EP2840809A2 - Commande de l'intensité d'effet d'un microphone directionnel binaural - Google Patents

Commande de l'intensité d'effet d'un microphone directionnel binaural Download PDF

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Publication number
EP2840809A2
EP2840809A2 EP14161630.0A EP14161630A EP2840809A2 EP 2840809 A2 EP2840809 A2 EP 2840809A2 EP 14161630 A EP14161630 A EP 14161630A EP 2840809 A2 EP2840809 A2 EP 2840809A2
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EP
European Patent Office
Prior art keywords
signal
audio signals
hearing aid
processing device
signal processing
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP14161630.0A
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German (de)
English (en)
Other versions
EP2840809B1 (fr
EP2840809A3 (fr
Inventor
Marc Aubreville
Eghart Fischer
Homayoun Kamkar Parsi
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Priority to EP18248116.8A priority Critical patent/EP3490273A1/fr
Priority to EP18183297.3A priority patent/EP3410745A1/fr
Publication of EP2840809A2 publication Critical patent/EP2840809A2/fr
Publication of EP2840809A3 publication Critical patent/EP2840809A3/fr
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Publication of EP2840809B1 publication Critical patent/EP2840809B1/fr
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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/405—Arrangements for obtaining a desired directivity characteristic by combining a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/20—Processing of the output signals of the acoustic transducers of an array for obtaining a desired directivity characteristic
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/20—Processing of the output signals of the acoustic transducers of an array for obtaining a desired directivity characteristic
    • H04R2430/21—Direction finding using differential microphone array [DMA]
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/20—Processing of the output signals of the acoustic transducers of an array for obtaining a desired directivity characteristic
    • H04R2430/23—Direction finding using a sum-delay beam-former

