EXHIBIT 2117
`EXHIBIT 2117
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`(19) United States
`(12) Patent Application Publication (10) Pub. No.: US 2009/0270698 A1
`
`
` Shioi et al. (43) Pub. Date: Oct. 29, 2009
`
`US 20090270698A1
`
`(54) BIOINFORMATION MEASUREMENT
`DEVICE
`Inventors:
`
`(76)
`
`Masahiko Shioi, Osaka (JP);
`Yoshiko Miyamoto, Osaka (JP);
`Shlnjl Uchlda, Osaka (JP)
`Correspondence Address:
`MCDERMOTT WILL & EMERY LLP
`600 13TH STREET, NW
`WASHINGTON, DC 20005-3096 (US)
`
`(21) Appl. No.:
`
`12/067,917
`
`(22) PCT Filed:
`
`Oct. 19, 2006
`
`(86) PCT No.:
`
`PCT/JP2006/320813
`
`§ 371 (c)(1)S
`(2), (4) Date:
`
`Mar. 24, 2008
`
`(30)
`
`Foreign Application Priority Data
`
`Oct. 21, 2005
`
`(JP) ................................. 2005-306902
`
`Publication Classification
`
`(51)
`
`Int. Cl.
`(200601)
`A613 5/1455
`(52) US. Cl. ........................................................ 600/310
`(57)
`ABSTRACT
`A bioinformation measurement device that enables further
`accurate bioinformation measurement
`is provided. The
`device includes an insertion portion 104 to be inserted in an
`ear cavity 200; a first light inlet 105 and a second light inlet
`106 provided at the insertion portion 104, for introducing the
`infrared light irradiated from the ear cavity 200 to the inser-
`tion portion 104; an optical guide path provided in the inser-
`tion portion 104 for guiding the first infrared light introduced
`from the first light inlet 105 and the second infrared light
`introduced from the second light inlet 106; a dispersive ele-
`ment for dispersing the first infrared light and the second
`infrared light guided by the optical guide path; an infrared ray
`detector 108 for detecting the first infrared light and the
`second infrared light dispersed by the dispersive element; and
`a computing unit for computing bioinformation based on the
`intensities of the first infrared light and the second infrared
`light detected by the infrared ray detector 108.
`
`LQ__
`
`\\‘
`
`106
`
`119
`
`105
`
` 1 05
`
`114
`
`1 o 1
`
`1 03
`
`1 02
`
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`Patent Application Publication
`
`Oct. 29, 2009 Sheet 1 0f 8
`
`US 2009/0270698 A1
`
`FIG.
`
`1
`
`O)
`,_
`,_
`
`105
`
`105
`
`106
`
` O
`
`101
`
`103
`
`114-
`
`102
`
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`Patent Application Publication
`
`Oct. 29, 2009 Sheet 2 0f 8
`
`US 2009/0270698 A1
`
` .2:an0222 hwy—02.50
`$3.26;
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`
`
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`
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`Patent Application Publication
`
`Oct. 29, 2009 Sheet 3 0f 8
`
`US 2009/0270698 A1
`
`FIG. 3
`
`ID
`0Y.
`
`104
`
`414 —————_———-———————_.__._-.
`
`412
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`Patent Application Publication
`
`Oct. 29, 2009 Sheet 4 0f 8
`
`US 2009/0270698 A1
`
`FIG. 4
`
`6
`
`121
`
`123
`
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`Patent Application Publication
`
`Oct. 29, 2009 Sheet 5 of 8
`
`US 2009/0270698 A1
`
`FIG.
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`

`Patent Application Publication
`
`Oct. 29, 2009 Sheet 6 0f 8
`
`US 2009/0270698 A1
`
`LD
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`
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`Patent Application Publication
`
`Oct. 29, 2009 Sheet 7 of 8
`
`US 2009/0270698 A1
`
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`

`

`Patent Application Publication
`
`Oct. 29, 2009 Sheet 8 0f 8
`
`US 2009/0270698 A1
`
`L0
`
`0‘
`
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`
`FIG. 8
`
`119
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`104
`
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`US 2009/0270698 A1
`
`Oct. 29, 2009
`
`BIOINFORMATION MEASUREMENT
`DEVICE
`
`TECHNICAL FIELD
`
`an infrared ray detector for detecting the first infra-
`[0010]
`red light and the second infrared light dispersed by the dis-
`persive element.
`
`EFFECT OF THE INVENTION
`
`[0001] The present invention relates to a bioinformation
`measurement device which noninvasively measures bioinfor-
`mation by using infrared irradiated light from the ear cavity.
`
`[001 1] Based on the bioinformation measurement device of
`the present invention, a further accurate bioinformation mea-
`surement can be carried out by considering the effects of the
`external ear canal on the measurement.
