. ICG binds very rapidly and almost completely to serum albumin in plasma. In this state, it exhibits very high near-infrared absorption and is absorbed by the liver, allowing rapid and repeated measurements. ICG is used in various investigations of liver function and to calculate cardiac output from recirculation time.

[0008] Starting from a bolus injection of indocyanine green, its absorption in the cerebral vasculature under investigation can be determined invasively and / or non-invasively, for example by NIRS, after which the measurement data can be further processed, for example to determine cerebral blood flow.

[0009] U.S. Patent No. 7,529,576 describes a device for measuring organ blood flow and blood volume, particularly cerebral blood flow (CBF), using an injected, nearly inert indicator. The device uses a per se known sensor to detect the portion of irradiated near-infrared radiation emerging from the organ tissue, which includes both pulsatile and non-pulsatile components. The evaluation algorithm takes into account the inflow function characterizing organ perfusion and calculates the blood volume in the organ as the quotient of the concentration from the non-pulsatile component associated with the organ tissue and the concentration from the pulsatile component of the injected indicator associated with the blood volume in the organ. The blood volume value associated with the determined mean transit time allows the calculation of the blood flow in the organ. However, a drawback of this method is that, because the sensor is attached to a surface, the influence of layers located between the measurement volume and the inlet and / or outlet of the measurement signal distorts and weakens the measurement signal, and this influence is not taken into account in the evaluation.

[0010] U.S. Patent No. 6,223,069 describes a method for measuring cerebral blood flow and extracerebral organ blood flow. Flow measurements of an intravenously infused bolus of a tracer substance with absorption characteristics in the near-infrared spectrum are performed simultaneously in both cerebral hemispheres using near-infrared spectroscopy and in the arterial blood of the systemic circulation using pulse densiometric arterial chromogenicity. The evaluation algorithm developed to evaluate the measurements is based on the deconvolution of arterial and cerebral flow kinetics to calculate a transcerebral transport function. From these kinetics, a blood flow index can be determined that is directly proportional to cerebral blood flow.

[0011] Previously known methods and devices for non-invasively measuring blood flow, particularly blood volume and / or absolute concentration values ​​of components in tissues or organs using injected indicators are often technically difficult to implement and time-consuming. In addition to the inaccuracies that arise from the use of simplifying assumptions about the behavior of the injected indicators in the initial rise of the input signal for the evaluation of the measurement data of conventional NIRS measurements, further problems arise from a non-constant measurement background with changing absorption characteristics.

[0012] In the past, simplified interpretation of measurement data often assumed that background absorption did not change during NIRS measurements. Based on this assumption, differential absorption was calculated using a modified Beer-Lambert law. Assuming idealized background constancy, the background effects due to tissue shape, composition, and absorption behavior can be summarized in the coefficient G. However, in real systems and under real conditions, background absorption is not constant. In particular, the water concentration and intracranial pressure in the brain measurement volume are not constant, which leads to inaccuracies in the evaluation of NIRS measurement signals and the determination of brain tissue concentration values, blood volume, and blood flow. Summary of the Invention [Problem to be solved by the invention]

[0013] In view of the shortcomings of previously known methods and devices, it would be desirable to provide a method and device for determining absolute concentration values ​​of constituents in tissue, and more particularly, for determining such absolute concentration values ​​in brain tissue, as well as blood flow, more particularly cerebral blood flow and blood volume, with greater accuracy than previously possible.

[0014] It would further be desirable to provide a method and device for evaluating a detectable measurement signal. Preferably, such a device would be used or performed non-invasively and could be combined with an indicator injection with reasonable technical effort. Furthermore, such a device could be used to perform invasive measurements, for example, using a sensor unit or optode placed under the body surface. [Means for solving the problem]

[0015] The present invention provides a method and apparatus that is expected to substantially eliminate the influence of background and background absorption changes by taking into account fluctuations in background and tissue water concentration when determining absolute concentrations of tissue constituents. In this way, changes in measurement conditions can be verified, improving the accuracy and significance of measurement results.

[0016] Similarly, the influence of the use of indicators is reduced when determining blood flow and blood volume. While previously known systems rely on the application of indicators to determine blood flow and / or blood volume, assuming that the indicator bolus has the shape of a rectangular pulse, the method and apparatus of the present invention avoids such a simplifying assumption. In particular, due to dispersion effects, pulsation, and other factors that must be considered, a rectangular shape does not exist in reality, and the simplifying assumption results in distorted quantification. In reality, an increase in indicator concentration in the considered volume takes the form of a fuzzy peak. According to the principles of the present invention, the influence of actual increases in indicator concentration on the accuracy of the resulting measurement results can be virtually eliminated.

