Information processing device, information processing method, and program

Abstract

There is provided an information processing apparatus including a prediction unit that predicts a degree of conducted hearing loss based on examination results of a first hearing examination and a second hearing examination that conduct sound using air and include examination contents different from each other.

Description

Technical Field

[0001] The present disclosure relates to an information processing device, an information processing method, and a program. Background Art

[0002] When considering the use of hearing aids, medical institutions, hearing aid shops, etc. first perform pure sound audiometry. Pure sound audiometry is a hearing test performed using a testing device called an audiometer, and specifically, an air conduction hearing test and a bone conduction hearing test are performed using an audiometer. For example, an air conduction hearing test and a bone conduction hearing test are performed using the method described in the following non-patent document 1. Then, the difference between the air conduction hearing level obtained by the air conduction hearing test and the bone conduction hearing level obtained by the bone conduction hearing test is calculated, and the degree of conductive hearing loss can be grasped. In addition, information about the degree of conductive hearing loss is used to determine whether to prioritize research on treatments other than hearing aids before starting to wear hearing aids. In addition, information about the degree of conductive hearing loss is also used to determine the gain of the hearing aid.

[0003] Reference List

[0004] Non-patent literature

[0005] Non-patent document 1: Hearing Test Method of Japanese Society of HearingMedicine 1.Pure Sound Hearing(Threshold)Level Measurement Method byAudiometer(2008) Summary of the invention

[0006] Technical issues

[0007] When performing a bone conduction hearing test, a bone conduction headset is worn on the subject's head. However, since the bone conduction headset needs to be accurately attached to a place where the test sound can be effectively transmitted, it is difficult for people other than professionals to attach the bone conduction headset. Therefore, for example, it is not easy for an individual subject to perform a bone conduction hearing test and obtain information on the degree of conductive hearing loss.

[0008] Therefore, the present disclosure proposes an information processing device, an information processing method, and a program that can easily predict the degree of conductive hearing loss using air-conducted sound.

[0009] Solution to the problem

[0010] According to the present disclosure, there is provided an information processing device including: a prediction unit that predicts the degree of conductive hearing loss based on a test result of a hearing test using air-conducted sound. In the information processing device, the hearing test is a first hearing test and a second hearing test including test contents different from each other.

[0011] In addition, according to the present disclosure, there is provided an information processing method, comprising: predicting the degree of conductive hearing loss based on the test results of a hearing test using air-conducted sound by an information processing device. In the information processing method, the hearing test is a first hearing test and a second hearing test including test contents different from each other.

[0012] In addition, according to the present disclosure, there is provided a program that causes a computer to execute the following function: a function of predicting the degree of conductive hearing loss based on the test results of a hearing test using air-conducted sound. In the program, the hearing test is a first hearing test and a second hearing test including test contents different from each other. BRIEF DESCRIPTION OF THE DRAWINGS

[0013] Figure 1 This is an illustration used to explain the difference in the paths between air-conducted sound and bone-conducted sound.

[0014] Figure 2 This is an illustration for explaining the corresponding range of the damaged part in pure sound audiometry.

[0015] Figure 3 This is a flowchart for explaining the process of determining the necessity of treatment before wearing a hearing aid.

[0016] Figure 4 This is an explanatory diagram for explaining an example of setting the hearing aid gain for each hearing loss.

[0017] Figure 5 This is an explanatory diagram for explaining an example of the pure sound audiometry method of the related art.

[0018] Figure 6 It is an explanatory diagram for explaining a hearing test according to an embodiment of the present disclosure.

[0019] Figure 7 It is an explanatory diagram for explaining an example of a hearing test in the related art.

[0020] Figure 8 It is an explanatory diagram for explaining an example of the observation result of the self-recording audiometer.

[0021] Fig. 9 This is an illustration for explaining the corresponding range of the self-recording audiometer with respect to the injury site.

[0022] Fig.10It is an explanatory diagram for explaining the outline of the first embodiment of the present disclosure.

[0023] Fig.11 It is an explanatory diagram for explaining learning data according to the first embodiment of the present disclosure.

[0024] Fig.12 is a block diagram of an information processing terminal according to a first embodiment of the present disclosure.

[0025] Fig.13 It is an explanatory diagram for explaining the conductive hearing loss prediction unit according to the first embodiment of the present disclosure.

[0026] Fig.14 is a flowchart for explaining the flow of the information processing method according to the first embodiment of the present disclosure (Part 1).

[0027] Fig.15 is a flowchart for explaining the flow of the information processing method according to the first embodiment of the present disclosure (Part 2).

[0028] Fig.16 1 is an explanatory diagram for explaining an example of a hearing test service according to the first embodiment of the present invention.

[0029] Fig.17 It is an explanatory diagram for explaining the outline of the second embodiment of the present disclosure.

[0030] Fig.18 is a block diagram of an information processing terminal according to a second embodiment of the present disclosure.

[0031] Fig.19 It is a flowchart for explaining the flow of the information processing method according to the second embodiment of the present disclosure.

[0032] Fig. 20 is a flowchart for explaining the flow of the information processing method according to the third embodiment of the present disclosure (Part 1).

[0033] Fig.21 : is a flowchart (part 1) for explaining the flow of an information processing method according to a modification example of the third embodiment of the present disclosure.

[0034] Fig. 22 It is a flowchart (Part 2) for explaining the flow of the information processing method according to the modification example of the third embodiment of the present disclosure.

[0035] Fig.23 is a flowchart (Part 2) for explaining the flow of the information processing method according to the third embodiment of the present disclosure.

[0036] Fig.24is a block diagram of an information processing terminal according to a fourth embodiment of the present invention.

[0037] Fig.25 : is a flowchart for explaining the flow of the information processing method according to the fourth embodiment of the present disclosure.

[0038] Fig.26 It is an explanatory diagram for explaining the fourth embodiment of the present disclosure.

[0039] Fig. 27 It is an explanatory diagram (Part 1) for explaining a display example according to a fourth embodiment of the present disclosure.

[0040] Fig.28 It is an explanatory diagram (Part 2) for explaining a display example according to the fourth embodiment of the present disclosure.

[0041] Fig.29 It is an explanatory diagram (Part 1) for explaining an application example according to the fourth embodiment of the present disclosure.

[0042] Fig.30 It is an explanatory diagram (Part 2) for explaining an application example according to the fourth embodiment of the present disclosure.

[0043] Fig.31 is a block diagram of an external device according to a fourth embodiment of the present disclosure.

[0044] Fig.32 is a diagram showing a schematic configuration of a hearing aid system according to an embodiment of the present disclosure.

[0045] Fig.33 is a functional block diagram of a hearing aid and a charger according to an embodiment of the present disclosure.

[0046] Fig.34 is a block diagram of an information processing terminal according to an embodiment of the present disclosure.

[0047] Fig.35 is a block diagram of a server according to an embodiment of the present disclosure.

[0048] Fig.36 is a diagram showing an example of data utilization;

[0049] Fig.37 is a diagram showing an example of data.

[0050] Fig.38 is a diagram illustrating an example of cooperation with another device.

[0051] Fig.39 is a diagram showing an example of using transition; DETAILED DESCRIPTION

[0052] The preferred embodiments of the present invention are described in detail below with reference to the accompanying drawings. Note that in this specification and the accompanying drawings, components having substantially the same functional configuration are represented by the same reference numerals and symbols, thereby omitting redundant explanations of the components. In addition, in this specification and the accompanying drawings, multiple components having substantially the same or similar functional configurations are sometimes distinguished by attaching different alphabets after the same reference numerals. However, when it is not particularly necessary to distinguish each of the multiple components having substantially the same or similar functional configurations, only the same reference numerals and symbols are attached.

[0053] Note that the explanation is given in the following order.

[0054] 1. Background leading to the creation of embodiments of the present disclosure

[0055] 2. First Implementation

[0056] 2.1 Overview

[0057] 2.2 Configuration

[0058] 2.3 Information Processing Methods

[0059] 2.4 Application Examples

[0060] 3. Second Implementation

[0061] 3.1 Overview

[0062] 3.2 Configuration

[0063] 3.3 Information Processing Methods

[0064] 4. Third Implementation

[0065] 5. Fourth embodiment

[0066] 5.1 Configuration

[0067] 5.2 Information Processing Methods

[0068] 5.3 Display Example

[0069] 5.4 Application Examples

[0070] 6. Summary

[0071] 7. Overview of hearing aid systems

[0072] 8. Examples of data utilization

[0073] 9. Examples of collaboration with other devices

[0074] 10. Examples of using transitions

[0075] 11. Supplement

[0076] <<1. Background leading to creation of embodiments of the present disclosure>>

[0077] First, before explaining the embodiments of the present disclosure, the background that led to the creation of the embodiments of the present disclosure by the present inventors is explained.

[0078] First, refer to Figures 1 to 9 Describe the hearing aid fitting study. Figure 1 This is an illustration for explaining the difference in the paths of air-conducted sound and bone-conducted sound. Figure 2 is an illustration for explaining the corresponding range of the damaged part in pure sound audiometry, and Figure 3 This is a flowchart for explaining the flow of determining the necessity of treatment before wearing a hearing aid. Figure 4 is an explanatory diagram for explaining setting examples of hearing aid gain for each type of hearing loss, Figure 5 is an explanatory diagram for explaining an example of pure sound audiometry of the prior art, and Figure 6 : is an explanatory diagram for explaining a hearing test according to an embodiment of the present disclosure. Figure 7 is an explanatory diagram for explaining an example of a hearing test in the related art, Figure 8 is an explanatory diagram for explaining an example of the observation result of the self-recording audiometer, and Fig. 9 This is an explanatory diagram for explaining the corresponding range of the self-recording audiometry method for the damaged part.

[0079] When considering wearing a hearing aid, a medical institution, a hearing aid store, etc. performs pure sound audiometry on a user (subject). Pure sound audiometry includes two types of threshold tests, air conduction audiometry and bone conduction audiometry. Usually, these two tests are performed.

[0080] exist Figure 1In the figure, the first path 121 represents the path of air-conducted sound. Air-conducted sound is sound that reaches the inner ear as vibration after passing through the outer ear and the middle ear. Then, the vibration is converted into an electrical signal in the inner ear. Further, the electrical signal travels toward the auditory cortex through the posterior labyrinth system. Then, the air conduction hearing test is a test in which the test sound is transmitted to the inner ear using the first path 121. In the air conduction hearing test, because the air-conducted sound reaches the inner ear via the outer ear and the middle ear, the state in which the degree of obstruction of the outer ear, the middle ear, the inner ear, and the posterior intricate disorder is added can be measured. The hearing loss caused by the obstruction of the outer ear and the middle ear is called conductive hearing loss, the hearing loss caused by the obstruction of the inner ear is called inner ear hearing loss, the hearing loss caused by the obstruction of the posterior labyrinth system is called retrocochlear hearing loss, and the inner ear hearing loss and retrocochlear hearing loss are collectively referred to as sensorineural hearing loss. In addition, the hearing loss in which conductive hearing loss and sensorineural hearing loss occur simultaneously is called mixed hearing loss. That is, the air conduction hearing test can also be considered as a test that can measure the degree of conductive hearing loss and the degree of sensorineural hearing loss in a cumulative state. The hearing level measured in the air conduction hearing test is called the air conduction hearing level. The air conduction hearing level can be expressed by the following formula (1).

[0081] Air conduction hearing level = degree of conductive hearing loss + degree of sensorineural hearing loss…(1)

[0082] On the other hand, Figure 1 , the second path 122 indicates the path of the bone conduction sound. Bone conduction sound is sound that reaches the inner ear as vibration after passing through the skull. After reaching the inner ear, the bone conduction sound is the same as the case of the above-mentioned air conduction sound. The bone conduction hearing test is a test in which the test sound is transmitted to the inner ear using the second path 122. In the bone conduction hearing test, since the bone conduction sound reaches the inner ear without passing through the outer ear and the middle ear, the cumulative state of the degree of obstruction of the inner ear and the posterior labyrinth system can be measured without being affected by obstructions of the outer ear and the middle ear. That is, the bone conduction hearing test can also be considered as a test that can measure the degree of sensorineural hearing loss without being affected by conductive hearing loss. The hearing level measured in the bone conduction hearing test is called the bone conduction hearing level. The bone conduction hearing level can be expressed by the following formula (2).

[0083] Bone conduction hearing level = degree of sensorineural hearing loss…(2)

[0084] In addition, the difference between the air conduction hearing level and the bone conduction hearing level is called an air-bone gap. The air-bone gap indicates the degree of conductive hearing loss and can be expressed by the following formula (3).

[0085] Air-bone gap = air conduction hearing level - bone conduction hearing level = degree of conductive hearing loss…(3)

[0086] Figure 2 The corresponding ranges of air conduction hearing test and bone conduction hearing test for pure sound audiometry of the damaged part are shown. Air conduction hearing test can be used to obtain indicators of obstacles causing conductive hearing loss, inner ear hearing loss and retro-cochlear hearing loss. Bone conduction hearing test can be used to obtain indicators of obstacles causing inner ear hearing loss and retro-cochlear hearing loss. Since the same test sound is used for both air conduction hearing test and bone conduction hearing test, the response to the measurement at the damaged part is the same. For this reason, the air-bone gap obtained by subtracting the bone conduction hearing level from the air conduction hearing level represents the degree of conductive hearing loss. It should be noted that this is as explained using formula (1) to formula (3).

[0087] For example, when an obstacle equivalent to 40dBHL exists only in the inner ear (sensorineural hearing loss is 40dBHL), the result of the air conduction hearing test and the result of the bone conduction hearing test are both about 40dBHL. For example, when an obstacle equivalent to 30dBHL exists only in the posterior labyrinth system (sensorineural hearing loss is 30dBHL), the result of the air conduction hearing test and the result of the bone conduction hearing test are both about 30dBHL. On the contrary, for example, when an obstacle equivalent to 35dBHL exists only in the middle ear (conductive hearing loss is 35dBHL), the result of the air conduction hearing test is about 35dBHL, but the result of the bone conduction hearing test is about 0dBHL. For example, when an obstacle equivalent to 30dBHL exists in the middle ear and an obstacle equivalent to 35dBHL exists in the inner ear, a mixed hearing loss of 65dBHL is caused (30dBHL for conductive hearing loss and 35dBHL for sensorineural hearing loss). In this case, the result of the air conduction hearing test is about 65 dBHL and the result of the bone conduction hearing test is about 35 dBHL.

[0088] As mentioned above, air conduction hearing test and bone conduction hearing test are tests that can distinguish between conductive hearing loss and sensorineural hearing loss and can measure the degree of conductive hearing loss and sensorineural hearing loss.

[0089] Therefore, when considering the use of hearing aids, information about the degree of conductive hearing loss is important in two points. First, information about the degree of conductive hearing loss is used to determine whether research on treatment other than hearing aids should be prioritized before starting to wear hearing aids. As a second point, when determining the gain of a hearing aid, information about the degree of conductive hearing loss and information about the degree of sensorineural hearing loss are used.

[0090] First, the first point is explained. When conductive hearing loss is suspected, research on treatments other than hearing aids should be prioritized before wearing hearing aids. If a disorder that causes conductive hearing loss occurs, it is likely that the disorder can be improved by early treatment. On the contrary, when time passes, there is a possibility that the disorder cannot be improved by treatment. Therefore, when conductive hearing loss is suspected, it is expected to first visit a medical institution, etc., and determine the necessity of treatment that should be prioritized. When there is a treatment that should be prioritized, perform that treatment first. As described above, when considering wearing a hearing aid, it is important to grasp the degree of conductive hearing loss. Note that in the case where there is no treatment that should be prioritized even if there is conductive hearing loss, for example, in the case where conductive hearing loss still exists even if the conductive hearing loss has been treated, consider wearing a hearing aid.