Definitions

  • the invention relates to a method for operating a hearing aid system and a hearing aid system having at least two hearing aid devices, between which a signal path is provided, and with at least one signal processing unit which is provided for processing audio signals.
  • hearing impairment affects both ears
  • the hearing impaired should be provided binaurally with hearing aids.
  • Modern hearing aids have signal processing algorithms which automatically vary the parameters of the hearing aids as a function of the hearing situation. In the case of binaural care, the hearing situation is assessed on both ears.
  • Noise and noise are omnipresent in everyday life and make speech communication more difficult, especially if there is an impairment of natural hearing. Therefore, techniques are desirable that suppress noise and noise, but change the desired sounds and tones, hereinafter also referred to as useful signals, as little as possible.
  • One possible way of suppressing unwanted noise is spatial filtering. If the noise and the useful noises come from different directions on the wearer of a hearing aid, it is possible to suppress unwanted noise by a different sensitivity of the hearing aid in different directions in relation to the hearing aid and its wearer. In the case of binaural hearing aid systems, it is particularly appropriate to combine the signals of the two hearing aid devices of the hearing aid system in order to achieve a directivity.
  • the carrier has been customary for the carrier to manually switch between different modes of operation having either a directional characteristic or an omnidirectional sensitivity.
  • the object of the present invention is therefore to provide a method for operating a hearing aid system and a hearing aid system, by means of which a spatial noise suppression is better and more effective.
  • the method according to the invention relates to a method for operating a hearing aid system with at least two hearing aid devices for the purpose of the arrangement on both sides of a head of a wearer.
  • the hearing aids have a transducer for receiving an acoustic signal and conversion into a respective first audio signal.
  • the hearing aid system has a signal processing device for processing audio signals and a signal connection for transmitting a first audio signal from each hearing aid device to the signal processing device.
  • the signal processing device evaluates a signal component from a preferred direction with respect to the head in the first audio signals and generates with the first audio signals a first binaural directional microphone signal and adjusts its directional characteristic depending on the evaluation.
  • the hearing aid system evaluates signal components from the preferred direction, it can be determined with certainty whether a signal source is actually present in the preferred direction. It is thereby avoided in an advantageous manner to activate a directional characteristic when no signal source is present in the preferred direction.
  • the hearing aid system according to the invention for carrying out the method according to the invention shares its advantages.
  • the preferred direction is mapped into a plane of symmetry of the two hearing aid devices.
  • the preferred direction is aligned in the direction of the head of the wearer by this transformation.
  • the subsequent steps can be designed in the preferred direction in the viewing direction and do not have to be adapted to a respectively changing preferred direction.
  • the signal processing device determines a minimum of the level of the first audio signals or a minimum of the level of the first preprocessed audio signals. From the minimum and a second reference signal with a reduced sensitivity in the preferred direction the signal processing device then forms a quotient to evaluate the signal component.
  • the determination of the minimum of the levels and the quotient allows in a simple manner to determine a measure of noise from one direction unequal to the preferred direction and thus to adjust the directivity of the auditory situation in the sequence.
  • the signal processing device determines a quotient of a first reference signal with directivity in the preferred direction and a second reference signal with a reduced sensitivity in the preferred direction for evaluating the signal component from a preferred direction.
  • the first reference signal is a weighted sum of the first audio signals of both hearing aid devices.
  • the formation of a weighted sum of the first audio signals of the two hearing aids makes it possible with little computational effort to provide a signal that, for example, has a directional characteristic with a maximum of sensitivity in the direction of viewing of the wearer of the hearing aid.
  • a weighting of the first audio signals takes place adaptively such that an energy of the weighted sum is minimized.
  • the adaptive adjustment of the coefficients already reduces the amount of noise by selecting a combination with the lowest energy of the noise.
  • the second reference signal is a weighted difference of the first audio signals of both hearing aid devices.
  • the formation of a weighted difference of the first audio signals of the two hearing aids makes it possible with little computational effort to provide a signal that, for example, has a directional characteristic with a minimum of sensitivity in the direction of viewing of the wearer of the hearing aid.
  • the second reference signal is a signal of a binaural eight which has a minimum in the direction of the preferred direction.
  • a binaural eight is a signal that is generated from the difference in the signals of two spaced omnidirectional or monaural directional microphones.
  • the binaural eight signal is particularly easy to generate and advantageously exhibits a pronounced minimum of sensitivity in a plane centered between the hearing aids and parallel to the line of sight. This is particularly advantageous if the preferred direction lies in this plane.
  • the signal processing device increases the directional characteristic of the binaural directional microphone with a rising value of the quotient.
  • An increasing value of the quotient indicates that there is a signal in the preferred direction which is lifted out of the ambient noise.
  • An increase in the directional characteristic then advantageously emphasizes this signal with respect to the ambient noise, which are simultaneously damped by the stronger directional characteristic.
  • the signal processing device determines a cross-correlation of the first audio signals of both hearing aid devices in order to evaluate the signal component.
  • the cross-correlation it can be determined to what extent the two signals are similar to each other and therefore originate from a common source. If the cross-correlation is particularly high, the two signals are almost identical and can therefore be assigned to a source with the same distance from both microphones, which advantageously lie in a preferred direction in the direction of the carrier in this preferred direction.
  • the signal processing device increases the directional characteristic of the binaural directional microphone with increasing cross-correlation.
  • An increasing value of the cross-correlation indicates that there is a signal source in the preferred direction.
  • An increase in the directional characteristic then advantageously emphasizes this signal source with respect to the ambient noise, which are simultaneously damped by the stronger directional characteristic.
  • the evaluation of the signal components from the preferred direction in the first audio signals for at least two different frequency ranges are made individually and the directional characteristic of the first binaural directional microphone signal for each frequency range is set individually depending on the rating.
  • a different evaluation and directional characteristic for different frequency ranges advantageously makes it possible to take account of different propagation conditions for different frequencies or to treat different signal sources differently in different frequency ranges.
  • Fig. 1 shows the basic structure of a hearing aid system 100 according to the invention.
  • the hearing aid system 100 has two hearing aid devices 110, 110 '.
  • a hearing aid housing 1, 1 'for carrying behind the ear are one or more microphones 2, 2' installed for recording the sound or acoustic signals from the environment.
  • the first acoustic signals are, for example, analog or digital electrical signals.
  • a signal processing unit 3, 3 ' which is also integrated in the hearing aid housing 1, 1', processes the first audio signals.
  • the output signal of the signal processing unit 3, 3 ' is transmitted to a loudspeaker or receiver 4, 4', which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular of the signal processing unit 3, 3 ' takes place by means of a likewise integrated into the hearing aid housing 1, 1' battery 5, 5 '.
  • the hearing aid system 100 has a signal connection 6, which is designed to transmit a first acoustic signal from the signal processing device 3 to the signal processing device 3 '. It is provided in the preferred embodiment that also signal processing device 3 'transmits a first acoustic signal to the signal processing device 3 in the opposite direction. Furthermore, it is conceivable for the signals of several or all of the microphones 2, 2 'to be transmitted to the other hearing aid device 110, 110' in each case.
  • a signal connection 6 are wired, optical or wireless connections such. Bluetooth conceivable.
  • the method according to the invention can also be used in other hearing aid devices such as, for example, an IDO (in-the-ear) hearing aid.
  • Fig. 2 shows a schematic arrangement of a hearing aid system according to the invention, its carrier and the signal sources in a plan view from above.
  • the carrier 201 of the hearing aids 110, 110 ' is arranged in the center of a polar coordinate system 200.
  • the carrier 201 carries the hearing aid devices 110, 110 'in accordance with the application, for example in the case of HDO hearing aid devices behind the respective ear or in the case of IDO hearing aid devices in the respective auditory canal.