[0017] According to the present invention, a method and apparatus are provided for determining absolute concentration values, blood flow, and / or blood volume of constituents in tissue of an organ. In one embodiment, a sensor irradiates the tissue of the organ with radiation having at least one wavelength in the near-infrared spectrum. The emerging radiation is detected by the sensor, and a measurement signal is generated using near-infrared spectroscopy. The measurement signal, responsive to the detected intensity of the radiation emerging from the tissue, is input to a programmable evaluation algorithm in a programmed evaluation unit, which calculates the temporal change in the detected intensity of the emerging radiation and calculates the absolute concentration value of the constituent by using a system matrix.

[0018] According to one embodiment, an indicator having an absorption peak in the near-infrared spectrum is introduced during acquisition of near-infrared spectroscopy data, and a time course of concentration values ​​of the indicator in the organ tissue is determined. A mean transit time mtt is derived from the time course of the indicator concentration values, and blood volume is determined from the time course of the indicator concentration values ​​or a parameter derived therefrom using at least one transport function g(t) characterizing blood flow in the organ tissue.

[0019] Further details of the invention will become apparent from the following description of preferred embodiments thereof, as illustrated in the accompanying drawings. Further advantages of the invention will also become apparent from the detailed description, together with suggestions and suggestions as to how the objects of the invention may be modified or developed within the scope of the claims. [Brief explanation of the drawings]

[0020] [Figure 1] FIG. 1 is a schematic diagram of an apparatus according to the invention for determining absolute concentration values ​​and / or blood flow in tissue of interest, for example brain tissue. [Figure 2] FIG. 2 is a schematic diagram of a programmed evaluation unit suitable for implementing the algorithm of the present invention. [Figure 3] FIG. 3 is a schematic diagram of a method according to the invention implemented as a program in an evaluation unit for determining cerebral blood flow from input signals. DETAILED DESCRIPTION OF THE INVENTION

[0021] In accordance with the principles of the present invention, absolute values ​​of physiological components can be calculated using a sensor that emits radiation at wavelengths in the near-infrared spectrum and detects the emerging radiation to generate a measurement signal using near-infrared spectroscopy. During near-infrared spectroscopy, a bolus of indicator is introduced into the blood vessel and can be used to repeatedly determine inflow and outflow functions using a programmed evaluation unit. The indicator can be a dye and is introduced into the vascular system using an indicator injection device, such as a syringe or injection device, which is known per se.

[0022] More specifically, the concentration of the indicator bolus in the considered volume may be described by an inflow function and an outflow function. Since these functions are not known or measurable, certain assumptions are made to enable their iterative determination. To this end, the present invention provides a programmable evaluation algorithm that takes into account the outflow of the injected indicator from the considered region or volume during the rising edge of the measurement signal.

[0023] The method according to the invention for determining absolute concentration values ​​of constituents and / or blood flow and / or blood volume in tissue of an organ comprises, inter alia: irradiating the tissue with radiation having at least one wavelength in the near-infrared spectrum and detecting the intensity of the emerging radiation by near-infrared spectroscopy as a measurement signal responsive to the detected intensity of the radiation emerging from the tissue; - converting the time variation of the detected intensity of radiation emerging from the tissue of the organ into absolute concentration values ​​of the components using a system matrix and an evaluation algorithm implemented by a program in the evaluation unit; applying an indicator consisting of a dye having an absorption peak in the near-infrared spectrum during near-infrared spectroscopy and determining the concentration value of the indicator in the tissue over time; deriving a mean transit time mtt from the time course of the concentration values ​​of the indicator using at least one transport function g(t) characterizing the blood flow in the tissue; calculating blood flow and / or blood volume from the time course of concentration values ​​of the indicator and / or derived parameter; It has.

[0024] In one embodiment of the method of the present invention, the system matrix can be first calibrated using known values ​​of the concentration of the constituent in tissue, such as blood, background, and / or water, obtained from in vivo measurements of healthy patients or healthy tissue, and / or boundary conditions defined to constrain the concentration values ​​of the constituent in tissue.

[0025] According to one embodiment of the method according to the invention, the method is arranged to determine from the intensity of the applied radiation and the intensity of the detected radiation, in particular from the measurement signals, absolute concentration values ​​of at least one of the components comprising hemoglobin, deoxyhemoglobin, water, background and / or indicator, as well as the blood volume and / or blood flow rate in the tissue of the organ.