[0091] Reference Figure 3 The flowchart shown in the figure illustrates an example of the determination process of the necessity of treatment before wearing a hearing aid. First, an air conduction hearing test and a bone conduction hearing test are performed on the subject (step S101). Then, it is determined whether the subject has a problem with hearing (step S102). In step S102, for example, it is determined whether the hearing aid is worn at an appropriate level. Specifically, in Japan, a hearing level of 25dBHL or more and less than 40dBHL is defined as mild hearing loss, and a hearing level of 40dBHL or more and less than 70dBHL is defined as moderate hearing loss. In addition, in Japan, hearing aids are usually worn when the hearing level is 40dBHL or higher. However, the determination criteria may vary depending on the situation. Then, in the case where it is determined that the subject has no problem with hearing (step S102: No), the process enters step S103. Next, it is determined that the subject is followed up regularly as needed (step S103), and the process ends.

[0092] On the other hand, in the case where it is determined that there is a problem with the subject's hearing (step S102: Yes), the process proceeds to step S104. Subsequently, it is determined whether there is a conductive hearing loss (step S104). Whether there is a conductive hearing loss can be determined by the air-bone gap. From a treatment point of view, for example, when the air-bone gap is 25dBHL or more, the standard for determining the presence of a conductive hearing loss is widely used. Then, when it is determined that there is no conductive hearing loss (step S104: No), the process proceeds to step S105. Next, it is recommended to the subject to consider a hearing aid (step S105), and the process ends.

[0093] On the other hand, when it is determined that the subject has a conductive hearing loss (step S104: Yes), the process proceeds to step S106. Next, it is determined whether treatment other than hearing aids is required (step S106). This determination is usually performed in a medical institution or the like. In the case where it is determined that treatment is not required (step S106: No), the process proceeds to step S105. On the other hand, in the case where it is determined that treatment is required (step S106: Yes), the process proceeds to step S107. Then, it is determined that the subject is treated (step S107), and the process ends.

[0094] from Figure 3 It can be seen that before wearing a hearing aid, the future strategy of whether to perform treatment first or consider wearing a hearing aid varies greatly depending on whether there is a treatment that should be performed in addition to the hearing aid. Therefore, in order to prevent the subject from missing the opportunity for treatment, in other words, in order to prevent the subject from missing the opportunity to improve hearing loss, it is important to grasp the degree of conductive hearing loss.

[0095] Next, the second point will be explained. Figure 4 1 shows an example of setting the hearing aid gain for each type of hearing loss. Figure 4 The left side of FIG. 1 shows an example of a gain setting of a hearing aid in the case of conductive hearing loss. Figure 4 An example of a gain setting for a hearing aid in the case of mixed hearing loss is shown in the center of Figure 4 The right side of shows an example of the gain setting of a hearing aid in the case of sensorineural hearing loss. Mixed hearing loss is hearing loss in which both conductive hearing loss and sensorineural hearing loss occur simultaneously.

[0096] In the case of conductive hearing loss, since there is no obstruction in the inner ear, it is considered desirable to amplify the sound collected by the microphone of the hearing aid with a constant gain. Amplifying the sound with a constant gain regardless of the input level in this way is generally referred to as linear amplification. Figure 4 In the example shown on the left side of , in the first part 751, the sound is amplified with a constant gain regardless of the input level. Specifically, the inclination of the straight line in the first part 751 is 45 degrees. Note that the inclination of the straight line is not limited to this. Figure 4 In the example shown on the left side of , the second part 752 is set to output limitation and is generally set to prevent further deterioration of hearing loss due to loud sounds.

[0097] Since most sensorineural hearing losses have inner ear hearing losses, the supplementation phenomenon often occurs. When the supplementation phenomenon occurs, the sound is expected to be amplified by increasing the gain for weak input levels and decreasing the gain for strong input levels. Amplifying the sound with different gains depending on the input level is often called nonlinear amplification. Figure 4In the example shown on the right, the sound is amplified with different gains according to the input level in the sixth part 756, the seventh part 757, and the eighth part 758. Specifically, the inclination of the straight line in the seventh part 757 is closer to the horizontal than 45 degrees. Figure 4 The ninth portion 759 in the example shown on the right side is set as the output limit.

[0098] Here, the supplementary phenomenon will be described. The supplementary phenomenon is also called the recruitment phenomenon, and is an abnormality in loudness (the sense of sound amplitude) caused by a disorder of outer hair cells present in the cochlea of ​​the inner ear. When the supplementary phenomenon exists, since the subject is sensitive even to small volume changes, symptoms sometimes occur in which, for example, the subject feels a very loud sound even though the subject does not easily hear a small sound.

[0099] In the case of mixed hearing loss, for example, the sound is set to be amplified with a gain between that of conductive hearing loss and sensorineural hearing loss. Figure 4 In the example shown in the center of FIG. 75 , the inclination in the fourth portion 754 is an inclination between the inclination in the first portion 751 and the inclination in the seventh portion 757. Note that the inclination in the fourth portion 754 is determined by, for example, the degree of conductive hearing loss and the degree of sensorineural hearing loss. Figure 4 The fifth portion 755 in the example shown at the center is set to output limit.

[0100] from Figure 4 As can be seen in Figure 1, the gain setting required for a hearing aid differs greatly between conductive hearing loss and sensorineural hearing loss. Therefore, in order to make adjustments suitable for the hearing of a subject who is a user of a hearing aid, it is important to grasp the degree of conductive hearing loss and the degree of sensorineural hearing loss. Therefore, when considering wearing a hearing aid, a hearing test is performed on the subject.

[0101] Figure 5 An example of pure sound audiometry of the related art is shown. An apparatus that performs pure sound audiometry is generally called an audiometer. The audiometer 913 includes an air conduction headset 911, a bone conduction headset 912, and a response button 914. Pure sound audiometry is performed using the audiometer 913 in medical institutions, hearing aid stores, and the like.

[0102] When performing an air conduction hearing test included in pure sound audiometry, an air conduction headset 911 is worn on the head of the subject 901 so that the subject 901 hears the test sound. Then, the test sound is transmitted to the subject 901 via the Figure 1The first path 121 shown in reaches the inner ear. When hearing the test sound, the subject 901 answers by pressing the response button 914. As the air conduction headphone 911, there are an overhead type and an inner ear type. For music appreciation, the overhead air conduction headphone has a form similar to a general overhead headphone. The inner ear type air conduction headphone has a form similar to a general inner earphone for music appreciation.

[0103] When performing a bone conduction hearing test included in pure sound audiometry, the bone conduction headset 912 is worn on the head of the subject 901 so that the subject 901 hears the test sound. Figure 1 The second path 122 shown in FIG. 1 reaches the inner ear. At this time, in principle, the ear opposite to the inspection ear (the ear on the side being inspected) is masked by an air conduction headset not shown for masking, etc. Since the bone conduction headset 912 vibrates the skull, the test sound emitted from the skull is heard with both ears at the same time. Therefore, unless masking is performed, the test for each ear cannot be performed. Therefore, masking is performed to prevent the subject from hearing the test sound with the opposite ear and responding. When hearing the test sound, the subject 901 presses the response button 914 to answer. The attachment position of the bone conduction headset 912 is usually the mastoid (behind the auricle) or the front middle part. The bone conduction headset 912 needs to be accurately worn on a place where the test sound can be effectively transmitted (such as the mastoid and the front middle part). Therefore, it is necessary to pay attention when wearing the bone conduction headset 912. In addition, the bone conduction headset 912 must not touch the outer ear. It is also inappropriate for the bone conduction headset 912 to hold the hair. In addition, since the air introduction receiver (not shown) for masking is also worn at the same time, it is also necessary to prevent the bone conduction headset 912 and the air conduction headset for masking from deviating from each other. Therefore, preferably, the bone conduction headset 912 is worn on the head of the subject 901 by the professional 903.

[0104] Figure 6 An example of a hearing test in which the subject 102 purchases a hearing aid via the Internet or the like without going through a medical institution, a hearing aid store, or the like is shown. Hearing aids are mainly sold by a hearing aid professional 903 working at a medical institution, a hearing aid store, or the like. On the other hand, in recent years, a form of selling hearing aids other than through the hearing aid professional 903 has begun to spread. The reason for this is that, for example, the price of hearing aids causes people who need hearing aids or areas where the services of the hearing aid professional 903 can be received to be unevenly distributed.

[0105] In this case, for example, Figure 6As shown, the subject 102 performs an air conduction hearing test using the information processing terminal 117 via the Internet 119. Specifically, in order to perform the air conduction hearing test, for example, dedicated application software may be downloaded and installed in the information processing terminal 117. The hearing aid 116 itself may have a function of the air conduction hearing test.

[0106] In this case, since the hearing aid 116 does not have the bone conduction headphone 912, an air conduction hearing test can be performed, but a bone conduction hearing test cannot be performed. Therefore, in the form of selling the hearing aid 116 without the hearing aid professional 903 (hearing aids sold in this form are called OTC (Over-The-Counter) hearing aids, etc.), there is a problem that although the air conduction hearing level can be measured, the bone conduction hearing level cannot be measured. In other words, in the form of selling the hearing aid 116 without the hearing aid professional 903, there is a problem that the degree of conductive hearing loss cannot be measured.

[0107] According to this situation, in the form of selling the hearing aid 116 without going through the hearing aid professional 903, it is assumed that the air conduction hearing level, which initially indicates both the degree of conductive hearing loss and the degree of sensorineural hearing loss, indicates the degree of sensorineural hearing loss, and the hearing aid gain is generally as Figure 4 .

[0108] Figure 7 An example of a hearing test in a group medical test at a school or company is shown. The group medical test is mainly aimed at effectively finding people with hearing impairment from many people with normal hearing ability, that is, screening. For this reason, in the group medical test, a bone conduction hearing test is usually not performed. In the bone conduction hearing test, a lot of time is required because the hearing aid works in the correct wearing position and the correct wearing state and the test is performed. In addition, in the bone conduction hearing test, it is necessary to perform appropriate masking, etc. Therefore, compared with the air conduction hearing test, the tester who performs the test needs to have a lot of professional knowledge and skills. Therefore, it is difficult to ensure a suitable tester. Therefore, in the group medical test whose main purpose is to effectively find people with hearing impairment from many people with normal hearing ability, the bone conduction hearing test is usually rarely performed.

[0109] However, the inventors of the present invention desire to provide a method that can easily grasp the degree of conductive hearing loss using air-conducted sound even in a form in which the hearing aid 116 is not sold through the hearing aid professional 903 or a group medical examination is conducted, in order to prevent the subject 901 from losing the opportunity to receive immediate treatment. In addition, in order to appropriately set the hearing aid gain, the inventors of the present invention desire to establish a method that can easily grasp the degree of conductive hearing loss using air-conducted sound even in a form in which the hearing aid 116 is not sold through the hearing aid professional 903. Then, while repeating careful studies to obtain such a method, the inventors have obtained ideal results from the following to create an embodiment of the present disclosure.

[0110] There is a hearing test that can predict the presence or absence of conductive hearing loss using only air-conducted sound. The self-recording audiometer designed by Bekesy in 1947 (also called the Bekesy-type audiometer) can provide materials for determining the presence or absence of conductive hearing loss only in the case of air-conducting headphones without using bone-conducting headphones 912. The self-recording audiometer is characterized in that two types of intermittent sounds and continuous sounds are used as test sound sources. In the test of the self-recording audiometer, the subject 901 continuously presses a button while hearing the test sound, and continuously releases the button while not hearing the test sound. In addition, the self-recording audiometer gradually reduces the intensity of the test sound during the period when the subject 901 presses the button, and gradually increases the intensity of the test sound during the period when the subject 901 releases the button. As a result, when the intensity of the test sound during the test performed by the self-recording audiometer is recorded, a sawtooth wave pattern is observed.

[0111] Figure 8 An example of the observation result of the self-recording audiometer is shown. When the intermittent sound is used in the self-recording audiometer, the intensity of the recorded test sound transitions across the air conduction hearing threshold of the subject 901. That is, in the self-recording audiometer, the threshold (the median of the peak and valley of the sawtooth wave) in the case where the intermittent sound is used as the test sound is substantially equal to the result of the air conduction hearing test of the audiometer of the prior art.

[0112] Then, the observation results of the automatic recording audiometer are classified as follows, which can predict the type of hearing loss of the subject 901. For example, Figure 8 As shown in the upper right side of , when the amplitude (difference between peak and valley) of the sawtooth wave observed when using continuous sound in the self-recording audiometer is reduced compared with the result obtained when using intermittent sound, the observation result is classified as a sawtooth wave is classified as Jerger classification type II. In Jerger classification type II, the supplementary phenomenon is positive, and sensorineural hearing loss due to inner ear disorder is suspected.

[0113] On the other hand, when continuous sound is used, e.g. Figure 8 As shown on the lower left side of , a phenomenon is sometimes observed in which the threshold (the median of the peak and valley of the sawtooth wave) gradually increases over time. In this case, the observation result is classified as Jerger classification type III. Jerger classification type III is positive for temporary threshold changes, and sensorineural hearing loss due to posterior intricate disorders is suspected.

[0114] For example, as in Figure 8 As shown in the lower center of FIG, when the threshold (the median of the peak and trough of the sawtooth wave) observed when using continuous sound in a self-recording audiometer is lower than the result obtained when using intermittent sound, the observation is classified as Jerger classification type IV. In Jerger classification type IV, the sensorineural hearing loss is due to a disorder of the posterior labyrinthine system.

[0115] In addition, for example, as in Figure 8 As shown in the lower right part of , in the case where the threshold (the median of the peak and valley of the sawtooth wave) observed when continuous sound is used for the self-recording audiometer is higher than the result when intermittent sound is used, the observation result is classified as Jerger classification type V. In Jerger classification type V, psychometric hearing loss is suspected.

[0116] In addition, for example, Figure 8 As shown in the upper left side of , when the amplitude of the sawtooth wave does not decrease, the transient threshold rise does not occur, and the results of intermittent sound and continuous sound overlap each other, the observation result is classified as Jerger classification type I. Jerger classification type I is estimated to be normal. In addition, although it is not Figure 8 , when the amplitude reduction of the sawtooth wave does not occur, the results of the intermittent sound and the continuous sound overlap each other, and a threshold rise occurs, suspecting conductive hearing loss.

[0117] That is, in a self-recording audiometer using continuous sound and intermittent sound, inner ear hearing loss, high labyrinth system hearing loss, sensorineural hearing loss, and conductive hearing loss can be estimated by performing Jerger classification on the obtained results. Specifically, inner ear hearing loss (sensoreneural hearing loss) is estimated in the case of Jerger classification type II, post-cochlear hearing loss (sensoreneural hearing loss) is estimated in the case of Jerger classification type III and Jerger classification type IV, and conductive hearing loss is estimated in the case of Jerger classification type I in which a threshold increase occurs.

[0118] Next, the corresponding range of the self-recording audiometry method regarding the damaged part will be described. Fig. 9 The corresponding ranges for self-recording audiometry about the damaged area are shown. Fig. 9 As shown, the results of the self-recording audiometry method by intermittent sounds can be an indicator of disorders that cause conductive hearing loss, inner ear hearing loss, and retrocochlear hearing loss. However, conductive hearing loss (corresponding to range 333) and retrocochlear hearing loss (corresponding to range 335) cannot be distinguished only by intermittent sounds. In addition, when there is a reduction in the amplitude of a sawtooth wave, the inner ear hearing loss (corresponding to range 334) can be distinguished because the replenishment phenomenon is positive, but when there is no reduction in the amplitude of a sawtooth wave, the replenishment phenomenon is not necessarily negative.

[0119] The results of self-recording audiometry by continuous sound can also be an indicator of disorders causing conductive hearing loss, inner ear hearing loss and retrocochlear hearing loss. However, conductive hearing loss (corresponding to range 336) and retrocochlear hearing loss (corresponding to range 338) cannot be distinguished only by continuous sound. When there is a reduction in the amplitude of the sawtooth wave, the complementary phenomenon is positive and the inner ear hearing loss (corresponding to range 337) can be distinguished, but when there is no reduction in the amplitude of the sawtooth wave, the complementary phenomenon is not necessarily negative. The reduction in the amplitude of the sawtooth wave is not always the same in the case of intermittent sound (corresponding to range 334) and in the case of continuous sound (corresponding to range 337).

[0120] However, when the thresholds in intermittent sounds (corresponding to range 335) and continuous sounds (corresponding to range 338) are different, ie, when the transient threshold rise is positive, retro-cochlear hearing loss can be distinguished by comparing the thresholds.

