WO2012038168A1 - Amélioration de la communication avec le patient dans un système irm - Google Patents

Amélioration de la communication avec le patient dans un système irm Download PDF

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Publication number
WO2012038168A1
WO2012038168A1 PCT/EP2011/064313 EP2011064313W WO2012038168A1 WO 2012038168 A1 WO2012038168 A1 WO 2012038168A1 EP 2011064313 W EP2011064313 W EP 2011064313W WO 2012038168 A1 WO2012038168 A1 WO 2012038168A1
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Prior art keywords
stage
gradient
signal
acoustic signal
vibration
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PCT/EP2011/064313
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German (de)
English (en)
Inventor
Mario Bechtold
Peter-Christian Eccardt
Marco Friedrich
Stefan Nunninger
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Siemens Aktiengesellschaft
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Publication of WO2012038168A1 publication Critical patent/WO2012038168A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/283—Intercom or optical viewing arrangements, structurally associated with NMR apparatus
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
    • G01R33/3854—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils means for active and/or passive vibration damping or acoustical noise suppression in gradient magnet coil systems

Definitions

  • the invention relates to the improvement of disturbed speech signals for patient communication on a magnetic resonance imaging (MRI) scanner.
  • MRI magnetic resonance imaging
  • the patient is inside the tube of the MRI while the operator of the MRI is scanning the MRI
  • a doctor or an MTA located in an adjacent control room in which the control console of the MRI is installed. Communication between operator and patient is not possible directly because the MRI is located in a closed, soundproofed examination room. Therefore, as a rule, a communication system with a microphone in the examination room and a loudspeaker in the control room is provided so that voice utterances of the patient can be picked up by the microphone and transmitted to the loudspeaker.
  • An MRI scan typically consists of one or a whole series of MRI scans, in which the data required for imaging is captured by the known sequence of RF and gradient fields, and examination pauses. This device allows a sufficient understanding of the patient at least during the examination breaks, i. in the period between two measurements.
  • the MRI device basically generates a strong background noise, which is also recorded by the microphone. This significantly interferes with or prevents communication from the patient to the operator during an exam.
  • the characteristic of the noise depends on the type of examination selected, in particular on the set measurement sequence and the measurement parameters.
  • the power of the background noise compared to the performance of the patient speech sound at the microphone depends on the type of examination and the microphone design. At typical In contrast to standard MRI equipment, the power of signal components of the microphone signal due to recorded background noise is often significantly greater than the power of signal components due to the recorded speech sound, which greatly reduces the intelligibility of the patient's speech via the recorded microphone signal.
  • a reference signal for the noise in the immediate vicinity of the gradient coils of the MRI is used to generate a replica of the noise in the microphone signal.
  • This replica is used to reduce the amount of noise in the microphone signal by subtracting the microphone signal.
  • the invention therefore provides a method for reduction a noise component in an acoustic signal recorded during an RT measurement, wherein at least one gradient current is generated at least temporarily during the MRT measurement, wherein in the method
  • the parameter is used in a first stage of a signal processing to a caused due to the gradient current noise in the recorded acoustic
  • the estimated amount of noise is used to correct the recorded acoustic signal. For example. can be subtracted from the recorded acoustic signal to correct the estimated noise component.
  • a parameter which represents a measure of the respective gradient current is determined individually.
  • the respective parameter is used in the first stage of the signal processing in order to estimate an individual noise component due to the respective gradient current in the recorded acoustic signal in particular model-based.
  • the estimated individual noise components are then used to correct the recorded acoustic signal. For example.
  • the individual estimated noise components can be subtracted from the recorded acoustic signal.
  • the first stage comprises a first sub-stage and a second sub-class, wherein
  • the parameter determines a vibration value which is a measure of a gradient-related vibration of a surface; represents the MRT device, in particular the cladding surface, wherein the vibration is at least a part of the cause of the noise component, and
  • the estimation of the noise caused by the gradient current in the recorded acoustic signal in the second sub-stage is based on the determined vibration value.
  • a multiplicity of gradient currents is generally generated at least temporarily.
  • a parameter representing the respective gradient current is determined individually, wherein in the first sub-stage the respective parameter is used to calculate an individual vibration value, wherein the individual vibration values are each a measure of one with the respective gradient current represent coherent vibration of the surface of the MRI device.
  • the vibration value is calculated from the individual vibration values, for which purpose the individual vibration values can, for example, be summed up.
  • the respective gradient current can be measured in a first embodiment, so that the parameter representing the gradient current is the corresponding measurement signal.
  • the parameter representing the respective gradient current can be calculated on the basis of the measurement method underlying the MRT measurement and the selected measurement parameters.
  • a vibration value which is a measure of a vibration of a surface of the MRI apparatus, in particular the cladding surface, wherein the vibration represents at least part of the cause of the noise component.
  • the vibration value is used in a first stage of a signal processing in order to estimate the noise component in the recorded acoustic signal in particular model-based.