[0026] In particular, radiation of at least one wavelength in the near-infrared spectrum, more preferably radiation of at least four wavelengths, is applied into the tissue of the organ at a first location. A measurement signal is detected by a sensor arranged at a second location spaced from the first location, which measurement signal represents the applied and detectable radiation intensity or components of the applied radiation. Preferably, each of the at least four wavelengths can be selected so that each of the detected components has a local absorption peak or so that the absorption of all components is at least as uniform as possible. The detected measurement signal can be sent as an input signal to a programmed evaluation unit, for example one or more processors programmatically executing an evaluation algorithm comprising the following steps: a) obtaining a measurement signal based on the applied and detected portions of radiation having at least one wavelength in the near infrared spectrum, which is transmitted to an evaluation unit; b) determining absolute concentration values ​​of at least hemoglobin, deoxyhemoglobin, background, and / or water components in the tissue of the organ; c) determining the time course of the concentration of the injected indicator in the tissue of the organ from the measurement signals; d) iteratively determining the inflow function i(t) and outflow function o(t) characterizing the blood flow in the tissue of the organ using a transport function g(t) with a determinable mean transit time mtt until a termination criterion is reached; e) fitting the iteratively determined inflow function i(t) and the iteratively determined outflow function o(t) using a lognormal function or another type of function representing the tissue passage system; f) calculating the blood volume in the tissue of the organ using either the time function curve determined in step c) or e); g) calculating the blood flow volume in the organ as the quotient of the blood volume in the organ tissue calculated in step f) and the mean transit time mtt determined in step d); It has.

[0027] Based on the detectable near-infrared radiation emerging from the organ tissue, i.e., the detected intensity signal, the optical density (OD) value can be determined. Generally, optical density or extinction is a measure of the attenuation of radiation as it passes through a medium due to absorption, scattering, diffraction, and / or reflection. The optical density value can be determined as the negative logarithm of the transmittance as a function of the radiation wavelength.

[0028] Absolute concentration values ​​of components and background associated with the measurement volume of organ tissue can be determined using a preferably calibratable system matrix. The system matrix describes the imaging characteristics of NIR spectroscopy, taking into account the optical path lengths at different wavelengths, the extinction coefficients of the components considered, and the molecular weights of the individual components (e.g., hemoglobin and water). The system matrix can be used to solve simultaneous equations so that absolute concentration values ​​of components can be determined from the detected measurement signals.

[0029] According to one embodiment, the background of the tissue of the organ under consideration can be taken into account for the preferably one-time calibration of the system matrix. The background can consist of several components, e.g., tissue, fat, bone, etc., in some combination thereof, for each of which an extinction coefficient is used as a specific material constant. More generally, the extinction coefficient depends on the wavelength of the emitted radiation and the temperature during the measurement. The extinction coefficients of the background components can be obtained from clinical data and / or literature for known concentration values, such as blood, hemoglobin, and / or water, in proportion to the expected presence of such components in the background. The known extinction coefficients themselves allow for calibration of the NIR spectroscopy or the system matrix. Calibration is therefore an essential part of the evaluation algorithm for determining absolute concentration values ​​of organ tissue components.

[0030] In addition to the absorption characteristics of the inhomogeneous background, the optical density of the tissue under consideration, e.g., the optical density of the cerebrum, is taken into account when setting up the system matrix. The solution space of the system matrix can be restricted by defining a definable relationship between the determined optical density of the tissue at different wavelengths and the weighted sum of the concentration values ​​of the components.

[0031] Using the detectable time-varying optical density, absolute concentration values ​​of components in organ tissues can be calculated using the system matrix.

[0032] According to one aspect of the present invention, the method can include determining blood volume and / or blood flow using indocyanine green as an injectable indicator. However, the use of this indicator is not limited. In such embodiments, the concentration of the injected indicator in the target organ tissue depends on the concentration of the injected indicator entering the organ tissue with the inflowing blood and the volume of blood flowing through the organ tissue. Because the concentration of the injected indicator in the organ tissue varies due to distribution kinetics and degradation, blood exiting the organ tissue will have a different indicator concentration or concentration time course than the inflowing blood. After administration of the indicator, for example, in the form of an indicator bolus, the indicator reaches the target tissue via the bloodstream after a certain time, the so-called transit time (mtt), and is perfused into the existing capillary network or vasculature. From the determinable concentration-time curve of the injected indicator, the volume of distribution of the same indicator, as well as the blood volume and / or blood flow rate in the target organ tissue, can be determined, thereby taking actual effects into account in the evaluation.

[0033] According to one embodiment of the method, the blood flow in the tissue can be determined from the time course of determinable concentration values ​​of an indicator in an organ or tissue of an organ. For this purpose, an inflow function i(t) and an outflow function o(t) can be determined iteratively. The inflow function i(t) describes the proportion of the change in concentration of the injected indicator in the measurement volume under consideration, e.g., brain tissue, that is caused by the inflowing blood volume. The outflow function o(t) describes the proportion of the change in concentration of the indicator in the measurement volume that is caused by the outflowing blood volume.