[0121] As explained above, testing by a self-recording audiometer (self-recording audiometry) is considered to be a test suitable for classifying sensorineural hearing loss into inner ear hearing loss and retrocochlear hearing loss when the sensorineural hearing loss is known. However, in the test of the self-recording audiometer, since different test sounds (i.e., intermittent sounds and continuous sounds) are used, a certain degree of conductive hearing loss cannot be obtained by simple subtraction as in pure sound audiometry.

[0122] As can be seen from the above description, the self-recording audiometry is a test method that performs a test using two types of test sounds (i.e., intermittent sound and continuous sound) and combines the two types of test sounds to specify the presence or absence and location of a hearing impairment. In addition, since the self-recording audiometry can be performed using only air conduction headphones, the self-recording audiometry can be performed by the hearing aid 116. That is, the hearing aid 116 can detect conductive hearing loss.

[0123] Therefore, the inventors created an embodiment of the present disclosure by focusing on the following points: performing a test by giving two types of test sounds (i.e., intermittent sound and continuous sound) through air conduction air conduction headphones, and the air conduction air conduction headphones are a measurement method through self-recording hearing measurement.

[0124] However, the Jerger classification performed on the results obtained in the self-recording audiometer using continuous sound and intermittent sound also indicates where the disorder exists and does not refer to the degree of the disorder. In particular, in mixed hearing loss, it is difficult to interpret the Jerger classification. That is, the importance of self-recording audiometry is a minor diagnosis of sensorineural hearing loss (i.e., whether the sensorineural hearing loss is inner ear hearing loss or post-cochlear hearing loss), and does not grasp a certain degree of conductive hearing loss. Therefore, only by applying the self-recording audiometry, a method capable of easily grasping a certain degree of conductive hearing loss using air-conducted sound cannot be established.

[0125] Therefore, in view of this situation, the inventors have created an embodiment of the present disclosure described below. According to an embodiment of the present disclosure, the degree of conductive hearing loss can be predicted using air conduction headphones (i.e., air conduction sound). Therefore, according to an embodiment of the present disclosure, the subject 901 can be recommended to consult a medical institution, etc., and the subject can be prevented from missing the opportunity for early treatment of the disorder causing the hearing loss. In addition, according to an embodiment of the present invention, the gain of the hearing aid 116 of the subject 901 can be appropriately set according to the hearing of the subject 901. The details of this embodiment of the present disclosure are explained sequentially below.

[0126] <<2. First embodiment>>

[0127] <2.1 Overview>

[0128] First, refer to Fig.10 and Fig.11 An overview of the first embodiment of the present disclosure is explained. Fig.10 1 is an explanatory diagram for explaining the outline of the present embodiment, and specifically shows corresponding ranges of damaged parts in the first and second sets of self-recording audiometer tests in the present embodiment. Fig.11 It is an explanatory diagram for explaining learning data according to the present embodiment.

[0129] In the present embodiment, two sets of hearing tests are performed as in the self-recording audiometry method using two types of test sounds, ie, intermittent sound and continuous sound.

[0130] like Fig.10As shown, the first group of hearing tests (first hearing tests) according to the present embodiment include hearing tests having a corresponding range 541 and capable of measuring the threshold of air conduction hearing ability. For example, the first group of hearing tests according to the present embodiment may include an air conduction hearing test of pure sound audiometry and a self-recording audiometry using intermittent sound. Instead of pure sound, a warning tone or narrowband noise (specifically, continuous noise at a predetermined frequency) may be used. In addition, the first group of hearing tests according to the present embodiment may be a combination of multiple hearing tests.

[0131] like Fig.10 As shown, the hearing test of the second group according to the present embodiment (the second hearing test) may have a corresponding range 542, a corresponding range 543, and a corresponding range 544, or may have a corresponding range 545 and a corresponding range 546. In addition, the hearing test of the second group according to the present embodiment may have a corresponding range 545 alone or a corresponding range 546 alone.

[0132] The second group of hearing tests according to the present embodiment includes hearing tests for the inner ear and / or the posterior labyrinth system. For example, when it is assumed that the self-recording audiometry by intermittent sound is used for the hearing test of the first group, the hearing test of the second group may be the self-recording audiometry by continuous sound. In the present embodiment, by comparing the results of the self-recording audiometry by intermittent sound with the results of the self-recording audiometry by continuous sound, it is possible to distinguish Fig.10 In addition, as described above, the inner ear hearing loss in the corresponding range 543 can be distinguished by comparing the results of the self-recording audiometry by intermittent sound with the results of the self-recording audiometry by continuous sound, by observing the presence or absence of the amplitude reduction of the sawtooth wave. As a result, according to the present embodiment, it is possible to distinguish whether there is a conductive hearing loss in the corresponding range 542.

[0133] Examples of hearing tests of the inner ear that may be included in the second group of hearing tests according to the present embodiment include hearing tests that indicate positive when there is hearing loss in the inner ear. Specific examples of hearing tests include SISI (Short Incremental Sensitivity Index) test, ABLB (Alternating Binaural Loudness Balance) test, and DL (Differential Leaman) test.

[0134] For example, in the S1SI test, when the subject 901 notices that the sound is loud, a test sound is output at a constant interval, and the intensity is increased by a constant level from time to time to make the subject 901 respond. Then, in the S1SI test, the number of correct answers of the subject 901 for the intensity of the sound is scored, and the inner ear hearing loss is estimated based on the score.

[0135] For example, in the ABLB test, pure sounds with the frequency to be tested are heard in the left and right ears, the levels at which sounds of the same size can be heard in the left and right ears are calculated, a line is connected through the left and right results, and the inner ear hearing loss is estimated based on the gradient of the line.

[0136] An example of an auditory test of the posterior labyrinth system that may be included in the second group of auditory tests according to the present embodiment includes a TD (Tone Decay) test. For example, the TD test is used to measure auditory fatigue. A continuous sound of an audible threshold of a fixed frequency is output to the subject 901, and if the measured sound cannot be heard within a prescribed time, the level of the sound is immediately increased by a prescribed amount and output again. This operation is repeated, and the post-cochlear hearing loss is estimated based on the level of the sound that is successfully heard within a predetermined time or longer.

[0137] In addition, examples of other hearing tests include tests for estimating the tendency of retrocochlear hearing loss by comparison with the average pure sound hearing level. Specifically, for example, it is known that the results of a speech recognition threshold test are substantially consistent with the results of pure sound audiometry, but in the case of retrocochlear hearing loss, the results of the speech recognition threshold test are more significantly reduced. Therefore, the second group of hearing tests may include a speech recognition threshold test.

[0138] Furthermore, the maximum speech intelligibility, which is the highest score of the speech discrimination ability test, is related to the average pure sound hearing level in the case of sensorineural hearing loss. The maximum speech intelligibility tends to decrease as the average pure sound hearing level decreases. In the case of conductive hearing loss, it is known that the maximum speech intelligibility tends to approach a score of 100% even if the average pure sound hearing level decreases. Therefore, the second set of hearing tests may include a maximum speech intelligibility test.

[0139] The distorted speech audiometry test is used for the purpose of detecting retrocochlear hearing loss because it is known that when retrocochlear hearing loss is present, the score of the speech audiometry test is lower when distortion is present than when distortion is not present. Therefore, the distorted speech audiometry test may also be included in the second set of hearing tests.

[0140] In addition, examples of the complex rear auditory test that can be included in the second group of auditory tests according to the present embodiment include a binaural separation function test and a direction sensing test. For example, the binaural separation function test is a test that presents different auditory stimuli to the left and right ears at the same time.

[0141] Note that in the above description, several specific names of tests that can be included in the auditory test of the first group and the auditory test of the second group are exemplified. However, in the present embodiment, the tests that can be included in the auditory test of the first group and the auditory test of the second group are not limited to the specific auditory tests described above. For example, the tests that can be included in the auditory test of the first group and the auditory test of the second group can be modifications of the specific auditory tests described above.

[0142] Then, in the present embodiment, the degree of conductive hearing loss is predicted by combining the results of the first group of hearing tests and the second group of hearing tests including test contents different from each other. In the present embodiment, the degree of conductive hearing loss is predicted by a statistical method using these results or by applying a learning model to these results. Therefore, in the present embodiment, the degree of conductive hearing loss can be easily grasped using air-conducted sound.

[0143] Therefore, in this embodiment, in order to predict the degree of conductive hearing loss or generate a learning model using a statistical method, learning data including known test results are prepared.

[0144] Fig.11 An example of learning data in this embodiment is shown. Fig.11 In the example, the hearing test information 781 of the first group of N sets including the test results of the hearing test of the first group, the hearing test information 782 of the second group including the test results of the hearing test of the second group, and the degree information 784 of the conductive hearing loss of the same subject 901 in the same period are prepared as one set. Note that Fig.11 The first group of hearing test information 781 shown in FIG. includes only one test result. However, in the present embodiment, the test result is not limited to one test result, and may be a plurality of test results. In addition, the learning data in the present embodiment may include additional information 783. Fig.11 Only one piece of additional information is shown in FIG. 1 , but the additional information may be multiple pieces of additional information.

[0145] The first group of hearing test information 781 may be a test result of a hearing threshold test. More specifically, for example, the first group of hearing test information 781 may be an air conduction hearing level. In addition, in this embodiment, the numerical value of the air conduction hearing level may be directly used, or the numerical value of the air conduction hearing level may be standardized to 0.0 to 1.0.

[0146] The hearing test information 782 of the second group may be a test result indicating a positive in the case of sensorineural hearing loss. More specifically, the hearing test information 782 of the second group may be, for example, a test result of a self-recording audiometry method using continuous sound. Note that in the present embodiment, when the result of the self-recording audiometry method using continuous sound is used as the hearing test information 782 of the second group, it is desirable to perform a comparison with the result of the self-recording audiometry method using intermittent sound. For this reason, it is desirable that the hearing test information 781 of the first group includes the result of the self-recording audiometry method using intermittent sound.

[0147] More specifically, as described above, for the determination of hearing impairment of the inner ear, the reduction of the amplitude of the sawtooth wave can be used. When the amplitude of the sawtooth wave is 3 dB or less, the hearing impairment of the inner ear is strongly suspected, and when the amplitude is 2 dB or less, it is determined that there is an inner ear disorder. Therefore, in the present embodiment, for example, the case where the amplitude is 2.5 dB or less can be defined as positive (+), the case where the amplitude is greater than 2.5 dB can be defined as negative (-), and in addition, positive can be defined as 1.0, and negative can be defined as 0.0. Alternatively, the amplitude can be converted into a fraction that represents a value between positive and negative as a continuous value.

[0148] As explained above, the transient threshold rise of continuous sound can be used to determine the hearing disorder of the posterior labyrinth system. Thus, in the present embodiment, for example, when the transient threshold rise of continuous sound is 10 dB or more relative to the threshold of intermittent sound, it can be determined as positive (+), and when the transient threshold rise is less than 10 dB, it can be determined as negative (-). In addition, positive can be defined as 1.0, and negative can be defined as 0.0. Alternatively, the amplitude can be converted into a fraction that represents a value between positive and negative as a continuous value.

[0149] In the present embodiment, when the second set of hearing tests is for both inner ear hearing loss and retrocochlear hearing loss, the hearing test indicating a positive in the case of inner ear hearing loss and the hearing test indicating a positive in the case of retrocochlear hearing loss can be combined to form the hearing test of the second set. For example, the second set of hearing tests according to the present embodiment may include a SISI test used as a hearing test indicating a positive in the case of inner ear hearing loss and a TD test used as a hearing test indicating a positive in the case of cochlear hearing loss.

[0150] Specifically, in the present embodiment, according to Jerger's determination standard, for example, the case where the score of the SISI test is 60% or more can be defined as positive (+), the case where the score is 20% to 55% can be defined as pseudo-positive (+'), and the case where the score is 15% or less can be defined as negative (-). In addition, a positive value can be defined as 1.0, and a negative value can be defined as 0.0, or the score can be converted into a score that represents a value between a positive value and a negative value as a continuous value.

[0151] In the present embodiment, in the TD test, for example, the case where the rise width of the minimum level that can be heard for more than 1 minute is 10 dB or more can be defined as positive (+), and the case where the rise width is less than 10 dB can be defined as negative (-). In addition, a positive value can be defined as 1.0, and a negative value can be defined as 0.0, or the score can be converted into a score that represents a value between a positive value and a negative value as a continuous value.

[0152] In addition, in the present embodiment, the auditory test information 781 of the first group and the auditory test information 782 of the second group may include information obtained by biosensing of the object 901. For example, examples of biosensing information include information of electroencephalograms. More specifically, examples of electroencephalogram information include auditory evoked responses. Specifically, in the auditory brainstem response (ABR), which is one of the auditory evoked responses, it is clinically known that the response classified as I wave originates from the cochlear nerve (posterior labyrinth system). Therefore, in the present embodiment, for example, the case where the height of the I wave of the ABR is less than 0.1V can be defined as positive (+) and the case where the height is above 0.1V can be defined as negative (-).

[0153] also, Fig.11 The additional information 783 shown in can be information indicating a statistical trend due to the auditory state. For example, as the additional information 783, attribute information of the object 901, such as the age, gender, medical history, family history, occupational history, lifestyle, etc. of the object 901, can be used. For example, as the age is higher, disorders of the inner ear and posterior labyrinth system tend to develop with aging. Therefore, in the present embodiment, for example, the additional information 783 may be included in which the case where the age of the object 901 is over 75 years old is set to 1.0 and the case where the age is less than 75 years old is set to 0.0, or the information included in the additional information 783 may be a fraction representing the age by a continuous value from 0.0 to 1.0.

[0154] The degree information 784 of the conductive hearing loss is a value indicating the degree of the conductive hearing loss. In the present embodiment, for example, the air-bone gap may be used as a value indicating the degree of the conductive hearing loss. Instead of using the air-bone gap as it is, the air-bone gap may be converted into a conductive hearing loss score value z and used. In the present embodiment, for example, the conductive hearing loss score value z may be a ratio of the air-bone gap to the air-conduction hearing level expressed by the following formula (4).

[0155] z = air-bone gap / air-conducted pure sound hearing level…(4)

[0156] The conductive hearing loss score value z is a value of about 0.0 to 1.0. In addition, when the conductive hearing loss score value z does not fall within the range of 0.0 to 1.0, further arithmetic processing may be performed on the conductive hearing loss score value z to fall within the range of 0.0 to 1.0. In the present embodiment, for example, z=0.0 may indicate sensorineural hearing loss, z=1.0 may indicate conductive hearing loss, and z greater than 0.0 and less than 1.0 may indicate mixed hearing loss.

[0157] Furthermore, in this embodiment, the degree of conductive hearing loss information 784 is based on Fig.11 Specifically, for example, the air conduction hearing level included in the first group of hearing test information 781 is represented as y1, the SISI test score included in the second group of hearing test information 782 is represented as y2, the TD test score is represented as y3, and the Mth test score included in the second group of hearing test information 782 is represented as y M+1 Then, these values ​​are calculated and set as feature vectors. Furthermore, the conductive hearing loss score value z indicating the degree information 784 of the conductive hearing loss is calculated according to the following formula (5).

[0158]

[0159] In formula (5), U i is the load factor and u0 is a predetermined deviation value. Different statistical determination methods can be used to determine the load factor u i and deviation value u0. For example, a large number of known empty bone gaps and hearing test information 781 and 782 corresponding to the first and second groups are obtained, and learning data in which feature vectors and expected score values ​​(e.g., 0.0 to 1.0) are paired are prepared based on the empty bone gaps and hearing test information 781 and 782. In addition, by performing multiple regression analysis on the learning data, a linear approximation load can be obtained, and the load coefficient u can be determined. iAnd the deviation value u0. In addition, in this embodiment, a neural network may be used instead of the multiple regression analysis, and a discrimination method such as Bayesian estimation method or vector quantization may be used. There is no particular limitation.

[0160] Then, in the present embodiment, the conductive hearing loss score value z of the information 784 indicating the degree of conductive hearing loss can be calculated from the hearing test information 781 and 782 of the first and second groups by using the formula (5) determined as described above.