  • the viewing direction of the carrier 201 is forward, which corresponds to 0 degrees in the polar diagram. In the following example, the preferred direction is assumed to be parallel to the viewing direction. However, it is also conceivable that the preferred direction is arranged at an angle to the viewing direction.
  • the preferred direction is determined in advance by an adaptive method and the first audio signals are preprocessed in such a way that the preferred direction is mapped or transformed to the direction 0 degrees.
  • a preprocessing could be done for example by adjusting the amplitude and phase of the first audio signals.
  • Subsequent processing steps may then process the preprocessed first audio signals as if their origin were in the 0 degree direction. In this case, for example, symmetry properties or head shadows of audio signals with this origin can be used.
  • a speaker 202 In the preferred direction is a speaker 202, which is assumed in the following as the source of a useful signal in the preferred direction.
  • the carrier 201 At other angles to the carrier 201 further persons 203, 204, 205 and 206 are arranged.
  • a binaural Eight 210 210 is shown, which indicates a directional characteristic of a difference signal of the first audio signals of the two transducers of the two hearing aids of the binaural hearing aid system.
  • a directional directional characteristic 220 is indicated which results, for example, from a weighted summation of the first audio signals of the two transducers of the two hearing aids of the binaural hearing aid system.
  • the directional characteristic 220 has a maximum of sensitivity in the preferred direction 0 degrees.
  • Fig. 3 shows a schematic flow diagram of a method according to the invention in the signal processing device 3, 3 '.
  • the signal processing device 3 forms a sum signal of the first audio signals of the transducers 2, 2 '.
  • the sum signal shows a maximum of the sensitivity in the preferred direction, in which speaker 202 is also arranged.
  • the directional characteristic can, for example, the directional characteristic 220 in Fig. 2 same.
  • the first audio signals are added immediately. But it is also conceivable that the first audio signals are first corrected in their amplitude and phase, for example, to select a different preferred direction or to compensate for tolerances between the transducers 2, 2 '. It is possible that the correction takes place in the sense of an adaptive filter. This could be, for example, a Wiener filter.
  • the coefficients can be chosen so that the energy content of the sum signal is minimal, so that not originating from the preferred direction acoustic signals are already attenuated. This would also make it possible to use head shadow effects specifically to achieve a signal with the greatest possible proportion of the preferred direction.
  • each hearing aid can have a monaural directional microphone that is combined from two omnidirectional microphones.
  • step S20 the signal processing device 3, 3 'forms a difference signal of the first audio signals of the transducers 2, 2'.
  • a possible directional characteristic 210 of the difference signal is in the form of a binaural eight in Fig. 2 shown.
  • the difference signal indicates a minimum of the sensitivity in the preferred direction of the speaker 202
  • Directional characteristic 210 in directions other than the preferred direction of increased sensitivity, so that acoustic signals of the speakers 203, 204 205 or 206 relative to acoustic signals of the speaker 202 lead to stronger first acoustic signals.
  • the difference signal can also be formed from a plurality of first audio signals in order to realize directional characteristics of a higher order.
  • step S30 the signal processing device 3, 3 'forms a quotient of the sum signal and the difference signal.
  • the transducers 2, 2 ' provide first level 1 audio signals to the speaker 202 and the factors in the summation and the difference are equal to 1, respectively. the signals are normalized.
  • the discussed values should be scaled accordingly, which, however, does not alter the inventive idea and these embodiments are covered by the protection of the invention.
  • the quotient assumes a value significantly greater than 1, because because of the minimum of the directional characteristic 210 in the preferred direction, the difference signal is small and even approaches zero in the theoretical extreme case. At the same time, the sum signal is maximal, for normalized sensitivity this would be a value 2. The quotient increases correspondingly to large positive values.
  • the signal value of the difference signal goes to a value equal to that of the sum signal, since the two directional characteristics 201, 220 intersect in the direction of the speaker 203.
  • the quotient itself goes against the value 1.
  • the signal value of the difference signal goes to a maximum while the sum signal goes to a value less than 1 and greater than 0 in the direction of 0.
  • the quotient itself also goes to a value less than 1 and greater than 0 in the direction 0. Comparable applies to speaker 206. Typical values for the quotient are then between 0.5 and 0.25.
  • the signal processing device 3, 3 ' increases the directivity of the binaural directional microphone signal when the quotient increases or exceeds a predetermined value.
  • This value may be, for example, 0, 5 or 1 relative to a normalized audio signal.
  • the binaural directional microphone signal has a greater signal level, while for example for signal sources such as speakers 203, 204, 205 or 206 in other directions at an angle to the preferred direction, the signal has lower signal level.
  • An increase in the directional characteristic can be done in one embodiment by the binaural directional microphone signal is obtained by a weighted superimposition of the sum signal and an omnidirectional microphone signal, to increase the directional characteristic of the sum signal over the omnidirectional signal is weighted more.
  • the binaural directional microphone signal is obtained by a weighted superimposition of the sum signal and an omnidirectional microphone signal, to increase the directional characteristic of the sum signal over the omnidirectional signal is weighted more.
  • other combinations of binaural directional microphones of higher order with an omnidirectional microphone signal are conceivable.
  • the signal processing device 3, 3 ' lowers the directional characteristic of the binaural directional microphone signal in step S40 when the quotient decreases.
  • this is the case for speaker 204, for example.
  • the sensitivity of the binaural directional microphone for directions increases at an angle to the preferential direction while decreasing in the preferential direction.
  • the binaural directional microphone no longer has a directional characteristic, so it has an omnidirectional directional characteristic.
  • the signal level of the binaural directional microphone is equal to that for signal sources such as speakers 203, 204, 205 or 206 in other directions at an angle to the preferred direction.
  • the minimum of the first audio signals or the first preprocessed audio signals is determined instead of the sum in step S10.
  • step S30 the quotient of the determined minimum and the difference of the first audio signals or of the first preprocessed audio signals is then formed correspondingly. Otherwise, the alternative method corresponds to the method already described.
  • the signal processing device 3, 3 ' determines a value for the cross-correlation of the first audio signals instead of the quotient in step S10'. If the origin of an audio signal is in the plane of symmetry between the two hearing aid devices 110, 110 ', the first audio signals are ideally identical and have a high value for the cross-correlation. For values outside, the cross-correlation decreases accordingly. The same applies if the first audio signals originate from a large number of independent spatially distributed sources.
  • the signal processing device 3, 3' corresponding to S40 increases the directional characteristic of the binaural directional microphone signal as the value of the cross-correlation increases or becomes greater than zero and lowers the directional characteristic of the binaural directional microphone signal when the value for the cross-correlation decreases.
  • the preferred direction is not in the plane of symmetry between the hearing aid devices.
  • the preferred direction in a different direction outside the plane of symmetry of the two hearing aids 110, 110' are directed.
  • the minimum of the first preprocessed audio signal and the second preprocessed audio signal is included in the quotient as a counter.
  • the pre-processing of the first audio signals can be permanent or adaptive using a method that determines a spatial direction of a sound source and determines appropriate amplitude and phase corrections to map the spatial direction in the plane of symmetry between the hearing aids in the viewing direction of the wearer. Accordingly, in carrying out a method according to the invention, the speaker 202 in FIG Fig. 2 also be arranged in a direction other than the indicated preferred direction 0 degrees with respect to the carrier 201.
  • Fig. 4 schematically shows the function blocks for generating a quotient according to the inventive method.
  • the first acoustic signals of the transducers are summed in adder 301 and subtracted into adder 302 after the inverter 303 has inverted the first acoustic signal of the transducer 2.
  • the sum and difference signals are first converted into rectifiers 305, 306 in amounts and rectified and averaged in the low passes 307, 308 before the quotient is formed in the divider 309.
  • Fig. 4 can be inventively represented by analog modules, digital discrete or integrated units such as ASICS or FPGA or as software in a digital signal processor processor or a general processor.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Stereophonic System (AREA)
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EP14161630.0A 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural Active EP2840809B1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP18248116.8A EP3490273A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural
EP18183297.3A EP3410745A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102013207149.3A DE102013207149A1 (de) 2013-04-19 2013-04-19 Steuerung der Effektstärke eines binauralen direktionalen Mikrofons