`
`BACKGROUND ART
`
`BRIEF DESCRIPTION OF THE DRAWINGS
`
`[0002] As a conventional bioinformation measurement
`device, there has been proposed a device that noninvasively
`measures a living subject, particularly a blood-sugar level by
`using infrared irradiated light from the eardrum (for example,
`patent document 1). For example, patent document 1 dis-
`closes a device that determines a blood-sugar level with an
`infrared ray detector by noninvasively measuring a radiation
`naturally generated from eardrums as heat in the infrared
`range of the spectrum, and having a spectrum that is distinc-
`tive of human organs.
`
`Patent Document 1 Japanese Unexamined Patent Application
`No.
`
`DISCLOSURE OF THE INVENTION
`
`Problem to be Solved by the Invention
`
`[0003] According to Planck’s law, however, any object hav-
`ing a temperature inevitably emits an infrared radiation due to
`the heat. In the case of the above conventional measurement
`device, not only the eardrum, but the external ear canal is also
`a radiant of infrared light. Thus, irradiated light from the
`eardrum and irradiated light from the external ear canal enter
`the infrared ray detector. The irradiated light from the external
`ear canal is considered a noise, since the irradiated light from
`the external ear canal contains less information on blood
`compared with the irradiated light from the eardrum, because
`the skin of the external ear canal is thick compared with that
`of the eardrum and the blood supply is at a relatively deeper
`position. Thus, the irradiated light from the external ear canal
`has been a factor of inaccurate measurement.
`
`[0004] Considering the above conventional problem, the
`present invention aims to provide a bioinformation measure-
`ment device which can carry out a further accurate bioinfor-
`mation measurement.
`
`Means for Solving the Problem
`
`To solve the above conventional problem, a bioin-
`[0005]
`formation measurement device of the present invention for
`measuring bioinformation based on an intensity of infrared
`light includes:
`[0006]
`an insertion portion to be inserted into an ear cavity;
`[0007]
`a first light inlet and a second light inlet provided at
`the insertion portion, for introducing infrared light irradiated
`from the ear cavity into the insertion portion;
`[0008]
`an optical guide path provided in the insertion por-
`tion, for guiding first infrared light introduced from the first
`light inlet and second infrared light introduced from the sec-
`ond light inlet;
`[0009]
`a dispersive element for dispersing the first infrared
`light and the second infrared light guided by the optical guide
`path; and
`
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`FIG. 1 A perspective illustration showing an exter-
`[0012]
`nal view of a bioinformation measurement device in one
`embodiment of the present invention.
`[0013]
`FIG. 2 A diagram showing a configuration of the
`bioinformation measurement device.
`[0014]
`FIG. 3 A perspective illustration showing an inser-
`tion portion and a shutter of the bioinformation measurement
`device.
`FIG. 4 A perspective illustration showing an optical
`[0015]
`filter wheel of the bioinformation measurement device.
`[0016]
`FIG. 5 An illustration showing a configuration of an
`example of a first variation of the bioinformation measure-
`ment device.
`[0017]
`FIG. 6 A perspective illustration showing an inser-
`tion portion of the bioinformation measurement device in
`another embodiment of the present invention.
`[0018]
`FIG. 7 An illustration of a configuration of the bio-
`information measurement device.
`[0019]
`FIG. 8 A perspective illustration showing an
`example of a variation of the insertion portion of the bioin-
`formation measurement device.
`
`BEST MODE FOR CARRYING OUT THE
`INVENTION
`
`[0020] A bioinformation measurement device of the
`present invention for measuring bioinformation based on an
`intensity of infrared light includes:
`[0021]
`an insertion portion to be inserted into an ear cavity;
`[0022]
`a first light inlet and a second light inlet provided at
`the insertion portion, for introducing infrared light irradiated
`from the ear cavity into the insertion portion;
`[0023]
`an optical guide path provided in the insertion por-
`tion, for guiding first infrared light introduced from the first
`light inlet and second infrared light introduced from the sec-
`ond light inlet;
`[0024]
`a dispersive element for dispersing the first infrared
`light and the second infrared light guided by the optical guide
`path; and
`an infrared ray detector for detecting the first infra-
`[0025]
`red light and the second infrared light dispersed by the dis-
`persive element. Further preferably, a computing unit for
`computing bioinformation based on the intensities of the first
`infrared light and the second infrared light detected by the
`infrared ray detector is further included.