  • the estimated amount of noise is used to correct the recorded acoustic signal. For this purpose, the estimated noise component can be subtracted from the recorded acoustic signal.
  • the estimation of the noise component is preferably model-based.
  • the estimated amount of noise or estimated noise is subtracted from the recorded acoustic signal.
  • the corrected in the first stage acoustic signal is fed to a second stage of signal processing in which the corrected acoustic signal is reduced using a one-channel algorithm to residual noise and / or independent of the gradient currents noise.
  • Suitable time domain algorithms are described, for example, in the above-mentioned US Pat. No. 4,691,030 A and US Pat. No. 2005283068 A1.
  • a signal processing device for reducing a noise component in an acoustic signal recorded during an MRT measurement on an MRI apparatus, in particular for a communication system of an MRI apparatus, wherein during the MRI measurement at least one gradient current (14 ⁇ is generated at least temporarily points
  • the arithmetic unit is designed to estimate a noise component due to the gradient current in the recorded acoustic signal, in particular based on a model Noise is used to record the recorded acoustic Correct signal.
  • the estimated noise component can be subtracted from the recorded acoustic signal.
  • the MRI apparatus has a plurality of gradient coils, and during the MR measurement, a corresponding plurality of gradient currents are generated at least temporarily.
  • the arithmetic unit can therefore have a number of first filters corresponding to the number of gradient coils, wherein the parameter signal comprises a number of individual parameter signals corresponding to the number of gradient currents, which respectively represent a measure of the respective gradient current and which can be fed to the first filters.
  • the first filters are designed to estimate an individual noise component due to the respective gradient current in the recorded acoustic signal, in particular model-based.
  • the first stage has a computing element in which the recorded acoustic signal can be corrected on the basis of the estimated individual noise components. For example. For this purpose, the individual estimated noise components can be subtracted from the recorded acoustic signal.
  • the arithmetic unit has a first and a second sub-stage, wherein
  • the first sub-stage has a filter device to which the parameter signal can be fed
  • the filter device is designed to determine a vibration value based on the parameter signal, which represents a measure of a gradient current related vibration of a surface of the MRI device, in particular the cladding surface, wherein the vibration represents at least part of the cause of the noise component, and
  • the second sub-stage is designed to estimate the caused due to the gradient current noise in the recorded acoustic signal based on the determined vibration value in particular model-based. If the MRI apparatus has a multiplicity of gradient coils and a corresponding multiplicity of gradient currents is generated at least temporarily during the MRT measurement, the filter device of the first sub-stage has a number of second filters corresponding to the number of gradient coils, in which
  • the parameter signal comprises a number of individual parameter signals corresponding to the number of gradient currents, each of which represents a measure of the respective gradient current and which can be fed to the second filters,
  • the second filters are designed to respectively estimate an individual vibration value, in particular model-based, wherein the individual vibration values each represent a measure of a vibration of the surface of the MRI apparatus which is related to the respective gradient current, and
  • the first sub-stage comprises a computing element for calculating the vibration value from the individual vibration values.
  • An alternative embodiment of the signal processing device for reducing a noise component in an acoustic signal recorded on an MRI apparatus during an MRI measurement, in particular for a communication system of an MRI apparatus, comprises:
  • At least one sensor which can be attached to a surface of the MRI apparatus, in particular on the cladding surface, for determining a vibration value that represents a measure of a vibration of the surface of the MRI apparatus, wherein the vibration represents at least a part of the cause of the noise component .
  • a first stage with an arithmetic unit wherein the vibra- tion value can be fed to the arithmetic unit and the arithmetic unit is designed to estimate, based on the vibration value, the noise component in the recorded acoustic signal, in particular model-based, and - A computer to which the recorded acoustic signal and the estimated noise component can be supplied and in which the recorded acoustic signal is correctable based on the estimated noise component.
  • the signal processing device may have a second stage, to which the acoustic signal corrected in the first stage can be supplied, the second stage being designed to reduce the corrected acoustic signal using a single-channel algorithm for residual interference noise and / or noise free from the gradient currents ,
  • the interference noises in the input signal of the communication system are modeled by parallel arrangement of a plurality of adaptive filters, ideally in each case one filter for each measurement signal of the gradient currents or for each gradient coil.
  • the vibrations of the cladding surface of the MRI system are modeled in a two-stage, model-based approach. From this conclusions about the noise in the input signal of the communication system are drawn. In this embodiment, all relevant noise-generating mechanisms of the MRI system are advantageously detected, and not just the dominant source of interference, ie the vibrations of the gradient coil structure.
  • non-linear signal processing approaches for example the realization of a Hammerstein model, for example with a power filter structure
  • the invention realizes an integration of several signal processing algorithms into a total solution, consisting of model-based approaches in the first stage, followed by a single-channel noise reduction in the second stage.
  • the multistage improvement of the speech signal in the communication channel means that the solution according to the invention simultaneously achieves the high reduction of the noise by algorithms of the first stage as well as the reduction of any residual noise and of further disturbances uncorrelated to the gradient currents in algorithms of the second stage can.