[0161] In the above description, the conductive hearing loss score value z of the degree information 784 indicating the conductive hearing loss is calculated using a statistical method. However, the present embodiment is not limited to such a method. In the present embodiment, for example, a learning model may be generated using deep machine learning, and the conductive hearing loss score value z of the degree information 784 indicating the conductive hearing loss may be calculated using the learning model.

[0162] Specifically, for example, a learning model can be generated by performing deep machine learning using a plurality of learning data prepared in advance, and the generated learning model can be used to predict the degree information of the conductive hearing loss 784. Here, one learning sample means an information set in which the hearing test information 781 of the first group, the hearing test information 782 of the second group (input data), and the degree information 784 of the conductive hearing loss in the same period of the same subject 901 (teacher data) are set as one set.

[0163] As described above, in the present embodiment, by using a statistical method or a method using the above-mentioned learning model, the degree of conductive hearing loss can be predicted using only air-conducted sound.

[0164] <2.2 Configuration>

[0165] Then, in this embodiment, the above-mentioned prediction of the degree of conductive hearing loss can be performed using a combination of the information processing terminal 117 and the hearing aid 116 (or the earphone speaker 115). Fig.12 and Fig.13 The functional configuration of the information processing terminal 117 according to the present embodiment is described. Fig.12 is a block diagram of the information processing terminal 117 according to the present embodiment and Fig.13 It is an explanatory diagram for explaining the conductive hearing loss prediction unit according to the present embodiment.

[0166] like Fig.12As shown, the information processing terminal 117 according to the present embodiment includes a first group hearing test sound source generating unit (sound source generating unit) 161, a second group hearing test sound source generating unit (sound source generating unit) 162, a test control unit 163, a conductive hearing loss degree predicting unit (prediction unit) 164, and a test information storage unit 165. In addition, the information processing terminal 117 according to the present embodiment includes an additional information storage unit 166, a hearing test sound output tool 171, an information output tool (output unit) 172, an information input tool 73, and a communication tool 174. The functional units included in the information processing terminal 117 according to the present embodiment are explained in order below.

[0167] Note that all or part of the functions of the functional components of the information processing terminal 117 according to the present embodiment described below are not limited to being executed by the information processing terminal 117, and may be executed by, for example, the hearing aid 116, the earphone speaker 115, or a server on the Internet 119. Specifically, for example, the information processing terminal 117 includes a first group hearing test sound source generation unit 161, a second group hearing test sound source generation unit 162, a test control unit 163, a test information storage unit 165, an additional information storage unit 166, and a communication tool 174. The hearing aid 116 or the earphone speaker 115 includes a hearing test sound output tool 171. In addition, the server on the Internet 119 includes a conductive hearing loss degree prediction unit 164.

[0168] (First group of auditory test sound source generating unit 161)

[0169] The first group hearing test sound source generation unit 161 is controlled by the test control unit 163 described below, and generates a sound source of the test sound of the first group hearing test. In addition, the first group hearing test sound source generation unit 161 outputs the generated sound source to the hearing test sound output tool 171. In the present embodiment, for example, when the first group hearing test is a combination of a plurality of tests, the first group hearing test sound source generation unit 161 repeatedly generates and outputs by the number of types of tests.

[0170] (Second group hearing test sound source generating unit 162)

[0171] The second group hearing test sound source generation unit 162 is controlled by the test control unit 163, and generates a sound source of the test sound of the second group hearing test. In addition, the second group hearing test sound source generation unit 162 outputs the generated sound source to the hearing test sound output tool 171. In the present embodiment, for example, when the hearing test of the second group is a combination of a plurality of tests, the second group hearing test sound source generation unit 162 repeatedly generates and outputs by the number of types of tests.

[0172] (Test control unit 163)

[0173] The test control unit 163 controls the sound source generation of the first group hearing test sound source generation unit 161 and the second group hearing test sound source generation unit 162 according to the input information from the information input tool 73 described below, and performs the hearing test according to the rule. In order to smoothly advance the test when performing the hearing test, the test control unit 163 can control the information output tool 172 described below, and perform guidance such as communicating surgery to the subject 901.

[0174] (Conductive hearing loss degree prediction unit 164)

[0175] The conductive hearing loss degree prediction unit 164 can receive the test results of the first and second groups of hearing tests stored in the test information storage unit 165 described below through the test control unit 163. The conductive hearing loss degree prediction unit 164 can predict the degree of conductive hearing loss based on the hearing test results. In addition, the conductive hearing loss degree prediction unit 164 can receive additional information 783 stored in the additional information storage unit 166 described below via the test control unit 163 and predict the degree of conductive hearing loss using the additional information. The conductive hearing loss degree prediction unit 164 can output the predicted prediction information of the degree of conductive hearing loss to the information output tool 172 through the test control unit 163.

[0176] Fig.13 78 shows the input and output of the conductive hearing loss degree prediction unit 164. The conductive hearing loss degree prediction unit 164 receives the input of the first group of hearing test information 781 and the second group of hearing test information 782, and outputs the prediction information of the degree of conductive hearing loss. In addition, additional information 783 may be input to the conductive hearing loss degree prediction unit 164. Then, for example, by using a statistical method or a method using the above-mentioned learning model, the conductive hearing loss degree prediction unit 164 can predict the degree of conductive hearing loss using only air-conducted sound.

[0177] (Test information storage unit 165)

[0178] The test information storage unit 165 stores the result information of the hearing test of the first group and the result information of the hearing test of the second group according to the control of the test control unit 163 .

[0179] (Additional information storage unit 166)

[0180] The additional information storage unit 166 stores the additional information 783 input via the information input tool 73 (specifically, for example, a keyboard, a touch panel, or an external information processing terminal) according to the control of the test control unit 163 .

[0181] (Auditory test sound output tool 171)

[0182] The hearing test sound output tool 171 may output the sound sources generated by the first and second hearing test sound source generation units 161 and 162 toward the subject 901 and perform a test. The hearing test sound output tool 171 may be a receiver of the hearing aid 116, for example.

[0183] (Information output tool 172)

[0184] The information output tool 172 may, for example, display the result information of the first set of hearing tests, the result information of the second set of hearing tests, information such as the predicted degree of conductive hearing loss, information derived from these types of information, etc. For example, the information output tool 172 may be a screen of the information processing terminal 117 or a display device wirelessly connected to the information processing terminal 117.

[0185] (Information Input Tool 73)

[0186] For example, a response from the subject 901 is input to the information input unit 173. Specifically, for example, when performing an air conduction hearing test, the subject 901 continues to press the response button 914 while hearing a sound. At this time, the subject 901 uses the response button 914 as the information input unit 173. In the present embodiment, the information input tool 73 may be such a response button 914, or may be a touch panel or other input device superimposed on the screen of the information processing terminal 117.

[0187] Furthermore, in the present embodiment, the response is not limited to pressing the response button 914, and may be a predetermined motion of the head or arm of the subject 901. In this case, the response may be input by sensing the motion of the subject 901 using an imaging device or an acceleration sensor. In the present embodiment, the response may be the voice of the subject 901. In this case, the voice may be collected by a microphone.

[0188] In addition, in the present embodiment, a response may be input using a biosensor. For example, a brain wave indicating an auditory brainstem response or the like of the subject 901 may be detected by the biosensor and input as a response. That is, in the present embodiment, in the case where the information input unit 173 is a unit capable of inputting information about a response or an answer from the subject 901, the information input unit 173 is not particularly limited.

[0189] (Communication Tool 174)

[0190] The communication tool 174 can receive additional information 783 such as age and gender from an external device, and send the additional information to the additional information storage unit 166 through the test control unit 163. In addition, the communication tool 174 can receive coefficients, deviation values, learning models, etc. used in the conductive hearing loss degree prediction unit 164 from an external device, and send the coefficients, deviation values, learning models, etc. to the conductive hearing loss degree prediction unit 164. Therefore, in the present embodiment, the coefficients, deviation values, and learning models can be always updated to coefficients, deviation values, and learning models with higher accuracy. In addition, the communication tool 174 can send prediction information of the degree of conductive hearing loss predicted by the conductive hearing loss degree prediction unit 164 to an external device.

[0191] It should be noted that in this embodiment, the functional configuration of the information processing terminal 117 is not limited to Fig.12 The configuration shown in .

[0192] <2.3 Information Processing Methods>

[0193] Then, refer to Fig.14 and Fig.15 The flow of the information processing method according to this embodiment will be described. Fig.14 and Fig.15 This is a flowchart for explaining the flow of the information processing method according to the present embodiment.

[0194] exist Fig.14 In the example shown, multiple steps are included in step S201 and step S202. First, Fig.14 In the example shown in , the hearing test of the first group and the hearing test of the second group are performed (step S201). In the present embodiment, the order of performing the test can be determined according to the test to be performed. For example, because the SISI test is usually performed when the hearing threshold is about 20dB higher, it is preferred to complete the hearing test of the hearing threshold in advance. Therefore, in the present embodiment, the hearing test of the hearing threshold can be performed first, and then the SISI test can be performed.

[0195] Subsequently, the degree of conductive hearing loss is predicted based on the result information of the hearing test of the first group and the result information of the hearing test of the second group (step S202), and the process ends. As described above, for example, formula (4) or formula (5) can be used to predict conductive hearing loss.

[0196] Fig.15 Another example is shown. Fig.15 In the example shown, multiple steps from step S301 to step S304 are included. Fig.15 The examples shown in Fig.14The example shown in is different in that when there is no problem with the air conduction hearing level obtained by the hearing test of the first group, the processing is ended without performing the hearing test of the second group. As shown in formula (1), the air conduction hearing level is the sum of the degree of conductive hearing loss and the degree of sensorineural hearing loss. Therefore, when there is no problem with the hearing at the air conduction hearing level, it can be seen that there is no problem with the degree of conductive hearing loss at that point in time. Fig.15 In the example shown, the time required for the entire test can be reduced by ending the hearing test of the second group without performing the hearing test. In particular, in a case such as a group medical test, reducing the test time is important.

[0197] Specifically, in Fig.15 In the example shown, first, a hearing test of the first group is performed (step S301). Subsequently, it is determined whether there is a problem with the air conduction hearing level based on the result information of the hearing test of the first group (step S302). As a determination criterion, for example, it can be determined based on whether the air conduction hearing level is 25dBHL or higher. Then, when there is no problem with the air conduction hearing level (step S302: no), the processing ends. On the other hand, in the case where there is a problem with the air conduction hearing level (step S302: yes), the processing enters step S303. Subsequently, a hearing test of the second group is performed (step S303). Then, based on the result information of the hearing test of the first group and the result information of the hearing test of the second group, the degree of conductive hearing loss is predicted (step S304), and the processing ends. As described above, for example, formula (5) can be used to predict conductive hearing loss.

[0198] <2.4 Application Examples>

[0199] Then, refer to Fig.16 An application example of this embodiment will be described. Fig.16 As described above, when considering purchasing a hearing aid 116, it is preferable to first perform a hearing test in order to understand the hearing strength and decide whether to visit a medical institution before wearing the hearing aid 116.

[0200] For example, in Fig.16In the illustrated example, the subject 901 operates the information processing terminal 117 to access a hearing aid sales site provided by a hearing aid sales company 291 via the Internet 119. It is assumed that the hearing aid sales site of the hearing aid sales company 291 provides a hearing test service. Note that the hearing test service may be provided by the hearing aid sales company 291 itself, or may be provided by a hearing test service providing company 292 that is different from the hearing aid sales company 291. When the hearing test service providing company 292 provides the hearing test service, the result of the hearing test may be provided from the hearing test service providing company 292 to the hearing aid sales company 291, or may be provided directly from the hearing test service providing company 292 to the subject 901.

[0201] Then, the subject 901 operates the information processing terminal 117 to perform the hearing test. In this application example, the program for performing the hearing test may be operated on the Internet 119 or may be operated on the information processing terminal 117, and is not particularly limited. In this application example, the earphone speaker (hereinafter also referred to as earphone) 115 connected to the information processing terminal 117 may not be calibrated for the hearing test. When an uncalibrated earphone 115 is used, if the specifications of the earphone 115 do not meet the sound pressure level and frequency characteristics assumed by the hearing test, the hearing test may not be accurately performed sometimes. Therefore, in this application example, it is preferred to obtain characteristic information (output characteristic information) such as the sound pressure level and frequency characteristics of the earphone 115 in advance before the test. The earphone 115 can be calibrated for the hearing test using this characteristic information. For example, characteristic information of various commercial earphones 115 is pre-stored in the information processing terminal 117, and the subject 901 selects and inputs information such as the model and specification of the earphone 115 owned by the subject 901, so that the information processing terminal 117 acquires characteristic information corresponding to the earphone 115. Alternatively, the information processing terminal 117 may communicate with the earphone 115, acquire information such as a model and specifications from the earphone 115, and download characteristic information of the earphone 115 from the database 299 based on the acquired information. In addition, the information processing terminal 117 may perform a hearing test after performing correction based on the acquired characteristic information (specific correction is described below). Here, the earphone 115 may be a wired type or a wireless type. The earphone 115 is not limited to an overhead earphone, and may be an earphone or a device similar to an earphone.

[0202] It is to be noted that in the present application example, the characteristic information of the earphone 115 is not limited to being pre-stored in the information processing terminal 117. The characteristic information of the earphone 115 may be downloaded from the database 299 to the information processing terminal 117 via the Internet 119 or a line not shown. Furthermore, in the present application example, the calibration of the earphone 115 may be performed on the information processing terminal 117, or the calibration of the earphone 115 may be performed on a program operating on the Internet 119. Furthermore, the subject 901 may respond or reply to the hearing test using the information processing terminal 117 or the like, and receive the test result via the information processing terminal 117 or the like.

[0203] It should be noted that in Fig.16 In the example shown in , when the characteristic information of the earphone 115 owned by the subject 901 cannot be obtained, the information processing terminal 117 or the like may notify the subject 901 to that effect and recommend the use of another earphone 115. Alternatively, when the subject 901 owns a plurality of headphones 115 whose characteristic information is known, the information processing terminal 117 or the like may present the earphone 115 having the characteristic information most suitable for the test among the headphones 115 to the subject 901. For example, when the subject 901 owns two earphones (i.e., an earphone that can output a strong sound pressure level and an earphone that can only output a weak sound pressure level), the former can handle a more deteriorated hearing loss. Therefore, the former is more likely to be applicable to the test. For example, when the subject 901 owns two earphones (i.e., an earmuff-type headphone and an ear-placed headphone), the former can handle an environment with a greater noise. Therefore, the former is more likely to be applicable to the test.

[0204] exist Fig.16 In the example shown, the person who desires hearing aid purchase can learn whether to first consider purchasing the hearing aid 116 or to visit a medical institution before considering purchasing based on the test results of the hearing test. Fig.16 In the example shown in FIG. 1 , since such a hearing test service can be used even without going through the professional 903, a person who desires to purchase a hearing aid can determine whether to consider purchasing the hearing aid 116 or visit a medical institution before considering the purchase. As a result, according to Fig.16 The example shown can prevent the subject 901 from missing out on the opportunity to early treat the disorder that causes hearing loss.

[0205] It should be noted that in reference Fig.16In the explanation of , the application of the hearing test performed when considering the purchase of the hearing aid 116 is explained as an example. However, the scenario to which the embodiments of the present disclosure can be applied is not limited to the time of the purchase consideration of the hearing aid 116. For example, when it is desired to use the hearing test service, the subject 901 can use the hearing test service of the hearing test service providing company 292 using the information processing terminal 117. At this time, the subject 901 can use the earphone 115 owned by the subject 901.

[0206] As described above, in the present embodiment, by combining the results of the first group of hearing tests and the second group of hearing tests including test contents different from each other and applying statistical methods and learning models to these results, the degree of conductive hearing loss can be predicted using only air-conducted sound.

[0207] <<3. Second Embodiment>>

[0208] <3.1 Overview>

[0209] Then, refer to Fig.17 The outline of the second embodiment of the present invention will be described. Fig.17 is an explanatory diagram for explaining the outline of this embodiment. Fig.16 In the example shown in , feature information of the headphones (sound output device) 115 to be used can be acquired based on an image of the headphones 115 .