[0034] In the iterative determination, each step involves approximating the inflow function i(t), which can be expressed as a function of the time course cICG(t) of the concentration of the indicator in the tissue of the organ and the outflow function o(t).

[0035]

number

[0036] The outflow function o(t) can be determined by deconvolving the convolution integral of the inflow function i(t) and the transport function g(t) using * as the convolution operator.

[0037]

number

[0038] As a starting parameter for the iterations for determining the inflow function i(t), an estimated or determinable mean transit time mtt, also called the turnaround time, is selected. The initial value of the mean transit time mtt can be determined by fitting and integrating the time course of the injected indicator concentration values ​​cICG(t) with a log-normal distribution or other type of function that describes the tissue transit system, i.e., the transit behavior of blood flow through tissue.

[0039] During the iterative determination of the inflow function i(t) and the outflow function o(t), the time variable t is set to zero for the time of indicator increase in the measurement volume. Furthermore, the inflow function i(t) and the outflow function o(t) are set to zero for t<0 to ensure a causal relationship between the time of indicator application and the measurable indicator increase.

[0040] The inflow function i(t) and outflow function o(t) are determined for an assumed mean transit time mtt using a transport function g(t). The time course of the transport function g(t) is generally a single-peaked asymmetric distribution that can be approximately described, for example, by a log-normal function. Here, the mean transit time mtt and the resulting transport function g(t), and the associated inflow function i(t) and outflow function o(t), are varied until a termination criterion is reached.

[0041] The inflow function i(t) at a certain time t can be expressed as follows, based on the time course cICG(t) of the concentration value of an indicator, for example, indocyanine green ICG, and the outflow function o(t), according to a balance equation:

[0042]

number

[0043] For the calculation of the influx function i(t), first, from the determinable time course of the optical density OD(t) of indocyanine green as the indicator component, the extinction coefficient εICG, and the covered light path length β, the concentration cICG(t) of the indicator in the considered tissue is determined according to:

[0044]

number

[0045] The outflow function o(t) at time t can be formulated as the convolution integral of the inflow function i(t) and the transport function g(t). That is, deconvolution of the convolution integral can be used to determine the inflow function i(t) and / or the outflow function o(t), where T is a small, constant time interval, or increment.

[0046]

number

[0047] The transport function g(t) can be formulated as a function of the transit time mtt according to one of the approaches known per se. A suitable approach is the lognormal function.

[0048]

number

[0049] Here, σ is a constant shape parameter whose value is a real number greater than 0. The shape parameter σ can be determined empirically, and σ roughly represents the width of the expected residence time distribution. As the value of σ decreases, the symmetry of the log-normal distribution increases.

[0050] In a subsequent step, a deconvolution of the established convolution integral is performed to determine the inflow function i(t) and the outflow function o(t) based on the determinable time course of the indicator concentration cICG(t). Here, the influence of recirculation on the time evolution of the concentration of the indicator cICG(t) in the considered measurement volume, and therefore on the inflow function i(t) and the outflow function o(t), is also removed by fitting a lognormal function.

[0051] In a subsequent step, it can be checked whether the previously determined function curves of the inflow function i(t) and the outflow function o(t) are plausible. Thus, the termination criterion for determining the mean transit time mtt can be defined by a plausibility criterion related to the inflow function i(t) and the outflow function o(t).

[0052] In one embodiment, the plausibility criterion can be defined by the distance between the center of gravity of the inflow function i(t) and the center of gravity of the outflow function o(t), which distance corresponds approximately to the mean transit time mtt.

[0053] Alternatively, the plausibility criterion can be defined by the ratio of the area under the inflow function i(t) to the area under the outflow function o(t). For example, the ratio can be 1:1.

[0054] If the function curves of the inflow function i(t) and the outflow function o(t) satisfy one of the plausibility criteria, i.e., if a termination criterion is reached, the variation of the transit time mtt is terminated, and the procedure for determining the blood volume and / or blood flow in the organ tissue under consideration continues using the determined function curves of the inflow function i(t), the outflow function o(t), and the determined mean transit time mtt. If the function curves of the inflow function i(t) and the outflow function o(t) do not satisfy any of the plausibility criteria, the mean transit time mtt can be increased or decreased by an increment τ, and the iterations according to the above steps can be performed again, starting with the corresponding modified mean transit time mtt as a starting parameter.