  • FIG. 1 shows an MRI system with a communication system
  • Figure 2 shows a first embodiment of the first stage of a
  • Figure 3 shows a second embodiment of the first stage of a
  • FIG. 1 shows a schematic diagram of a sectional view of an MRI apparatus 1 with the relevant parts of the invention for explaining the invention.
  • the MRI 1 is accommodated in an examination room 2, which is cable-insulated from a control room 3.
  • the patient 5 to be examined lies in the tube 6 of the MRI 1.
  • a communication system 21 with a microphone 8 and an electroacoustic transducer 9, for example.
  • a speaker provided.
  • the microphone 8 picks up the voice utterances 7 of the patient 5, so that they can be played back via the loudspeaker 9.
  • the signal components S r due to noise can, depending on the type of the selected MRT measurement and microphone implementation, have a considerably higher power than the signal components S sp by voice utterances, so that the transmission or intelligibility of the voice utterances 7 in the control room 3 is considerably disturbed.
  • the interference noises 10 are caused by alternating electric currents in the gradient coils 12 of the MRT device 1.
  • An MRT device 1 contains a gradient coil system 12 with typically several gradient coils 12/1, 12/2, 12/3 (not shown in detail here), which gradient currents 14/1, 14/2, 14 generated individually by a power amplifier 13 / 3 are flown through.
  • the currents 14/1, 14/2, 14/3 associated with the different gradient coils 12/1, 12/2, 12/3 can flow simultaneously and / or sequentially depending on the measurement.
  • the gradient currents 14 lead to an eddy current induction in adjacent conductive structures, for example in the vessel 16 for the superconducting coils and in RF antennas 17 on the cladding 18 of the MRT system 1.
  • the induced eddy currents lead by interaction with the basic magnetic field of the MR MR system 1 and with the gradient magnetic fields of the gradient coils 12 to vibration excitations of various parts of the system, which in turn noise emissions are emitted from these parts. The latter interaction is usually a nonlinear effect.
  • the illustrated parts of the MRI system are typically located together under the panel 18 of the MR system l r, for example, a flat plastic panel.
  • the panel 18 is excited mechanically and acoustically by the underlying parts of the system to vibrate, resulting in the emission of the noise 10 in the examination room.
  • the recorded by the microphone 8 in üntersuchungsraum Störschall 10 of the MR system 1 is essentially the radiated from this panel 18 sound.
  • a communication system 21 is provided with a microphone 8 and a speaker 9.
  • further components such as amplifiers or the like.
  • Microphone signal S M contained noise or 10 of the noise component S r.
  • the noise component S n is estimated in the microphone signal S M , based on a determination of the currents 14/1, 14/2, 14/3 in the gradient coils 12/1, 12/2, 12/3 of the MRT 1. Since a plurality of individually supplied gradient coils are usually present in an MRI apparatus, the gradient currents describing parameters or parameter signals 25/1, 25/2, 25/3 are determined individually for each of the gradient coils. For this purpose, a device 35, the gradient currents 14/1, 14/2, 14/3 are supplied.
  • the currents 14 in the device 35 for example a computer, since the currents required to supply the gradient coils depend on the selected measuring method, for example a spin echo Sequence or a FLASH sequence, and depending on the selected or predetermined measurement parameters such as, for example, the resolution.
  • the parameters 25 would be the calculated currents needed to perform the measurement method.
  • the computer 35 can then also be the control computer 36 to be operated by the operator 4 in the control room 3.
  • the parameters 25 are the above-mentioned measuring signals.
  • the gradient signals representing the measuring signals 25/1, 25/2, 25/3 are used to individually for each of the gradient coils 12/1, 12/2, 12/3 the From her caused noise component S n , i, Sn,?, S n , 3 in the microphone signal S M estimate.
  • FIG. 2 shows a schematic representation of the first stage 23, in which the use of three gradient coils
  • a respective filter structure 26/1, 26/2, 26/3 is identified, which determines the deviation between the noise component S n , i, S n , 2 / S n , 3 of the respective gradient coil 12/1 estimated in the filter structure , 12/2, 12/3 and the present in the microphone signal S M real noise component S n minimized.
  • each of the filter structures in a statistical analysis based on a correlation between the respective input signal 25/1, 25/2, 25/3 of the filter structure 26/1, 26/2, 26/3 and the microphone signal S M to the respective Measurement signal 25/1, 25/2, 25/3 associated noise component S n , i, S ri , 2 , S R , 3 model-based estimated.
  • the noise component S n in the microphone signal S K is finally by subtracting the estimated noise components S c , i > Sn, 2 / S n , 3 of the respective gradient coil 12/1, 12/2, 12/3 from the microphone signal S M in a summation 33rd largely reduced, so that at the output of the summation element 33 and the first stage 23, a corrected microphone signal S * 'is present.
  • Speech signal portions S sp of the microphone signal S K are not affected by this processing step and are after reduction of the noise S r. perceptible with significantly improved intelligibility.
  • the filter structures 26/1, 26/2, 26/3 can each be implemented as a parallel combination of a plurality of adaptive filters whose transmission behavior can be changed so that the deviation between the estimated noise component Sr., i / S n , 2, S n , 3 and real existing noise S n in the micro- fonsignal SM is minimized as described above.
  • Such adaptive filters are known per se.
  • the system behavior of the filter can be kept temporarily or permanently constant, but this leads to an increase in the deviations and thus the remaining noise in the communication channel with changes in the noise generating system or the characteristic of the noise.
  • error-minimizing filters 26/1, 26/2, 26/3 results when the transmission behavior of the filter corresponds to the transmission behavior of the system path between measuring signal 25 of the gradient current and the associated noise component in the microphone signal to a good approximation.