[0210] Specifically, in this embodiment, if Fig.17 As shown, the earphone 115 owned by the object 901 is imaged by the camera of the information processing terminal 117, and information such as the model and specifications of the earphone 115 is specified by the image recognition technology. Then, in the present embodiment, the characteristic information of the earphone 115 can be acquired based on the information such as the model and specifications of the recognized earphone 115, and used for correction at the time of testing. According to the present embodiment, the characteristic information of the earphone 115 can be easily acquired and corrected without interfering with the object 901. Note that the present embodiment can be mainly executed by a program operating on the Internet 119 or a program operating on the information processing terminal 117.

[0211] <3.2 Configuration>

[0212] Next, refer to Fig.18 The functional configuration of the information processing terminal 117 according to the present embodiment is described. Fig.18 It is a block diagram of the information processing terminal 117 according to the present embodiment.

[0213] like Fig.18As shown in the figure, as in the first embodiment, the information processing terminal 117 according to the present embodiment includes a first group hearing test sound source generation unit 161, a second group hearing test sound source generation unit 162, a test control unit 163, a conductive hearing loss degree prediction unit 164, and a test information storage unit 165. As in the first embodiment, the information processing terminal 117 according to the present embodiment includes an additional information storage unit 166, a hearing test sound output tool 171, an information output tool 172, an information input tool 73, and a communication tool 174. In addition, in the present embodiment, the information processing terminal 117 includes a level / frequency characteristic correction information storage unit 189 and a level / frequency characteristic correction unit 190. The functional units included in the information processing terminal 117 according to the present embodiment are explained in order below. Here, the description of the functional parts common to the first embodiment is omitted. Only the level / frequency characteristic correction information storage unit 189 and the level / frequency characteristic correction unit 190 are explained.

[0214] Note that all or part of the functions of the functional components of the information processing terminal 117 according to the present embodiment described below are not limited to being executed by the information processing terminal 117, and may be executed by, for example, the hearing aid 116, the earphone speaker 115, or a server on the Internet 119. Specifically, for example, the information processing terminal 117 includes a first group hearing test sound source generation unit 161, a second group hearing test sound source generation unit 162, a test control unit 163, a test information storage unit 165, an additional information storage unit 166, a communication tool 174, a level / frequency characteristic correction information storage unit 189, and a level / frequency characteristic correction unit 190. The hearing aid 116 or the earphone speaker 115 includes a hearing test sound output tool 171. In addition, the server on the Internet 119 includes a conductive hearing loss degree prediction unit 164.

[0215] (Horizontal / Frequency Characteristic Correction Information Storage Unit 189)

[0216] The horizontal / frequency characteristic correction information storage unit 189 stores images of various headphones 115 in association with the models of the headphones 115. The images are used when the horizontal / frequency characteristic correction unit 190 specifies the models of the headphones 115 using the image recognition technology. The horizontal / frequency characteristic correction information storage unit 189 also stores characteristic information of various headphones 115. The characteristic information is used when the horizontal / frequency characteristic correction unit 190 performs correction. Note that the information stored in the horizontal / frequency characteristic correction information storage unit 189 can be downloaded from the database 299 via the Internet 119 or a line not shown. It should be noted that in the present embodiment, the horizontal / frequency characteristic correction information storage unit 189 is not limited to storing images of the headphones 115, and may store identification signals and the like output from the headphones 115. In this case, by checking the identification signals and the like stored in the horizontal / frequency characteristic correction information storage unit 189 and the identification signals and the like acquired from the headphones 115, information such as the model and specifications of the headphones 115 can be specified.

[0217] (Horizontal / Frequency Characteristic Correction Unit 190)

[0218] The level / frequency characteristic correction unit 190 may correct the sound sources of the test sounds generated by the first group hearing test sound source generation unit 161 and the second group hearing test sound source generation unit 162 based on the characteristic information of the earphone 115 stored in the level / frequency characteristic correction information storage unit 189. In addition, the level / frequency characteristic correction unit 190 may output the corrected test sound sources to the hearing test sound output tool 171.

[0219] When acquiring the characteristic information of the headphones 115 , the horizontal / frequency characteristic correction unit 190 may specify the model of the headphones 115 based on the image of the headphones 115 using an image recognition technique.

[0220] It should be noted that in this embodiment, the functional configuration of the information processing terminal 117 is not limited to Fig.18 The configuration shown in .

[0221] <3.3 Information Processing Methods>

[0222] Then, refer to Fig.19 The flow of the information processing method according to this embodiment will be described. Fig.19 : is a flowchart showing the flow of the information processing method according to the present embodiment.

[0223] like Fig.19As shown, the information processing method according to the present embodiment includes a plurality of steps from step S401 to step S403. First, the level / frequency characteristic correction information is set (step S401). Specifically, the model of the earphone 115 is specified by applying image recognition technology to the image of the earphone 115 owned by the object 901 captured by the camera of the information processing terminal 117. Then, the characteristic information of the earphone 115 is acquired based on the designated model of the earphone 115. Based on the acquired information, the level / frequency characteristic correction information for correcting the test sound source is set. In addition, the sound source of the test sound is corrected according to the set level / frequency characteristic correction information. It should be noted that in the present embodiment, when the characteristic information of the earphone 115 used by the object 901 cannot be acquired, the object 901 is notified to this effect and the processing is terminated.

[0224] In addition, in this embodiment, steps S402 and S403 are performed in sequence. However, these steps are different from those in the embodiment described in Fig.14 Steps S201 and S202 of the information processing method of the first embodiment shown in FIG. 1 are the same. Therefore, the description of the steps is omitted here.

[0225] As described above, in this embodiment, since the earphone 115 owned by the object 901 is photographed by the camera of the information processing terminal 117 and the model of the earphone 115 is specified by the image recognition technology, the characteristic information of the earphone 115 can be easily acquired and corrected without interfering with the object 901.

[0226] <<4. Third embodiment>>

[0227] Then, refer to Fig. 20 An overview of a third embodiment of the present disclosure will be described. Fig. 20 1 is a flowchart for explaining the flow of the information processing method according to this embodiment. This embodiment is an application example when determining the necessity of visiting a medical institution before wearing a hearing aid. In this embodiment, it is mainly assumed that the subject 901 performs the examination by himself.

[0228] like Fig. 20 As shown, the information processing method according to this embodiment includes multiple steps from step S501 to step S508.

[0229] First, as in the above-mentioned embodiment, the first group hearing test and the second group hearing test are performed (step S501). Then, the degree of conductive hearing loss is predicted based on the result information of the first group hearing test and the result information of the second group hearing test (step S502).

[0230] Then, it is determined whether there is a problem with the hearing (step S503). In step S503, it is determined whether the level is a level suitable for wearing a hearing aid. In the present embodiment, for example, whether the air conduction hearing level is 40dBHL or more can be used as a criterion. When it is determined that there is no problem with the hearing (step S503: No), the process proceeds to step S504. Then, the recommended object 901 is followed up regularly as needed (step S504), and the process ends.

[0231] On the other hand, when it is determined that there is a problem with hearing (step S503: Yes), the processing proceeds to step S505. Then, it is determined whether the predicted value of the degree of conductive hearing loss is high (step S505). In the present embodiment, for example, when the predicted value of the degree of conductive hearing loss is above 25dBHL, a standard for determining that the predicted value of the degree of conductive hearing loss is high can be used. In this case, the predicted degree of conductive hearing loss is compared with a reference value (predetermined threshold value) of 25dBHL to determine. When it is determined that the predicted value of the degree of conductive hearing loss is not high (step S505: No), the processing proceeds to step S506. Then, it is recommended that the object 901 consider wearing a hearing aid (step S506), and the processing ends.

[0232] When it is determined that the predicted value of the degree of conductive hearing loss is high (step S505: Yes), the processing proceeds to step S507. Then, the subject 901 is asked whether he has confirmed with a practicing physician or the like that there is no problem in wearing the hearing aid (step S507). For example, in a case where the subject 901 has completed the treatment of the conductive hearing loss and still has the conductive hearing loss, it is determined that there is a high possibility that there is no problem in wearing the hearing aid. In the case of an answer that the confirmation with the practicing physician or the like has been completed (step S507: No), the processing proceeds to step S506. On the other hand, in the case of an answer that the confirmation with the practicing physician or the like has not been completed (step S507: Yes), the processing proceeds to step S508. In addition, it is recommended that the subject 901 visit a medical institution or the like (step S508), and the processing ends.

[0233] It should be noted that Fig. 20 In the flowchart shown in FIG. 5 , it is determined in step S503 whether there is a problem with hearing. However, the present embodiment is not limited thereto. In the present embodiment, for example, Fig.15 As shown, it can be determined whether there is a hearing problem between the first set of hearing tests and the second set of hearing tests.

[0234] The information processing method according to this embodiment may be modified. Fig.21 and Fig. 22 Modifications will be described. Fig.21 and Fig. 22 1 is a flowchart for explaining the process of an information processing method according to a modified example of the present embodiment. Fig.21 and Fig. 22 As shown, the information processing method according to this variation includes multiple steps from step S601 to step S613.

[0235] Specifically, in this variation, first, the hearing test of the first group is performed (step S601). Then, 0 is input to the count i of the hearing test of the second group (step S602). In addition, 1 is added to the count i of the hearing test of the second group (step S603).

[0236] Subsequently, the i-th hearing test of the second group of hearing tests including a plurality of hearing tests is performed (step S604). Then, the degree of conductive hearing loss is predicted based on the result information of the first group of hearing tests and the result information of the second group of hearing tests that have been performed, and the predicted probability of the degree of conductive hearing loss is predicted (step S606). In this modification, for example, the likelihood may be estimated as the predicted probability of the degree of conductive hearing loss. In this case, by performing deep machine learning using a large amount of known learning data used to generate the above-mentioned learning model, an estimation model for estimating the likelihood may be generated, and the likelihood of the re-predicted degree of conductive hearing loss may be estimated using the estimation model.

[0237] Subsequently, it is determined whether the count i of the hearing test of the second group is a predetermined value M (step S606). The predetermined value M may be, for example, the same as the number of hearing tests included in the hearing test of the second group, or may be appropriately set by the user. In the case where the count i of the hearing test of the second group is not the predetermined value M (step S606: Yes), the process proceeds to step S607. When the count i of the hearing test of the second group is the predetermined value M (step S606: No), the process proceeds to step S608. Fig. 22 Step S608 shown in FIG.

[0238] Subsequently, it is determined whether the predicted probability of the degree of conductive hearing loss predicted in step S605 is a sufficient probability (step S607). For example, the predicted probability of the degree of conductive hearing loss can be determined by comparing with a predetermined threshold. When the predicted probability of the degree of conductive hearing loss is sufficient (step S607: yes), the process proceeds to Fig. 22 . On the other hand, when the predicted probability of the degree of conductive hearing loss is insufficient (step S607: No), the process returns to step S603. From step S603, the next (i+1) hearing test in the second group of hearing tests including a plurality of hearing tests is performed, and the degree of conductive hearing loss is predicted using the result information of the second group of hearing tests which is greater in number than the last one. Therefore, the possibility that the predicted probability of the degree of conductive hearing loss is improved increases.

[0239] In addition, execution Fig. 22 However, these steps are different from those in the reference Fig. 20 The information processing method according to the present embodiment described above has the same steps S502 to S508. Therefore, the description of the steps is omitted here.

[0240] In this modification, the number of tests of the hearing test of the second group is increased until the prediction of the degree of conductive hearing loss has a constant probability. Therefore, according to this modification, since the hearing test of the second group is ended at the stage of obtaining the prediction of the degree of conductive hearing loss with a constant probability, that is, all the hearing tests of the second group are not always performed each time, the time required for the entire test can be reduced.

[0241] Next, refer to Fig.23 , describing the following implementation method: when a practicing physician or the like has confirmed that the predicted value of the degree of conductive hearing loss is not high or that there is no problem in wearing a hearing aid even if the predicted value of the degree of conductive hearing loss is high, the screen automatically changes to a hearing aid purchase screen. Fig.23 1 is a flowchart for explaining the flow of the information processing method according to the present embodiment. In addition, in the present embodiment, a purchase button may be used instead of the screen transition to the hearing aid purchase screen. In the present embodiment, since the subject 901 always performs a hearing test before the screen transitions to the hearing aid purchase screen, it is possible to prevent the subject 901 from purchasing the hearing aid 116 without noticing the hearing test service or from accidentally purchasing the hearing aid 116, regardless of whether the subject 901 is recommended to visit a medical institution in the hearing test service.

[0242] like Fig.23 As shown, the information processing method according to this embodiment includes multiple steps from step S701 to step S708. It should be noted that the steps other than step S706 are the same as those in the reference Fig. 20 The information processing method according to the present embodiment described above has the same steps S501 to S505 and S507 and S508. Therefore, the description of the steps is omitted here.

[0243] In this embodiment, the screen changes to the hearing aid purchase screen (step S706), and the process ends. On the hearing aid purchase screen, the purchase process can be performed.

[0244] It should be noted that Fig.23 In the flowchart shown in FIG. 1 , it is determined in step S703 whether there is a hearing problem. However, the present embodiment is not limited thereto. In the present embodiment, for example, Fig.15 As shown, it can be determined whether there is a hearing problem between the first set of hearing tests and the second set of hearing tests.

[0245] By the way, when purchasing goods or services on the website, the process is sometimes interrupted in the middle. Based on this situation, for example, despite the Fig.23 The hearing test is performed according to the process, but the processing reaches step S706 and the screen switches to the hearing aid purchase screen, however, access to the website is sometimes interrupted for some reason. Afterwards, in the case where the subject 901 wants to restart the purchase procedure, if the hearing test is performed again, there is a possibility that the subject 901's willingness to purchase the hearing aid 116 is greatly reduced. Thus, in the present embodiment, for example, this situation is avoided by being able to immediately skip the processing of step S706 as needed. For example, when the processing reaches step S706 once, information related to reaching step S706 is stored, and the information is confirmed at the next access to resume the processing from step S706. Note that in this case, since hearing changes over time, the elapsed time (specifically, the elapsed period from the last test) used to allow the processing to be immediately resumed from step S706 can be determined.

[0246] As described above, in the present embodiment, since the subject 901 can perform the examination himself and the degree of conductive hearing loss can be predicted, the subject 901 can learn whether to continue the purchase consideration of the hearing aid 116 or visit a medical institution before the purchase consideration even at the subject 901's home or the like. As a result, according to the present embodiment, it is possible to prevent the subject 901 from losing the opportunity to treat the obstacle that causes the hearing loss at an early stage. In addition, according to the present embodiment, even in the case of purchasing the hearing aid 116 via the Internet 119, it is possible to predict the degree of conductive hearing loss of the person who wants to purchase, so it is possible to prevent the person who wants to purchase from purchasing the hearing aid 116 wearing an inappropriate hearing aid.

[0247] <<5. Fourth embodiment>>

[0248] <5.1 Configuration>

[0249] Next, an overview of a fourth embodiment of the present invention will be described. This embodiment is an embodiment capable of setting hearing aid parameters of the hearing aid 116. First, reference will be made to Fig.24 The functional configuration of the information processing terminal 117 according to the present embodiment is described. Fig.24 It is a block diagram of the information processing terminal 117 according to the present embodiment.

[0250] like Fig.24As shown in FIG. 1 , as in the first embodiment, the information processing terminal 117 according to the present embodiment includes a first group hearing test sound source generating unit 161, a second group hearing test sound source generating unit 162, a test control unit 163, a conductive hearing loss degree predicting unit 164, and a test information storage unit 165. As in the first embodiment, the information processing terminal 117 according to the present embodiment includes an additional information storage unit 166, a hearing test sound output tool 171, an information output tool 172, an information input tool 73, and a communication tool 174. Furthermore, in the present embodiment, the information processing terminal 117 includes a hearing aid parameter determining unit 197 and a hearing aid parameter storage unit 198. The functional units included in the information processing terminal 117 according to the present embodiment are explained in sequence. However, the description of the functional parts common to the first embodiment is omitted here, and only the hearing aid parameter determining unit 197 and the hearing aid parameter storage unit 198 are described.