[0055] According to one aspect of the method, the blood volume in an organ tissue can be determined by the area under the inflow function i(t) and outflow function o(t) based on the assumption that the area is proportional to the blood volume BV, e.g., cerebral blood volume CBV, where the integration limits for determining the area can be selected according to the width of the curves of i(t) and o(t).

[0056] Instead of determining the blood volume using the integral of the inflow function i(t) and outflow function o(t) to determine the corresponding area, the time course of the indicator concentration values ​​cICG(t) can be used. The time course of the indicator concentration values ​​cICG(t) can be approximately described by an exponential function using regression in the time interval t1>0 until the final value t2>t1. This exponential function can be extrapolated to a specific time, for example t=0, i.e., the time of indicator injection.

[0057] Therefore, from the determined time course of the indicator concentration values ​​cICG(t), the calculation of the indicator concentration cTissue in the considered organ tissue immediately after injection can be determined by the following formula:

[0058]

number

[0059] The blood volume BV of an organ, e.g., cerebral blood volume CBV, is calculated as the quotient of the indicator concentration associated with the considered tissue, cTissue, the known indicator concentration in blood, cBlood, and the tissue density, ρTissue, according to:

[0060]

number

[0061] The concentration of the indicator in the blood can be calculated from the total blood volume BV and the amount of indicator injected.

[0062] The blood flow BF in the organ considered can be determined as the quotient of the blood volume BV, e.g., cerebral blood flow CBF, and the mean transit time mtt according to the following formula:

[0063]

number

[0064] As explained below, the present invention includes an apparatus provided and / or programmed to carry out the method. In a preferred embodiment, the apparatus comprises an evaluation unit arranged by a program to execute an evaluation algorithm, a unit including electrical and / or optical components, and at least one sensor arrangement for providing radiation having at least one wavelength in the near-infrared spectrum. The sensor unit comprises an optical component having at least one detector for detecting an exiting portion of the applied radiation.

[0065] Referring now to FIG. 1, an apparatus 1 for determining absolute concentration values ​​and / or determining blood volume and / or blood flow rate in brain tissue is described. To this end, the apparatus 1 includes a non-invasive measurement device and method coupled with an indicator application. The sensor arrangement 10 is removably attached to the patient's body surface. Alternatively, the sensor arrangement 10 can be inserted through the patient's body surface to invasively determine absolute concentration values.

[0066] The sensor arrangement 10 comprises electrical and optical components, for example, combined in unit 20, at least one sensor unit 30 for irradiating radiation having at least one wavelength in the near-infrared spectrum, and at least one detector unit 40 for detecting radiation emerging from the body tissue. The radiation, preferably at multiple different wavelengths in the near-infrared spectrum, is emitted into the body tissue from an external light source or from a light source located directly within unit 20 or sensor unit 30, such as multiple light or laser diodes. At least one wavelength of the irradiated radiation is matched to the injected indicator, e.g., indocyanine green ICG. When indocyanine green ICG is injected as the indicator, one of the wavelengths may be in the range of 780-900 nm, preferably approximately 808 nm. To determine the optical density of multiple components in a measurement volume, it is desirable to use at least four wavelengths.

[0067] The sensor arrangement 10 consists of at least one detector unit 40, preferably a first detector unit and a second detector unit (not shown), which are arranged at an optimized distance from each other, where optimization is understood as relating to the penetration depth of the irradiated radiation into the body tissue and / or the signal-to-noise ratio.

[0068] The first and second detector units (not shown) are configured to detect a portion of the radiation emerging from the tissue as a measurement signal, which is transmitted to the evaluation unit 50. The transmission of the measurement signal may be performed in real time by cable or wirelessly. The evaluation unit 50 may consist of electronic devices, e.g., one or more processors and / or light sources, and is preferably programmed to execute a program. The one or more processors can communicate with each other via a wired bus or wirelessly. In the case of wireless communication, remote access is possible at any time.

[0069] 2, an exemplary embodiment of an evaluation unit 50 will be described. The evaluation unit 50 comprises a computer, e.g., a laptop, desktop, or tablet, programmed with the evaluation algorithm software described herein, and includes at least one processor 100, memory 110, non-volatile storage 120, an optional transceiver 130, a power supply 140, and one or more input devices 150 and output devices 160.

[0070] Processor 100 may be a conventional multi-core processor, such as an Intel CORE i5 or i7 processor. Memory 110 may be comprised of volatile memory (e.g., random access memory (RAM)), non-volatile memory (e.g., read-only memory (ROM)), flash memory, or any combination thereof.