Related Child Applications (3)

Application Number Title Priority Date Filing Date
EP18248116.8A Division EP3490273A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural
EP18183297.3A Division EP3410745A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural
EP18183297.3A Division-Into EP3410745A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural

Publications (3)

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EP2840809A2 true EP2840809A2 (fr) 2015-02-25
EP2840809A3 EP2840809A3 (fr) 2017-05-17
EP2840809B1 EP2840809B1 (fr) 2019-01-02

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EP18183297.3A Withdrawn EP3410745A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural
EP18248116.8A Withdrawn EP3490273A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural
EP14161630.0A Active EP2840809B1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural

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EP18183297.3A Withdrawn EP3410745A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural
EP18248116.8A Withdrawn EP3490273A1 (fr) 2013-04-19 2014-03-26 Commande de l'intensité d'effet d'un microphone directionnel binaural

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US (1) US9253581B2 (fr)
EP (3) EP3410745A1 (fr)
DE (1) DE102013207149A1 (fr)
DK (1) DK2840809T3 (fr)

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US20140314260A1 (en) 2014-10-23
EP3410745A1 (fr) 2018-12-05
DE102013207149A1 (de) 2014-11-06
US9253581B2 (en) 2016-02-02
EP3490273A1 (fr) 2019-05-29
DK2840809T3 (da) 2019-04-08
EP2840809B1 (fr) 2019-01-02
EP2840809A3 (fr) 2017-05-17

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