[0251] Note that all or part of the functions of the functional components of the information processing terminal 117 according to the present embodiment described below are not limited to being executed by the information processing terminal 117, and may be executed by, for example, the hearing aid 116, the earphone speaker 115, or a server on the Internet 119. Specifically, for example, the information processing terminal 117 includes a first group hearing test sound source generation unit 161, a second group hearing test sound source generation unit 162, a test control unit 163, a test information storage unit 165, an additional information storage unit 166, and a communication tool 174. The hearing aid 116 or the earphone speaker 115 includes a hearing test sound output tool 171 and a hearing aid parameter storage unit 198. In addition, the server on the Internet 119 includes a conductive hearing loss degree prediction unit 164 and a hearing aid parameter determination unit 197.

[0252] (Hearing Aid Parameter Determination Unit 197)

[0253] The hearing aid parameter determination unit 197 may obtain the degree prediction information of the conductive hearing loss predicted by the conductive hearing loss degree prediction unit 164 through the test control unit 163, and determine the hearing aid parameters as the setting parameters of the hearing aid 116 based on the predicted degree of conductive hearing loss. The hearing aid parameters may be parameters used for gain setting control and noise suppression setting control (noise suppression strength, frequency characteristics, etc.) of the hearing aid 116. More specifically, the hearing aid parameters may be parameters for gain setting, such as Figure 44 754 is shown in FIG. 4 . For example, commonly and widely used schemes such as NAL-NL2 (National Acoustic Laboratory Nonlinear 2), DSLv5 (Desired Sensing Level Version 5), etc. can be used to determine hearing aid parameters. These schemes use air conduction hearing level and bone conduction hearing level as input data. If there is air conduction hearing level (result information of the first group of hearing tests) and prediction information of the degree of conduction hearing loss, the bone conduction hearing level can be calculated according to the above formulas (1) and (2).

[0254] In addition, for example, a person with sensorineural hearing loss tends to have more difficulty hearing in noise than a person with conductive hearing loss. Therefore, the hearing aid parameter determination unit 197 can determine the intensity and frequency characteristics of noise suppression using the degree prediction information of the conductive hearing loss and the degree prediction information of the sensorineural hearing loss. More specifically, for example, the hearing aid parameter determination unit 197 increases the intensity of noise suppression when the degree of sensorineural hearing loss is large. In addition, the hearing aid parameter determination unit 197 outputs the determined hearing aid parameter to the hearing aid parameter storage unit 198.

[0255] (Hearing aid parameter storage unit 198)

[0256] The hearing aid parameter storage unit 198 stores the hearing aid parameters determined by the hearing aid parameter determination unit 197 .

[0257] It should be noted that in this embodiment, the functional configuration of the information processing terminal 117 is not limited to Fig.24 The configuration shown in .

[0258] <5.2 Information Processing Methods>

[0259] Then, refer to Fig.25 and Fig.26 The flow of the information processing method according to this embodiment will be described. Fig.25 This is a flowchart for explaining the flow of the information processing method according to the present embodiment. Fig.26 is an explanatory diagram for explaining this embodiment. Fig.25 As shown, the information processing method according to this embodiment includes multiple steps from step S801 to step S803.

[0260] First, as in the above-mentioned embodiment, the hearing test of the first group and the hearing test of the second group are performed (step S801). Subsequently, the degree of conductive hearing loss is predicted based on the result information of the hearing test of the first group and the result information of the hearing test of the second group. At this time, in the present embodiment, the bone conduction hearing level is also predicted (step S802). If there is a predicted value of the air conduction hearing level (the hearing test information of the first group) and the degree of conductive hearing loss, the predicted value of the bone conduction hearing level can also be calculated according to the above-mentioned formula (1) and formula (2).

[0261] Then, a hearing aid parameter as a setting of the hearing aid 116 is determined based on the predicted values ​​of the air conduction hearing level and the bone conduction hearing level (step S803). For example, when determining the gain setting of the hearing aid 116, a generally widely used scheme NAL-NL2 or DSLv5 may be used. In addition, in the present embodiment, a unique scheme may be used to determine the hearing aid parameter.

[0262] Then, if Fig.26 As shown, the information processing terminal 117 performs a hearing test using the hearing aid 116 and obtains prediction information of the degree of conductive hearing loss. Then, the information processing terminal 117 registers the result information of the hearing test, the additional information 783, and the prediction information of the degree of conductive hearing loss in the database 299 on the Internet 119. That is, the database 299 on the Internet 119 stores various information. Then, the information stored in the database 299 can be used to improve the accuracy of the prediction of the degree of conductive hearing loss. For example, by comparing the relationship between various hearing test information in the learning data used to create the learning model and the average value and variance of the various hearing test information with the relationship between the information stored in the database 299, the difference from the learning data can be known, resulting in improvement of the learning data.

[0263] In addition, the information transmitted from the information processing terminal 117 to the database 299 may include log data on fine-tuning of the hearing aid 116. The difference from the log data in the case of the predicted value of the degree of conductive hearing loss can be grasped by comparing with the fine-tuning log data prepared separately when performing the bone conduction hearing test, and the learning data can be improved.

[0264] <5.3 Display Example>

[0265] Then, refer to Fig. 27 and Fig.28 A display example in this embodiment will be described. Fig. 27 and Fig.28 It is an explanatory diagram for explaining a display example according to the present embodiment.

[0266] Fig. 27This is a display example when displaying the predicted value of the bone conduction hearing level on the audiogram. The predicted value of the bone conduction hearing level can be calculated using the above-mentioned formula (1) and formula (2) using the air conduction hearing level (the result information of the hearing test of the first group) and the predicted value of the degree of conductive hearing loss. The audiogram is the most widely used display method when displaying hearing. In this embodiment, the hearing can be displayed in the form of an audiogram using the predicted value of the bone conduction hearing level.

[0267] In this embodiment, the audiogram is preferably displayed so that the bone conduction hearing level is seen as a predicted value. Fig. 27 In the example shown in , the bone conduction hearing level is indicated as a predicted value together with the field of the audiogram. Therefore, a person viewing the audiogram can recognize that the bone conduction hearing level described in the audiogram is a predicted value. It should be noted that in this embodiment, the display form is not limited to Fig. 27 The form shown in .

[0268] Fig.28 This is a display example when the predicted value of the bone conduction hearing level is represented as data. In this embodiment, the predicted value can be represented as data inside a device that has predicted the predicted value, can be represented as data during data communication between different types of devices, or can be represented as data in different types of devices, and is not particularly limited. Fig.28 In the example shown in , a "prediction flag" indicating that the bone conduction hearing level is a predicted value is included. Specifically, for example, it is decided that 1 represents a predicted value and 0 represents a measured value. In this way, even in a device different from the device in which the bone conduction hearing level is predicted, it is possible to distinguish whether it is a predicted value or a measured value. Fig.28 In the embodiment, the prediction marker is added to the bone conduction hearing level. However, in the present embodiment, the prediction marker can be added to the air-bone gap, the degree of conductive hearing loss, and the degree of sensorineural hearing loss, so that it can be seen that the air conduction difference, the degree of conductive hearing loss, and the degree of sensorineural hearing loss are predicted values. Thus, for example, a device that has received data to which the prediction marker has been added can change the content of processing between measurement and prediction.

[0269] As described above, in the present embodiment, since the subject 901 can perform a self-examination and predict the degree of conductive hearing loss, the subject 901 can appropriately install the hearing aid 116 in a place such as the subject 901's home.

[0270] <5.4 Application Examples>

[0271] Reference Figure 29 to Figure 31 An example of application of the hearing ability information to an external device other than the hearing aid 116 will be described. Fig.29 and Fig.30It is an explanatory diagram for explaining an application example according to the present embodiment. Fig.31 is a block diagram of an external device according to the present embodiment.

[0272] In this application example, Fig.29 As shown, the information processing terminal 117 obtains the degree prediction information of the conductive hearing loss and the air conduction hearing level of the subject 901, and then transmits these types of information to the external device 120. Optionally, the information processing terminal 117 may obtain the degree prediction information of the conductive hearing loss and the air conduction hearing level of the subject 901, and then determine the parameters for controlling the external device 120, and send the determined parameters to the external device 120. Fig.29 In the example shown, the external device 120 is a television device (acoustic device). Note that in the present embodiment, the external device 120 is not limited to a television device (acoustic device). The external device 120 can receive information from the information processing terminal 117 and change the processing content in the external device 120. In the following description, two examples of the processing performed by the external device 120 are described.

[0273] As a first example, for example, for an object 901 with a strong degree of sensorineural hearing loss, the external device 120 may weaken the signal level channel other than the audio channel compared to the audio channel in the multi-channel signal of the video content. Alternatively, the channel may be an object. In the case of sensorineural hearing loss, the frequency discrimination ability tends to decrease. Therefore, when a sound other than the voice overlaps with the voice, the object 901 often feels a stronger difficulty in listening to the voice than a normal listener. Although some hearing aids 116 have a function of sound enhancement processing, listening can be improved more reliably by not outputting sounds that may interfere with listening from the television device. Therefore, in this application example, the external device 120 performs a process of suppressing the intensity (volume) of the signal other than the voice output from the external device 120 based on hearing information such as the degree prediction information of the conductive hearing loss of the object 901, the air conduction hearing level, and the parameters sent from the information processing terminal 117, etc. In this application example, the external device 120 can change the content of the processing according to whether the received information is actual measurement information or prediction information. For example, when the received information is prediction information, it is conceivable that the effect of the processing is reduced compared to when the received information is measurement information.

[0274] As a second example, for example, the external device 120 can suppress the subject 901 with a strong sensorineural hearing loss, the sound of a door closing forcefully, and a sudden sound (such as a gunshot). In the case of sensorineural hearing loss, compression processing is generally performed by the hearing aid 116 due to the supplementation phenomenon. However, in order to maintain the naturalness of the voice intonation, the attack time (specifically, the time from when the sound rises until the compression amount reaches a predetermined value) cannot be greatly reduced. Therefore, in order to suppress the sudden sound without shortening the attack time, it is effective to read the sound signal in advance.

[0275] Fig.30 An example of suppressing sudden sounds and the effect of look-ahead is shown. Fig.30 The top of shows an example where a weak sound suddenly becomes a strong sound. Specifically, in this example, at 20 milliseconds, a weak sound suddenly becomes a strong sound. Fig.30 The second part from the top is an example of suppressing a sudden noise by compression without read-ahead (no processing delay). The sudden sound is fully suppressed at about 40 milliseconds, but Fig.30 The top example doesn't change much at about 20 milliseconds. Fig.30 The bottom of FIG shows an example of allowing 4 milliseconds of read-ahead (ie, a processing delay of 4 milliseconds). Fig.30 As shown at the bottom of FIG. 1 , it can be seen that the sudden sound is also suppressed near the time of 24 milliseconds. In addition, by further increasing the length of the pre-reading, the suppression amount can be further increased.

[0276] However, the pre-reading in the hearing aid 116 has a serious adverse effect. Since the pre-reading causes a processing delay, the hearing aid 116 cannot actively use the pre-reading. When the processing delay occurs, there is a problem in that the processing delay causes discomfort of mixing of the sound entering from the gap between the hearing aid 116 and the ear canal and the sound amplified by the hearing aid 116 or causes discomfort of a time difference between visual perception and auditory perception.

[0277] However, while pre-reading is not a realistic option in the hearing aid 116, pre-reading is believed to be a realistic and effective option in the external device 120. Fig.31 A block diagram of an external device 120 having such a configuration for audio and video control is shown in FIG. Fig.31 As shown, the external device 120 mainly includes an audio and video control unit 595 , a hearing information storage unit 596 , an audio processing unit 597 and a video delay amount adjustment unit 598 .

[0278] The hearing information storage unit 596 stores hearing information such as the degree prediction information of the conductive hearing loss of the subject 901, the air conduction hearing level, and parameters transmitted from the information processing terminal 117. The audio and video control unit 595 controls the audio processing unit 597 based on the hearing information stored in the hearing information storage unit 596. For example, the audio processing unit 597 Fig.30 The audio signal shown at the top is processed into Fig.30 , and outputs the audio signal. The audio signal processed by the audio processing unit 597 has a delay. Thus, the audio video control unit 595 controls the video delay amount adjustment unit 598. Specifically, the video delay amount adjustment unit 598 receives the video signal, adjusts the delay amount, and outputs the video signal. The delay amount added by the video delay amount adjustment unit 598 is determined according to the delay amount in the audio processing unit 597.

[0279] As described above, according to this application example, by adjusting the delay amount of the video signal according to the processing delay of the audio signal, it is possible to suppress the sudden sound of the audio signal while suppressing the deviation between the audio signal and the video signal.

[0280] In addition, the audio processing performed by the audio processing unit 597 may be processing based on the hearing level of the hearing information supplement object 901 stored in the hearing information storage unit 596, or may be processing for obtaining an effect different from the hearing level. For example, when the user of the hearing aid 116 is listening to the sound output from the speaker of the television device through the hearing aid 116, processing for giving a delay (such as sudden sound suppression) may be performed on the television device side, and processing for supplementing the hearing level may be left to normal processing on the hearing aid 116 side. Thus, when the hearing aid user and his / her family are watching TV together, the family can also enjoy natural sound while suppressing discomfort caused by the sudden sound of the hearing aid user. As described above, since the hearing aid 116 cooperates with the external device 120, the bad part of the hearing aid 116 can be supplemented.

[0281] It should be noted that in this application example, the functional configuration of the external device 120 is not limited to Fig.31 The configuration shown in .

[0282] <<6. Conclusion>>

[0283] As described above, in an embodiment of the present disclosure, the degree of conductive hearing loss can be predicted using air conduction headphones (i.e., air conduction sound). Therefore, according to an embodiment of the present disclosure, the subject 901 can be recommended to consult a medical institution, etc., and the subject 901 can be prevented from losing the opportunity for early treatment of the disorder causing the hearing loss. In addition, according to an embodiment of the present invention, the gain of the hearing aid 116 of the subject 901 can be appropriately set according to the hearing of the subject 901.

[0284] <<7. Overview of Hearing Assist System>>

[0285] Reference Figure 32 to Figure 35 An overview of a hearing aid system 1 according to an embodiment of the present disclosure is described. Fig.32 is a diagram showing a schematic configuration of a hearing aid system 1 according to an embodiment of the present disclosure, Fig.33 is a functional block diagram of a hearing aid 2 and a charger 3 according to an embodiment of the present disclosure, and Fig.34 is a block diagram of an information processing terminal 40 according to an embodiment of the present disclosure. Fig.35 is a block diagram of the server 90 according to an embodiment of the present disclosure.

[0286] like Fig.32 As shown, the hearing aid system 1 according to the embodiment of the present disclosure includes: a pair of left and right hearing aids 2; a charger 3 (charging case) that accommodates the hearing aids 2 and charges the hearing aids 2; and an information processing terminal 40 such as a smartphone that can communicate with at least one of the hearing aids 2 and the charger 3. In addition, the hearing aid system 1 according to the embodiment of the present disclosure includes a server 90 managed by a hearing aid sales company 291 or a hearing test service providing company 292. The devices included in the hearing aid system 1 according to the embodiment of the present disclosure are explained in order below.

[0287] In the following description, it is assumed that the hearing aid 2 is composed of a pair of hearing aids for both ears. However, the embodiment of the present disclosure is not limited thereto, and may be a monaural hearing aid worn on one of the left and right ears.

[0288] First, the functional structure of the hearing aid 2 is described. In the embodiment of the present disclosure, at least a portion of the hearing aid 2 is configured to be worn on a portion of the user's ear canal. Fig.33 As shown, the hearing aid 2 mainly includes a sound collecting unit 20 ( 20 b , 20 f ), a signal processing unit 21 , an output unit 22 , a battery 25 , a connecting unit 26 , communication units 27 and 30 , a storage unit 28 , and a control unit 29 .

[0289] The sound collecting unit 20 includes: an external (feedforward) sound collecting unit 20f that collects sound in the external area of ​​the ear canal; and an internal (feedback) sound collecting unit 20b that collects sound in the internal area of ​​the ear canal. It should be noted that in the hearing aid 2 according to the embodiment of the present disclosure, it is only necessary to set the external sound collecting unit 20f that collects at least the sound in the external area of ​​the ear canal. The sound collecting unit 20 includes a microphone (hereinafter also referred to as a microphone) 201 and an analog / digital (A / D) conversion unit 202. The microphone 201 collects sound, generates an analog audio signal (acoustic signal), and outputs the analog audio signal to the A / D conversion unit 202. The A / D conversion unit 202 performs digital conversion processing on the analog audio signal input from the microphone 201 and outputs the digitized audio signal to the signal processing unit 21.