[0071] The optional transceiver 130 can receive and / or transmit noninvasive measurement information to and from other components in the system, such as a remote monitoring station and / or a controller for injecting indicator dye, using any well-known communications facility that facilitates communication via wired or wireless connections, such as any IEEE 802 standard. The power supply 140 preferably connects to a standard outlet and / or may include a battery. The non-volatile memory device 120 preferably includes removable and / or non-removable storage devices, such as solid-state disk memory or a magnetic hard drive.

[0072] The input device(s) 150 may be one or more devices coupled to or integrated with the evaluation unit 50 for inputting data into the evaluation unit, and may include, for example, a keyboard or touch screen, a mouse, and / or a pen. The input device 150 may be used to input data used in populating the system matrix, as well as patient-specific information, such as height, age, complexion, gender, and identity, into the evaluation unit. The output device 160 may be any suitable device coupled to or integrated with the evaluation unit 50 for outputting or otherwise displaying data, such as a video screen, printer, or plotter. The output device 160 may further include a speaker or alarm bell that may be activated if one or more measurement signals fall below a clinically significant threshold indicating patient distress.

[0073] 2, operating system 170 and evaluation algorithm 180 are stored in non-volatile storage 120. Operating system 170 includes an operating system for the evaluation unit, such as Microsoft Windows or Linux, and the necessary drivers for input and output devices.

[0074] The evaluation algorithm 180 may be personalized for a particular patient based on input provided through the input device 150, or may include machine learning and search algorithms for analyzing the input patient-specific data to modify the data in the system matrix 190 to generate real-time extinction values ​​appropriate for the patient being monitored. The evaluation algorithm 180 may also include programming for communicating with and adjusting the input sampling rate of the input received from the sensor arrangement 10, and for generating an output that is displayed on the output device 160.

[0075] The evaluation algorithm 180 includes programmed instructions for generating absolute values ​​of blood volume and blood flow, particularly cerebral blood volume and blood flow, using noninvasive measurement signals obtained from the sensor arrangement 10, as described herein. Specifically, the evaluation algorithm may employ an iterative process for determining absolute concentration values ​​of specific blood components, e.g., oxyhemoglobin and deoxyhemoglobin, blood flow, and / or blood volume of tissues of an organ, using the patient's noninvasively measured physiological data, as described in the flowchart of FIG.

[0076] With reference to FIG. 3, an exemplary flow chart corresponding to a programmed evaluation algorithm 180 stored in the non-volatile memory device 120 of the evaluation unit 50 will be described.

[0077] The sensor arrangement 10 shown in FIG. 1 allows high-resolution, e.g., greater than 5 Hz, extinction measurements to be performed in step 200, e.g., on a patient's head. Thus, the time course of the optical density OD(t) for preferably multiple components within the considered measurement volume can be determined as the negative common logarithm of the quotient of the intensity of the detected near-infrared radiation and the intensity of the irradiated near-infrared radiation. Here, the optical density of the considered tissue can be determined for at least the components hemoglobin, deoxyhemoglobin, water, background, and / or indicator. In step 210, a preferably calibratable system matrix can be generated. For this purpose, the components and their proportions of the background in the measurement volume, as well as the influence of the background components on the extinction coefficient, are taken into account. Thus, by taking into account the density of the organ as well as literature values ​​and / or comparative measurements, absolute concentration values ​​of components in the considered measurement volume, particularly hemoglobin, deoxyhemoglobin, background, and / or water, as well as the injected indicator, can be determined in step 220. Such determined values ​​may also be adjusted to be patient specific, for example, to adjust bone density based on age or to take into account skin tone.

[0078] In step 240, the evaluation algorithm subjects the indicator concentration change over time cICG(t) determined in step 230 to a plausibility check. If this evaluation fails, the measurement is considered invalid. In step 250, the indicator concentration time course cICG(t) is fitted with a log-normal function. In step 260, the mean transit time mtt is estimated, which is subject to a definable limit, i.e., the minimum transit time mtt. min and maximum transit time mtt max and therefore in a determinable search interval. The search interval is defined in step 270. A query as to whether the mean transit time mtt is within the defined range can be made in step 280. The mean transit time mtt is determined for the iterative determination of the inflow function i(t) and the outflow function o(t) and for the determination of the blood volume and / or blood flow in the organ under consideration. The outflow function o(t) can be determined from the convolution of the inflow function i(t) with the transport function g(t), and in particular the ascending branch of the curve can be approximately determined by a lognormal function as a function of the mean transit time mtt.

[0079] In step 290, a corresponding transport function g(t) is determined based on the minimum transit time mtt. In step 300, the time course of the inflow function i(t) and the time course of the outflow function o(t) can then be determined. The time course of the inflow function i(t) and the time course of the outflow function o(t) can be approximately described using corresponding log-normal distributions, as shown in step 310. In step 320, a plausibility check is performed using a plausibility criterion that defines a termination criterion for the variation of the mean transit time mtt.