  • this is subdivided into a plurality of sub-stages 27, 28.
  • a schematic representation of this alternative embodiment is given in FIG. The subdivision is based on the observation that the system properties of parts of the noise-generating system are slowly changing over time, while the system properties of other parts may be subject to rapid temporal changes. Furthermore, this subdivision is based on the observation that noise components S 1 in the microphone signal S M , which are caused by different parts and transmission paths of the MRI system 1 and by different gradient currents 14, radiate essentially from one common surface 18 into the examination space 2 become. The system properties of this portion of the noise generating system may be considered to be slowly variable or even constant for the application discussed herein.
  • a first sub-stage 27 contains a parallel arrangement of filters 28/1, 28/2, 28/3 and at least one summation element 29 which, based on the measuring signals 25/1, 25/2, 25/3 of the gradient currents 14/1, 14/2, 14/3 simulate the vibration of the cladding surface 18.
  • a first sub-stage 27 contains a parallel arrangement of filters 28/1, 28/2, 28/3 and at least one summation element 29 which, based on the measuring signals 25/1, 25/2, 25/3 of the gradient currents 14/1, 14/2, 14/3 simulate the vibration of the cladding surface 18.
  • the vibrations of the panel 18 of the MR system 1, ie the parameter S n , vib / can also be detected by means of a sensor 34, for example an acceleration sensor , which is mounted on a suitable location of the panel 18 and outputs a sensor signal S se n, which is a measure of the vibration excitation of the cladding surface 18.
  • a sensor 34 for example an acceleration sensor
  • S se n a sensor signal
  • the signal S R , vib to be estimated can be used as a suitable combination of the Sensor signal S ser . and the output signal S n , sum of the summation element 29 are calculated. For example. could be a weighted averaging used here.
  • a second sub-stage 30 contains a further filter 31, which generates an estimate of the noise component S N in the microphone signal S M based on the modeled vibration excitation S n , vi b of the panel 18 of the MRT system 1.
  • Noise S N in the microphone signal S M are reduced by subtracting the estimated noise components of the microphone signal S M in a summing 32.
  • the output signal of the summation element 32 or the first stage 23 also corresponds in the embodiment of FIG. 3 to a corrected microphone signal S "'.
  • Speech signal portions S SP of the microphone signal S M are not affected by this processing step and are perceptible after reduction of the noise S N with much improved intelligibility.
  • An expedient embodiment of the second sub-stage 30 takes place, for example, as an adaptive filter 31, which detects the deviation between the estimated noise S N and that in FIG
  • Microphone signal SM real existing noise component minimized.
  • the system behavior of the filters in this embodiment of the first stage of the signal processing can be kept temporarily or permanently constant, but this can lead to an increase in the deviations and thus the remaining noise in the communication channel with changes in the noises generating system or the characteristic of the noise , It has also been observed that the generation of noise components in the microphone signal can not be fully described by linear system behavior.
  • the interaction between the eddy currents induced by the gradient currents and the gradient currents themselves constitutes a non-linear component.
  • the above-described filters 26, 28, 31 of the first and second embodiments can therefore expressly include both linear and non-linear processing steps.
  • nonlinear filters 28/1, 28/2, 28/3 for the first sub-stage 27 and a linear filter 31 for the second sub-stage 30 may be used.
  • the first sub-stage 27 then forms the vibrations of the cladding surface 18 of the
  • the second stage 30 estimates the recorded background noise 10 after the acoustic path with the aid of a linear filter 31.
  • the intelligibility of the patient language 7 in the microphone signal S M can be significantly improved even if the power of the signal components of noise 10 of the MRI is significantly greater than that of the patient language. 7
  • disturbing residual interference noise S n , res t may still be present after the first stage of the signal processing, ie the proportion S n of the noise in the microphone signal S M sets together with the reducible with the first stage 23 portion, hereinafter denoted by S n , o, and the residual interference noise corresponding proportion S n , rest -
  • the corrected microphone signal S M ' may thus also contain a component S n , rest ,
  • uncorrelated to the gradient currents 14 noise 10c in the examination room 2 as caused for example by an air conditioner or ventilation 19 or by the helium pump 20 of the MRI system 1, not reduced.
  • Signal enhancements in the frequency domain are achieved, for example, by an individual weighting of frequency bands, so that frequency bands having a dominant noise component are strongly attenuated, while frequency bands having a dominant voice signal component are output almost unattenuated.
  • the output signal S M * 'of the second stage 24 is then an improved estimate of the undisturbed speech signal S sp .
  • the peculiarity of the presented multilevel solution is that after a previous reduction of the noise with the aid of the first stage 23 now also single-channel algorithms can be applied, which were previously not directly applicable due to the low signal-to-noise ratio of the microphone signal S M. ,
  • the single-channel reduction of the residual interference noise and incorrelated interference in the second stage 24 leads to a further improvement in the intelligibility and quality of the patient language 7 in the output signal S M '' of the communication system 21.
  • the improved signal S M '' on the speaker rather 9 is output to the operator 4.
  • the operator 4 of the MRI system 1 can understand the examined person 5 during examination breaks as well as during an MRI measurement.
  • the models used for the respective estimation of the noise components in the various filters for simulating the system sections can be determined, for example, with the aid of corresponding reference measurements, wherein the models can be obtained, for example, from identification measurements.
  • a physical modeling is basically possible, but due to the complexity and the variance between the systems comparatively expensive.