[0290] The signal processing unit 21 performs prescribed signal processing on the digital audio signal input from the sound collecting section 20 under the control of the control unit 29 described later, and outputs it to the output unit 22. Here, examples of the predetermined signal processing include: filtering processing for separating the audio signal for each predetermined frequency band; amplification processing for amplifying the audio signal with a predetermined amplification amount for each predetermined frequency band, wherein the filtering processing is performed on each predetermined frequency band; noise reduction processing; and howling removal processing. The signal processing unit 21 can be configured by, for example, a memory and a processor including hardware such as a DSP (digital signal processor).

[0291] The output unit 22 includes a D / A (digital / analog) conversion unit 221 and a receiver 222. The D / A conversion unit 221 performs analog conversion processing on the digital audio signal input from the signal processing unit 21 and outputs the digital audio signal to the receiver 222. The receiver 222 outputs an output sound (voice) corresponding to the analog audio signal input from the D / A conversion unit 221. The receiver 222 can be configured using, for example, a speaker.

[0292] The battery 25 supplies power to the units constituting the hearing aid 2. The battery 25 may be configured by, for example, a rechargeable secondary battery such as a lithium ion battery. In addition, the battery 25 can be charged by power supplied from the charger 3 via the connection unit 26.

[0293] For example, when hearing aid 2 is stored in charger 3, connection unit 26 is connected to a connection portion of charger 3 to receive power and various information from charger 3 and output various information to charger 3. Connection unit 26 may be configured using, for example, a plurality of pins.

[0294] Under the control of the control unit 29, the communication unit 27 can communicate with the charger 3 or the information processing terminal 40 through the Internet 484 according to a predetermined communication standard. Here, as the predetermined communication standard, for example, Wi-Fi (registered trademark), Bluetooth (registered trademark), etc. are assumed. The communication unit 27 can be configured using, for example, a communication module, etc. In addition, under the control of the control unit 29, the communication unit 30 can communicate with another hearing aid 2 through short-range communication such as NFMI (Near Field Magnetic Induction).

[0295] The storage unit 28 stores various information related to the hearing aid 2. The storage unit 28 can be configured using, for example, a RAM (Random Access Memory), a ROM (Read Only Memory), a memory card, etc. The storage unit 28 can store a program 281 executed by the hearing aid 2 and various data 282 used in the hearing aid 2. Examples of the data 282 include the age of the user, the presence or absence of the user's experience of using the hearing aid 2, and the gender of the user. In addition, examples of the data include the use time of the hearing aid 2 by the user timed by a timing unit (not shown). In addition, the timing section is provided inside the hearing aid 2, and is capable of measuring the date and time, outputting the timing result to the control unit 29, etc. The clock unit can be configured using, for example, a timing generator or a timer having a clock function.

[0296] The control unit 29 controls the units constituting the hearing aid 2. The control unit 29 can be configured using, for example, a memory and a processor including hardware such as a central processing unit (CPU) or a DSP. The control unit 29 reads out a stored program 281 to a working area of ​​the memory, and executes the program by the processor to control components and the like.

[0297] Although in Fig.33 Although not shown, the hearing aid 2 may include an operation unit. The operation unit is capable of receiving an input of an activation signal (trigger signal) for activating the hearing aid 2 and outputting the received activation signal to the control unit 29. The operation unit may be configured using, for example, a push switch, a button, or a touch panel.

[0298] Next, the functional structure of the charger 3 is described. Fig.33 As shown, the charger 3 mainly includes a display unit 31 , a battery 32 , a storage unit 33 , a communication unit 34 , a storage unit 35 and a control unit 36 ​​.

[0299] The display unit 31 displays various states related to the hearing aid 2 under the control of the control unit 36. For example, the display unit 31 can display information indicating that the hearing aid 2 is being charged and information indicating that various information is being received from the information processing terminal 40. The display unit 31 can be configured using, for example, a light emitting diode (LED).

[0300] The battery 32 supplies power to units constituting the hearing aid 2 and the charger 3 accommodated in the accommodation unit 33 through a connection unit 331 provided in the accommodation unit 33. The battery 32 can be configured using a secondary battery such as a lithium ion battery.

[0301] The accommodating unit 33 stores each of the left and right hearing aids 2, respectively. In the accommodating unit 33, a connection unit 331 connectable to the connection unit 26 of the hearing aid 2 is provided. When the hearing aid 2 is accommodated in the accommodating unit 33, the connection unit 331 is connected to the connection unit 26 of the hearing aid 2, transmits power from the battery 32 and various information from the control unit 36, receives various information from the hearing aid 2, and outputs the information to the control unit 36. The connection unit 331 can be configured using, for example, a plurality of pins.

[0302] The communication unit 34 communicates with the information processing terminal 40 via the communication network according to a predetermined communication standard under the control of the control unit 36. The communication unit 34 can be configured using, for example, a communication module.

[0303] The storage unit 35 stores various programs 351 executed by the charger 3. The storage unit 35 can be configured using, for example, a RAM, a ROM, a flash memory, or a memory card.

[0304] The control unit 36 ​​controls the units constituting the charger 3. For example, when the hearing aid 2 is accommodated in the accommodation unit 33, the control unit 36 ​​causes the battery 32 to supply power via the connection unit 331. The control unit 36 ​​can be configured using, for example, a memory and a processor including hardware such as a CPU or a DSP. The control unit 36 ​​reads out the program 351 to a work area of ​​the memory, executes the program 351, and controls the components and the like by executing the program through the processor.

[0305] Next, the functional configuration of the information processing terminal 40 will be described. Fig.34 As shown, the information processing terminal 40 mainly includes an input unit 41 , a communication unit 42 , an output unit 43 , a display unit 44 , a storage unit 45 and a control unit 46 .

[0306] The input unit 41 receives input of various operations from the user, and outputs a signal corresponding to the received operation to the control unit 46. The input unit 41 can be configured using, for example, a switch or a touch panel.

[0307] The communication unit 42 communicates with the charger 3 or the hearing aid 2 via the communication network under the control of the control unit 46. The communication unit 42 can be configured using, for example, a communication module.

[0308] The output unit 43 outputs a volume of a predetermined sound pressure level for each predetermined frequency band under the control of the control unit 46. The output unit 43 can be configured using a speaker, for example.

[0309] The display unit 44 displays various information on the information processing terminal 40 and information on the hearing aid 2 under the control of the control unit 46. The display unit 44 can be configured using, for example, a liquid crystal display or an organic EL display (Organic Electroluminescent Display).

[0310] The storage unit 45 stores various information about the information processing terminal 40. For example, the storage unit 45 stores various programs 451 executed by the information processing terminal 40. The storage unit 45 can be configured using a recording medium such as a RAM, a ROM, a flash memory, or a memory card.

[0311] The control unit 46 controls the units constituting the information processing terminal 40. For example, the control unit 46 can be configured using a memory and a processor including hardware such as a CPU. The control unit 46 reads out a program stored in the storage unit 45 to a work area of ​​the memory and executes it, and controls each structural unit and the like by executing the program by the processor.

[0312] In addition, the server 90 may be configured as follows Fig.35 As shown in Fig.35 As shown, the server 90 mainly includes a communication unit 91 , a storage unit 95 and a control unit 96 .

[0313] Under the control of the control unit 96, the communication unit 91 communicates with the hearing aid 2 and the information processing terminal 40 via the Internet 484. The communication unit 91 can be configured using, for example, a communication module. The storage unit 95 stores various information related to the hearing aid 2. In addition, for example, the storage unit 95 stores various programs 961 executed by the server 90. The storage unit 95 can be configured using a recording medium such as a RAM, a ROM, a flash memory, or a memory card.

[0314] The control unit 96 controls the units constituting the server 90. The control unit 96 can be configured using, for example, a memory and a processor including hardware such as a CPU. The control unit 96 reads out a program stored in the storage unit 95 to a work area of ​​the memory and executes the program, and controls components and the like by executing the program through the processor.

[0315] It should be noted that in the embodiments of the present disclosure, the functional configurations of the hearing aid system 1 and the devices included in the hearing aid system 1 are not limited to Figure 32 to Figure 35 in the form shown.

[0316] <<8. Examples of data use>>

[0317] The data obtained relating to the use of the hearing aid device can be used in various ways. Fig.36 An example is described.

[0318] Fig.36 is a diagram showing an example of data utilization; in an exemplary system, there are an edge region 1000, a cloud region 2000, and an operator region 3000. As elements in the edge region 1000, a sound device 1100, a peripheral device 1200, and a vehicle 1300 are exemplified. As an element in the cloud region 2000, a server device 2100 is exemplified. As elements in the operator region 3000, an operator 3100 and a server device 3200 are exemplified.

[0319] The sound emitting device 1100 in the edge area 1000 is used by being worn by the user or arranged near the user to emit sound to the user. Specific examples of the sound emitting device 1100 include earphone speakers, headphones (earphone speakers), and hearing aids. More specifically, the sound emitting device 1100 may be Fig.16 The earphone speaker 115 or Fig.32 Hearing aids in 2.

[0320] The peripheral device 1200 and the vehicle 1300 in the edge area 1000 are devices used together with the sound emitting device 1100, and transmit signals such as content viewing sound and voice sound to the sound emitting device 1100. The sound emitting device 1100 outputs sound corresponding to the signal from the peripheral device 1200 or the vehicle 1300 to the user. A specific example of the peripheral device 1200 is a smartphone or the like.

[0321] Within edge region 1000, various data regarding the utilization of sound emitting device 1100 may be obtained. For illustration, reference is also made to Fig.37 .

[0322] Fig.37 is a diagram showing an example of data. Examples of data that can be acquired in edge region 1000 include device data, usage history data, personalized data, biometric data, emotional data, application data, fitting data, and preference data. Note that data can be understood as meaning information and can be read appropriately as long as there is no contradiction. Various well-known methods can be used to acquire exemplary data.

[0323] The device data is data about the sound-emitting device 1100 and includes, for example, type data of the sound-emitting device 1100, specifically, data for specifying whether the sound-emitting device 1100 is an earphone, a headset, TWS (True Wireless Stereo), a hearing aid (CIC (Completely In-Ear), ITE (In-Ear), RIC (Receiver In-Ear), etc.), etc.

[0324] The usage history data is the usage history data of the sound-emitting device 1100, and includes, for example, data such as music exposure dose, continuous use time of the hearing aid, and content viewing history (viewing time, etc.). In addition, the usage history data may also include the use time, number of uses, etc. of functions such as the sending of speech markers in the above-mentioned embodiment. The usage history data can be used for safe listening, conversion from TWS to hearing aids, replacement notification of wax guards (anti-clogging lumen intrusion filters), etc.

[0325] The personalized data is data about the user of the sound generating device 1100 and includes, for example, the head-related transfer function (HRTF), air conduction hearing level, and earwax type of the individual user. Further, the personalized data may also include hearing data.

[0326] The biological data is biological data of the user of the sound emission device 1100, and includes data such as sweating, blood pressure, blood flow, heart rate, pulse, body temperature, electroencephalogram, respiration, and myoelectric potential.

[0327] The emotion data is data indicating the emotion of the user of the sound emitting device 1100 , and includes, for example, data indicating comfort, discomfort, and the like.

[0328] The application data is data used in various applications, for example, and includes, for example, user attribute information data, such as the location of the user of the sound-emitting device 1100 (or the location of the sound-emitting device 1100) and the user's schedule, age and gender, and data such as weather, atmospheric pressure and temperature. For example, the location data can be used to search for a missing sound-emitting device 1100.

[0329] For example, the fitting data may include adjustment parameters of the hearing aid 2 or the earphone speaker 115 used by the user and the hearing aid gain for each frequency band set based on the user's audiometry results (audiogram).

[0330] The preference data is data related to the user's preference, and includes data such as preference of music to be listened to during driving.

[0331] Note that data of the communication state, data of the charging state, etc. of the sound emitting device 1100 may also be acquired. Part of the processing in the edge area 1000 may be performed by the cloud area 2000 according to the frequency band, communication state, charging state, etc. Since the processing is shared, the processing load in the edge area 1000 is reduced.

[0332] Return to reference Fig.36For example, the data as described above is acquired in the edge area 1000 and transmitted from the sound emitting device 1100, the peripheral device 1200, or the vehicle 1300 to the server device 2100 in the cloud area 2000. The server device 2100 stores (eg, saves or accumulates) the received data.

[0333] The operator 3100 in the operator area 3000 acquires data from the server device 2100 in the cloud area 2000 using the server device 3200. The data can be used by the operator 3100.

[0334] There may be various operators 3100. Specific examples of operators 3100 include hearing aid stores, hearing aid manufacturers, content production companies, and distribution operators that provide music streaming services, etc. These operators are referred to and shown as operators 3100-A, operators 3100-B, and operators 3100-C to be distinguishable. The server devices 3200 corresponding to the operators are referred to and shown as server devices 3200-A, server devices 3200-B, and server devices 3200-C. Different data is provided to such different operators 3100 and the utilization of data is promoted. The data provision to the operator 3100 may be data provision through subscription, recall, etc.

[0335] It is also possible to provide data from the cloud area 2000 to the edge area 1000. For example, when machine learning is required to implement processing in the edge area 1000, data for feedback, correction (correction), etc. of learning data are prepared in the cloud area 2000 by an administrator of the server device 2100 or the like. The prepared data is sent from the server device 2100 to the sound emitting device 1100, the peripheral device 1200, or the vehicle 1300 of the edge area 1000.

[0336] When a specific condition is satisfied in the edge area 1000, some incentives (such as privileges of advanced services) may be provided to the user. An example of a condition is a condition that at least a portion of the sound emitting device 1100, the peripheral device 1200, and the vehicle 1300 are devices provided by the same operator. If the incentive is an electronically available incentive (electronic coupon, etc.), the incentive may be transmitted from the server device 2100 to the sound emitting device 1100, the peripheral device 1200, or the vehicle 1300.

[0337] <<9. Example of collaboration with other devices>>

[0338] In the edge area 1000 , for example, a sound emitting device 1100 and other devices can cooperate using a peripheral device 1200 (eg, a smartphone) as a hub. Fig.38 An example is described.

[0339] Fig.38 1 is a diagram showing an example of cooperation with other devices. The edge area 1000, the cloud area 2000, and the operator area 3000 are connected through the network 4000 and the network 5000. A smartphone is illustrated as a peripheral device 1200 in the edge area 1000, and other devices 1400 are also illustrated as elements in the edge area 1000. Note that the vehicle 1300 ( Fig.36 ) icon.

[0340] The peripheral device 1200 can communicate with each sound-emitting device 1100 and the other device 1400. The communication method is not particularly limited, but for example, the Bluetooth LDAC, Bluetooth LE audio, etc. described above can be used. The communication between the peripheral device 1200 and the other device 1400 may be multicast communication. An example of multicast communication is Auracast (registered trademark) and the like.

[0341] The other device 1400 is used in cooperation with the sound-emitting device 1100 via the peripheral device 1200. Specific examples of the other device 1400 include a television (hereinafter referred to as a TV), a personal computer (PC), an HMD (head mounted display), a robot, a smart speaker, and a game device.

[0342] Even in the case where the sound-generating device 1100, the peripheral device 1200, and the other devices 1400 satisfy certain conditions (for example, conditions at least part of which are provided by the same operator), motivation may be provided to the user.