[0080] As a first plausibility criterion, i.e., as an end criterion for the variation of the mean transit time mtt, the positions of the centroids of the inflow function i(t) and the outflow function o(t) can be determined, which have a definable distance from each other according to the first plausibility criterion. The definable distance can correspond to the mean transit time mtt.

[0081] Alternatively, a further or second plausibility criterion can be used based on the area determined under the inflow function i(t) and the area determined under the outflow function o(t). If the second plausibility criterion is met, the areas to be determined are in a definable ratio to each other. Preferably, this ratio is 1:1.

[0082] If none of the above plausibility criteria are met, the mean transit time mtt can be varied in step 330 by increasing it by one increment, for example 0.5. This increase continues until one of the plausibility criteria is met, and other steps of the algorithm are executed. Otherwise, if a defined maximum allowable value for mtt is reached in step 270, such increase is stopped in step 280. In this case, mtt cannot be determined and the measurement is considered invalid.

[0083] In step 340, the blood volume BV and blood flow rate BF are determined based on the determined mean transit time mtt. To determine the blood volume, the time characteristic of the indicator concentration values ​​cICG(t) can be approximately described by an exponential function in the time interval t1>0 to t2>t1, and then this exponential function can be extrapolated to time t=0. Furthermore, the blood volume in the organ tissue under consideration can be considered to be proportional to the area under the inflow function i(t) and the outflow function o(t), which can be calculated by integration.

[0084] It is to be understood that the embodiments described herein are exemplary, and that the components can be arranged, substituted, combined, and designed in a wide variety of different configurations, all of which are intended to be within the scope of the present disclosure. Accordingly, the foregoing description of exemplary embodiments has been presented for purposes of illustration and description and is not intended to be exhaustive. Rather, it is intended that the scope of the present invention be defined by the claims. [Prior art documents] [Patent documents]

[0085] [Patent Document 1] U.S. Patent No. 6,456,862 [Patent Document 2] U.S. Patent No. 7,529,576 [Patent Document 3] U.S. Patent No. 6,223,069

Claims

1. 1. A method for determining absolute concentration values, blood flow, or blood volume of a component in tissue of an organ, comprising: irradiating the tissue with radiation having at least one wavelength in the near-infrared spectrum and generating a measurement signal responsive to the detected intensity of radiation emerging from the tissue by near-infrared spectroscopy; converting the temporal variations in the detected intensity of the radiation emerging from the tissue into absolute concentration values ​​of components using a system matrix and an evaluation algorithm implemented in an evaluation unit; introducing an indicator comprising a dye having an absorption peak in the near-infrared spectrum and determining the concentration of the indicator in the tissue over time; deriving a mean transit time mtt from the concentration values ​​of the indicator over time using at least one transport function g(t) characterizing blood flow in the tissue; calculating blood flow and / or blood volume from the time course of said concentration values ​​of said indicator and / or from parameters derived therefrom; Equipped with The evaluation algorithm comprises: a) receiving the measurement signal based on the emitted and detected portion of the emitted radiation having at least one wavelength in the near infrared spectrum as a measurement signal to be transmitted to the evaluation unit; b) determining absolute concentration values ​​of at least hemoglobin, deoxyhemoglobin, background, or water components in the tissue; c) determining from the measurement signal the time course of the concentration of the indicator in the tissue; d) iteratively determining inflow and outflow functions i(t) and o(t) indicative of blood flow in said tissue using said transport function g(t) having said determinable mean transit time mtt until a termination criterion is reached; e) fitting the iteratively determined inflow function i(t) and the iteratively determined outflow function o(t) with a lognormal function or another function representing the tissue passage system; f) calculating the blood volume in the tissue using either the function determined in step c) or e); g) calculating the blood flow rate in the tissue as the quotient of the blood volume calculated in step f) and the mean transit time mtt determined in step d). It is programmed to In step f), the blood volume in the tissue is determined from the area under the inflow function i(t) and the outflow function o(t).

2. 2. The method of claim 1, wherein the system matrix is ​​calibrated using known concentration values ​​of components in the tissue, measurable concentration values ​​of components in healthy tissue, or definable boundary conditions for constraining concentration values ​​of components in the tissue.

3. 2. The method of claim 1, wherein the measurement signal corresponds to an absolute concentration value of one or more of hemoglobin, deoxyhemoglobin, water, background, or the indicator, allowing for determination of the blood volume or the blood flow in the tissue.