Abstract

L'invention concerne l'amélioration de signaux vocaux parasités pour la communication avec le patient dans un système d'imagerie par résonance magnétique (IRM). Les parasites reposent sur l'effet connu que, en raison des courants à gradients, il se produit des vibrations audibles et l'émission de son parasite, de sorte qu'un signal acoustique reçu par un microphone dans un espace d'examen, se compose de fractions bruits parasites et d'un signal vocal émanant d'un patient. Dans le but de réduire la fraction bruits parasites, les courants à gradients sont mesurés et estimés de façon modélisée pour des fractions bruits parasites correspondant individuellement à chaque courant à gradient. Au moyen des fractions bruits parasites individuelles, le signal acoustique reçu est corrigé. En variante, la vibration de la surface du revêtement du système IRM est simulée, également de façon modélisée, au moyen des courants à gradients et, à partir de cela, la fraction bruits parasites est déterminée.
PCT/EP2011/064313 2010-09-21 2011-08-19 Amélioration de la communication avec le patient dans un système irm WO2012038168A1 (fr)

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DE102010041146A DE102010041146A1 (de) 2010-09-21 2010-09-21 Verbesserung der Patientenkommunikation in einem MRT
DE102010041146.9 2010-09-21

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CN112863533A (zh) * 2020-12-29 2021-05-28 深圳市联影高端医疗装备创新研究院 医疗成像设备中语音信号获取方法、装置、设备和介质

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