[0343] The sound-emitting device 1100 and other devices 1400 are able to collaborate using the peripheral device 1200 as a hub. Collaboration can be performed using various data stored in the server device 2100 in the cloud area 2000. For example, information such as adaptation data, viewing time, and the user's hearing is shared between the sound-emitting device 1100 and other devices 1400, thereby collaboratively performing volume adjustment of the devices and the like. When wearing a hearing aid 2 (HA) or a sound collector (PSAP: Personal Sound Amplification Product), the settings of the hearing aid 2 or PSAP can be automatically performed on a TV, PC, etc. For example, when a user using the hearing aid 2 uses other devices such as a TV or PC, a process of automatically changing the settings of the other devices can be performed so that the regular settings of a normal listener are changed to settings suitable for the user using the hearing aid. Note that whether the user is using the hearing aid 2 can be detected by automatically sending information indicating that the user has worn the hearing aid 2 (e.g., wearing detection information) to a device such as a TV or PC at the pairing destination of the hearing aid 2 when the user wears the hearing aid 2, or can be detected while being triggered by the user using the hearing aid approaching another device such as a TV or PC set as a target. It can be determined that the user is a hearing aid user by imaging the face of the user using a camera or the like provided in another device such as a TV or PC, or by a method other than the above method. For example, the hearing aid 2 (i.e., the sound-generating device 1100) and the other device 1400 that cooperate with each other can be used as headphones. In addition, when the other device 1400 includes a microphone that collects ambient sound, it is also possible to make the headphones as the sound-generating device 1100 function similarly to the hearing aid 2. In this case, the function of the hearing aid can be used in the same style (appearance, etc.) as listening to music. Headphones or earphones and hearing aids have many technically overlapping parts. It is assumed that the barrier between headphones or earphones and hearing aids disappears in the future, and one device has the functions of both headphones and hearing aids. When hearing is normal, that is, for normal listeners, by using the hearing aid as a normal earphone or headphone, you can enjoy the content viewing experience. When hearing is reduced due to aging, etc., the hearing aid can be used as a hearing aid by turning on the hearing aid function. Since the device as a headphone can be directly used as a hearing aid, continuous and long-term use by users can also be expected from the perspective of appearance and design.

[0344] Data of the user's listening history can be shared. Long-term listening may be a risk of future hearing loss. Notifications to the user, etc. can be made so that the listening time does not become too long. For example, when the viewing time exceeds a predetermined threshold, such notifications (safe listening) are performed. Notifications can be performed by any device in edge area 1000.

[0345] At least part of the devices used in the edge area 1000 may be provided by different operators. Information about the device settings of the operator and the like may be transmitted from the server device 3200 in the operator area 3000 to the server device 2100 in the cloud area 2000 and stored in the server device 2100. By using such information, devices provided by different operators can also cooperate with each other.

[0346] <<10. Examples of using transitions>>

[0347] The use of the sound generating device 1100 can be transformed according to various situations including the above-mentioned user's adaptation data, viewing time and hearing. Fig.39 An example is described.

[0348] Fig.39 is a diagram showing an example of use transition; when the user is a normal listener, for example, when the user is a child and for a period of time after the user becomes an adult, the sound emitting device 1100 is used as headphones or earphones (earphones / TWS). In addition to the above-mentioned safe listening, the adjustment and processing of the equalizer corresponding to the user's behavioral characteristics and the current position and external environment are performed (for example, for the scene where the user is in a restaurant and the scene where the user is riding in a vehicle, the noise cancellation mode is switched to the optimal noise cancellation mode respectively) or the collection of viewing music logs is performed, etc. Communication between devices using Auracast is also used.

[0349] When the user's hearing deteriorates, the hearing aid function of the sound-emitting device 1100 begins to be utilized. For example, when the user is a person with mild or moderate hearing loss, the sound-emitting device 1100 is used as an OTC hearing aid. When the user is a person with severe hearing loss, the sound-emitting device 1100 is used as a hearing aid. Note that OTC hearing aids are hearing aids sold in stores without the intervention of professionals, and are easily not purchased through hearing tests or professionals such as hearing professionals. Operations dedicated to hearing aids, such as adaptation, can be performed by the user himself. While the sound-emitting device 1100 is used as an OCT hearing aid or a hearing aid, audiometry is performed or the hearing aid function is turned on. For example, functions such as the transmission of speech marks in the above-described embodiment can also be used. Various information about hearing (hearing big data) is collected, adaptation, sound environment adaptation, remote support, etc. are performed, and transcription is further performed.

[0350] <<11.Supplement>>

[0351] It is to be noted that the embodiments of the present disclosure explained above may include, for example, an information processing method executed by the above-mentioned information processing device or information processing system, a program for causing the information processing device (computer) to run, and a non-transitory tangible medium recording the program. The program may be distributed via a communication line (including wireless communication) such as the Internet.

[0352] The steps in the information processing method in the embodiment of the present disclosure described above may not always be processed in the order described. For example, the steps may be processed with an appropriate change of order. The steps may be processed partially in parallel or individually, rather than in a time series. In addition, the processing of the steps may not always be processed according to the described method, and may be processed by another functional unit according to, for example, another method.

[0353] In the various processes described in the above-described embodiments, all or part of the processes described as being automatically performed may be performed manually, or all or part of the processes described as being manually performed may be performed automatically by a known method. In addition, unless otherwise specified, the processing procedures, specific names, and information including various data and parameters explained in the document and shown in the drawings may be optionally changed. For example, the various information shown in the drawings is not limited to the information shown.

[0354] The illustrated components of the device are conceptual in function and do not always need to be physically configured as illustrated in the figure. That is, the specific form of distribution and integration of the device is not limited to the illustrated form, and all or part of it can be configured by functionally or physically distributing and integrating into any unit according to various loads, usage conditions, etc.

[0355] The preferred embodiments of the present invention are described in detail above with reference to the accompanying drawings. However, the technical scope of the present disclosure is not limited to such examples. Obviously, a technician with ordinary knowledge in the technical field of the present disclosure can obtain various changes or corrections within the scope of the technical ideas described in the claims. It should be understood that these changes and corrections naturally belong to the technical scope of the present disclosure.

[0356] The effects described in this specification are merely illustrative or illustrative, and are not restrictive. That is, the technology according to the present disclosure can achieve other effects that are obvious to those skilled in the art from the description of this specification together with or instead of the effects described above.

[0357] It should be noted that the present technology can also adopt the following configurations.

[0358] (1) An information processing device comprising:

[0359] A prediction unit predicts a degree of conductive hearing loss based on a test result of a hearing test using air-conducted sound, the hearing test being a first hearing test and a second hearing test including test contents different from each other.

[0360] (2) The information processing device according to (1), wherein:

[0361] The test results of the first hearing test include air conduction hearing thresholds, and

[0362] The test results of the second hearing test include test results regarding the inner ear and / or the posterior labyrinthine system.

[0363] (3) The information processing device according to (1) or (2), wherein the prediction unit predicts the degree of conductive hearing loss using a statistical method.

[0364] (4) The information processing device according to (1) or (2), wherein the prediction unit predicts the degree of conductive hearing loss using a learning model.

[0365] (5) The information processing device according to any one of (1) to (4), wherein the first hearing test is an air conduction hearing test and / or a self-recording audiometry by intermittent sound.

[0366] (6) The information processing device according to any one of (1) to (5), wherein:

[0367] Second hearing test

[0368] Includes at least one test selected from the group consisting of: self-recording audiometry with continuous sound, SISI test, ABLB test, DL test, TD test, speech recognition threshold test, maximum speech intelligibility test, distorted speech audiometry, binaural separation function test and direction perception test.

[0369] (7) The information processing device according to any one of (1) to (4), wherein:

[0370] The first hearing test was a self-recording audiometry with intermittent sounds, and

[0371] The second auditory test was self-recording audiometry with continuous sound.

[0372] (8) The information processing device according to any one of (1) to (5), wherein

[0373] The prediction unit predicts the degree of conductive hearing loss based on the attribute information of the object.

[0374] (9) The information processing device according to any one of (1) to (8), further comprising:

[0375] A sound source generating unit generates air-conducted sound used in the first hearing test and the second hearing test.

[0376] (10) The information processing device according to any one of (1) to (9), further comprising:

[0377] The correction unit acquires output characteristic information of the sound output device and corrects the generated air-conducted sound based on the acquired output characteristic information, and the sound output device outputs the generated air-conducted sound.

[0378] (11) The information processing device according to (10), wherein the correction unit acquires the output feature information based on an image of the sound output device.

[0379] (12) The information processing device according to any one of (1) to (11), further including: an output unit that outputs a test result of the first hearing test, a test result of the second hearing test, and a predicted degree of conductive hearing loss.

[0380] (13) The information processing device according to any one of (1) to (12), further including: an output unit that compares the predicted degree of conductive hearing loss with a predetermined threshold value and outputs information for prompting the subject to consult a medical institution based on the comparison result.

[0381] (14) The information processing device according to any one of (1) to (12), further including: an output unit that compares the predicted degree of conductive hearing loss with a predetermined threshold value and outputs information for purchasing a hearing aid to the subject based on the comparison result.

[0382] (15) The information processing device according to any one of (1) to (14), further including: a parameter determination unit that determines a setting parameter of the hearing aid based on the predicted degree of conductive hearing loss.

[0383] (16) The information processing device according to (15), wherein the setting parameter is a parameter for performing gain setting control and / or noise suppression setting control on the hearing aid.

[0384] (17) The information processing device according to any one of (1) to (14), further including: a parameter determination unit that determines a setting parameter of an acoustic device outside the information processing device based on the predicted degree of conductive hearing loss.

[0385] (18) The information processing device according to (17), wherein the setting parameter is a parameter for delaying a voice output from the acoustic device or controlling a volume of a voice output from the acoustic device.

[0386] (19) An information processing method includes: predicting, by an information processing device, a degree of conductive hearing loss based on a test result of a hearing test using air-conducted sound, the hearing test being a first hearing test and a second hearing test including test contents different from each other.

[0387] (20) A program for causing a computer to execute the following function: predicting the degree of conductive hearing loss based on a test result of a hearing test using air-conducted sound, the hearing test being a first hearing test and a second hearing test including test contents different from each other.

[0388] (21) A learning model generating method comprising inputting a test result of a hearing test using air-conducted sound as input data into a learning device, the hearing test being a first hearing test and a second hearing test including test contents different from each other, and inputting a degree of conductive hearing loss corresponding to the test results of the first hearing test and the second hearing test as teacher data, wherein:

[0389] The learning device generates a learning model for predicting the degree of conductive hearing loss based on the test results of the first hearing test and the second hearing test.

[0390] Reference Numbers List

[0391] 1Hearing aid system

[0392] 2,116 hearing aids

[0393] 3. Charger

[0394] 20b, 20f sound collection unit

[0395] 21 Signal Processing Unit

[0396] 22 Output Units

[0397] 25, 32 batteries

[0398] 26,331 connection unit

[0399] 27, 30, 34, 42, 91 communication units

[0400] 28, 35, 45, 95 storage units

[0401] 29, 36, 46, 96 control units

[0402] 31, 44 display units

[0403] 33 Accommodation Units

[0404] 40,117 Information Processing Terminal

[0405] 41 Input unit

[0406] 43 Output Unit

[0407] 90 Servers

[0408] 102,901' object

[0409] 115 earphone speaker

[0410] 119,484 Internet

[0411] 120 External devices

[0412] 121 First Path

[0413] 122 Second Path

[0414] 161 The first group of auditory test sound source generation units

[0415] 162 The second group of auditory test sound source generation unit

[0416] 163 Test control unit

[0417] 164 Conductive Hearing Loss Degree Prediction Unit

[0418] 165 Test information storage unit

[0419] 166 Additional information storage unit

[0420] 171 Hearing Test Sound Output Tool

[0421] 172 Information Output Tools

[0422] 173 Information Input Tool

[0423] 174 Communication Tools

[0424] 189 Level / frequency characteristic correction information storage unit

[0425] 190 Level / Frequency Characteristics Correction Unit

[0426] 197 Hearing aid parameter determination unit

[0427] 198 Hearing aid parameter storage unit

[0428] 201b, 201f microphone

[0429] 202b, 202f A / D conversion unit

[0430] 221D / A conversion unit

[0431] 222 Receiver

[0432] 281,351 procedures

[0433] 282 Data

[0434] 291 Hearing aid sales company

[0435] 292 Hearing testing service providers

[0436] 299 Database

[0437] 333, 334, 335, 336, 337, 338, 541, 542, 543, 544, 545, 546 corresponding range

[0438] 595 Audio Video Control Unit

[0439] 596 Hearing Information Storage Unit

[0440] 597 Audio Processing Unit

[0441] 598 Video delay adjustment unit

[0442] 751 Part 1

[0443] 752 Part 2

[0444] 753 Part 3

[0445] 754 Part 4

[0446] 755 Part 5

[0447] 756 Part VI

[0448] 757 Part 7

[0449] 758 Part Eight

[0450] 759 Part 9

[0451] 781 Hearing test information for the first group

[0452] 782 Second Group Hearing Test Information

[0453] 783 Additional information

[0454] 784 Information on the degree of conductive hearing loss

[0455] 903 Professionals

[0456] 911 Air Conduction Headphones

[0457] 912 Bone Conduction Headphones

[0458] 913 Audiometer

[0459] 914 Response button.

Claims

1. An information processing device, comprising: A prediction unit predicts a degree of conductive hearing loss based on a test result of a hearing test using air-conducted sound, the hearing test being a first hearing test and a second hearing test including test contents different from each other.

2. The information processing device according to claim 1, wherein: The test results of the first hearing test include air conduction hearing thresholds, and the test results of the second hearing test include test results regarding the inner ear and / or posterior labyrinthine system.

3. The information processing device according to claim 1, wherein: The prediction unit predicts the degree of the conductive hearing loss using a statistical method.

4. The information processing device according to claim 1, wherein: The prediction unit predicts the degree of the conductive hearing loss using a learning model.

5. The information processing device according to claim 1, wherein: The first hearing test is an air conduction hearing test and / or a self-recording audiometry with intermittent sounds.

6. The information processing device according to claim 1, wherein: The second auditory test Includes at least one test selected from the group consisting of: self-recording audiometry with continuous sound, SISI test, ABLB test, DL test, TD test, speech recognition threshold test, maximum speech intelligibility test, distorted speech audiometry, binaural separation function test and direction perception test.

7. The information processing device according to claim 1, wherein: The first hearing test is a self-recording audiometry performed with intermittent sounds, and the second hearing test is a self-recording audiometry performed with continuous sounds.

8. The information processing device according to claim 1, wherein: The prediction unit predicts the degree of the conductive hearing loss based on attribute information of the object.

9. The information processing device according to claim 1, further comprising: A sound source generating unit generates the air-conducted sound used in the first hearing test and the second hearing test.

10. The information processing device according to claim 1, further comprising: A correction unit acquires output characteristic information of a sound output device, and corrects the generated air-conducted sound based on the acquired output characteristic information, wherein the sound output device outputs the generated air-conducted sound.

11. The information processing device according to claim 10, wherein: The correction unit acquires the output feature information based on an image of the sound output device.

12. The information processing device according to claim 1, further comprising: An output unit outputs the test result of the first hearing test, the test result of the second hearing test, and the predicted degree of the conductive hearing loss.

13. The information processing device according to claim 1, further comprising: An output unit compares the predicted degree of the conductive hearing loss with a predetermined threshold value and outputs information for prompting the subject to consult a medical institution based on the comparison result.

14. The information processing device according to claim 1, further comprising: An output unit compares the predicted degree of the conductive hearing loss with a predetermined threshold value and outputs information for purchasing a hearing aid to the subject based on the comparison result.

15. The information processing device according to claim 1, further comprising: A parameter determination unit determines setting parameters of the hearing aid based on the predicted degree of the conductive hearing loss.

16. The information processing device according to claim 15, wherein: The setting parameters are parameters for performing gain setting control and / or noise suppression setting control on the hearing aid.

17. The information processing device according to claim 1, further comprising: A parameter determination unit determines setting parameters of an acoustic device external to the information processing device based on the predicted degree of the conductive hearing loss.

18. The information processing device according to claim 17, wherein: The setting parameter is a parameter for delaying the voice output from the acoustic device or controlling the volume of the voice output from the acoustic device.

19. An information processing method, comprising: The degree of conductive hearing loss is predicted by an information processing device based on a test result of a hearing test using air-conducted sound, the hearing test being a first hearing test and a second hearing test including test contents different from each other.

20. A program for causing a computer to execute the following function: predicting the degree of conductive hearing loss based on the test results of a hearing test using air-conducted sound, the hearing test being a first hearing test and a second hearing test including test contents different from each other.

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