4. The iterative determination of the inflow function i(t) comprises a plurality of steps, in each step an approximation of the inflow function i(t) is calculated according to the following formula: [Equation 10] where d / dt(cICG(t)) is the determinable time change in the concentration of the indicator in the tissue, and o(t) is the efflux function determinable from the deconvolution of the convolution integral of the inflow function i(t) and the transport function g(t): [0011] 2. The method of claim 1 .

5. 2. The method of claim 1, wherein the termination criterion for determining the mean transit time mtt is defined by a plausibility criterion for the inflow function i(t) and the outflow function o(t).

6. 6. The method of claim 5, wherein the plausibility criterion can be defined as the distance between the center of gravity of the inflow function i(t) and the center of gravity of the outflow function o(t), and corresponds to the determinable mean transit time mtt.

7. 6. The method of claim 5, wherein the plausibility criterion can be defined as the ratio of the area under the inflow function i(t) to the area under the outflow function o(t).

8. 8. The method of claim 7, wherein the ratio is 1:

1.

9. 1. An apparatus for determining absolute concentration values ​​of a component, blood flow, or blood volume in tissue of an organ for use with an indicator introduced into the tissue via an infusion device, said indicator comprising a dye having an absorption peak in the near infrared spectrum, said apparatus comprising: a sensor arrangement for emitting radiation having at least one wavelength in the near-infrared spectrum into the tissue and for generating, by near-infrared spectroscopy, a measurement signal responsive to a detected intensity of radiation emerging from the tissue; an evaluation unit having a processor and a memory for storing a system matrix, said evaluation unit comprising: converting the temporal changes in the detected intensity of the radiation emerging from the tissue into absolute concentration values ​​of components using a system matrix; determining a time course of concentration values ​​of the indicator in the tissue; deriving a mean transit time mtt from the time course of concentration values ​​of the indicator using at least one transport function g(t) characterizing blood flow in the tissue; Calculating blood flow or blood volume from the time course of the indicator concentration values ​​or a parameter derived therefrom. an evaluation unit programmed to execute an evaluation algorithm; Equipped with The evaluation unit further comprises: a) receiving a measurement signal based on the emitted and detected portion of the emitted radiation having at least one wavelength in the near infrared spectrum; b) determining absolute concentration values ​​of at least hemoglobin, deoxyhemoglobin, background, or water components in said tissue; c) determining from the measurement signal the time course of the concentration of the indicator in the tissue; d) iteratively determining inflow and outflow functions i(t) indicative of blood flow in said tissue using a transport function g(t) having a determinable mean transit time mtt until a termination criterion is reached; e) fitting the iteratively determined inflow function i(t) and the iteratively determined outflow function o(t) with a lognormal function; f) calculating the blood volume in the tissue using either the function determined in step c) or e); g) calculating the blood flow in the tissue as the quotient of the blood volume calculated in step f) and the mean transit time mtt determined in step d). It is programmed to The evaluation unit is further programmed to determine the blood volume in the tissue from the area under the inflow function i(t) and the outflow function o(t) in step f).

10. 10. The apparatus of claim 9, wherein the system matrix is ​​calibrated using known concentration values ​​of the component in the tissue, measurable concentration values ​​of the component in healthy tissue, or definable boundary conditions for constraining the concentration values ​​of the component in the tissue.

11. 10. The device according to claim 9, wherein the measurement signal corresponds to absolute concentration values ​​of one or more of hemoglobin, deoxyhemoglobin, water, background, or the indicator, and the evaluation algorithm allows for the determination of the blood volume or the blood flow in the tissue.

12. The evaluation unit is further programmed to iteratively determine the inflow function i(t) in several steps, in each step an approximation of the inflow function i(t) is calculated according to the following formula: [0012] where d / dt(cICG(t)) is the determinable time course of the indicator concentration in the tissue, and o(t) is the efflux function that can be determined from the deconvolution of the convolution integral of the inflow function i(t) and the transport function g(t) by [0013] 11. The device of claim 10.

13. 10. The apparatus of claim 9, wherein the evaluation unit is further programmed such that the termination criterion for determining the mean transit time mtt is defined by a plausibility criterion of the inflow function i(t) and the outflow function o(t).

14. 14. The apparatus of claim 13, wherein the evaluation unit is further programmed such that the plausibility criterion is definable as a distance between the center of gravity of the inflow function i(t) and the center of gravity of the outflow function o(t), corresponding to the determinable mean transit time mtt.

15. 14. The apparatus according to claim 13, wherein the evaluation unit is further programmed such that the plausibility criterion is definable as a ratio of an area under the inflow function i(t) to an area under the outflow function o(t).

Images