`[0026]
`In the present invention, for the optical guide path,
`any optical guide path may be used as long as it can introduce
`infrared light: for example, a hollow pipe, and optical fiber
`that transmits the infrared light. When the hollow pipe is to be
`used, a gold layer is preferably provided at the inner surface of
`the hollow pipe. The gold layer may be formed by gold-
`plating, or by vapor depositing gold at the inner surface ofthe
`hollow pipe.
`[0027]
`For the dispersive element, any dispersive element
`may be used as long as it can disperse infrared light by
`wavelength: for example, an optical filter, a spectroscopic
`
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`

`US 2009/0270698 A1
`
`Oct. 29, 2009
`
`prism, a Michelson interferometer, and a diffraction grating,
`which transmit infrared light in a specific wavelength range.
`[0028]
`For the infrared ray detector, any infrared ray detec-
`tor may be used as long as it can detect the light with a
`wavelength in the infrared range: for example, a pyroelectric
`sensor, a thermopile, a bolometer, a HngTe (MCT) detector,
`and a Golay cell.
`[0029] A plurality of the infrared ray detectors may be
`provided.
`[0030]
`For the computing unit, for example, a microcom-
`puter such as CPU (Central Processing Unit) may be used.
`[0031] The bioinformation measurement device of the
`present invention may include a plurality of optical guide
`paths, including a first optical guide path for guiding the first
`infrared light introduced from the first light inlet, and a sec-
`ond optical guide path for guiding the second infrared light
`introduced from the second light inlet.
`[0032] The first infrared light and the second infrared light
`may also be guided by one optical guide path.
`[0033]
`In the bioinformation measurement device of the
`present invention, the second light inlet is preferably config-
`ured so that the infrared light irradiated from the eardrum is
`not introduced.
`
`[0034] With such a configuration, since the infrared light
`irradiated from the eardrum is not introduced from the second
`light inlet, the second infrared light introduced from the sec-
`ond light inlet corresponds only to the infrared light irradiated
`from the external ear canal. Thus, by using the intensity ofthe
`first infrared light including the infrared light irradiated from
`the eardrum and the infrared light irradiated from the external
`ear canal, and the intensity of the second infrared light, and
`correcting the effects of the infrared light irradiated from the
`external ear canal, a further accurate bioinformation measure-
`ment based on the infrared light irradiated from the eardrum
`can be carried out.
`
`In the bioinformation measurement device of the
`[0035]
`present invention, the insertion portion may include an end
`portion that is directed toward the eardrum when inserted into
`the ear cavity; and a side face. The first light inlet may be
`provided at the end portion of the insertion portion. Further,
`the second light inlet is preferably provided at the side face of
`the insertion portion.
`[0036] The bioinformation measurement device of the
`present invention preferably further includes a shielding por-
`tion provided at the insertion portion, for shielding the second
`light inlet from the infrared light irradiated from the eardrum.
`[0037] With such a configuration, the infrared light irradi-
`ated from the eardrum is not introduced from the second light
`inlet, and therefore the second infrared light introduced from
`the second light inlet corresponds only to the infrared light
`irradiated from the external ear canal. Thus, by using the
`intensity of the first infrared light including the infrared light
`irradiated from the eardrum and the infrared light irradiated
`from the external ear canal, and the intensity of the second
`infrared light, and correcting the effects of the infrared light
`irradiated from the external ear canal on the measurement, a
`further accurate bioinformation measurement based on the
`infrared light irradiated from the eardrum can be carried out.
`[0038] The surface of the shielding portion is preferably
`formed of gold, silver, copper, brass, aluminum, platinum, or
`iron; and the surface of the shielding portion is preferably
`glossy.
`Preferably, the shielding portion is provided remov-
`[0039]
`ably at the insertion portion.
`[0040] The bioinformation measurement device of the
`present invention may further include an optical path control
`unit for controlling the optical path ofthe infrared light reach-
`
`ing the infrared ray detector. The optical path control unit is
`preferably able to control the optical path so that the infrared
`light reaching the infrared ray detector can be switched
`between the first infrared light and the second infrared light,
`and the first infrared light only.
`[0041]
`For the optical path control unit, a shutter, and an
`aperture may be mentioned.
`[0042]
`In the bioinformation measurement device of the
`present invention, the computing unit may further include a
`warning output unit for making comparison between the
`threshold and the intensity difference between the first infra-
`red light intensity and the second infrared light intensity, and
`outputting a warning when the intensity difference is larger
`than the threshold. With such a configuration, a user can be
`notified of an inappropriate position of the bioinformation
`measurement device.
`
`For the warning output unit, a display for showing
`[0043]
`the warning, a speaker for outputting a warning with a sound,
`and a buzzer for producing a warning sound may be men-
`tioned.
`
`[0044] The bioinformation measurement device of the
`present invention further may include a memory unit for
`storing correlational data showing the correlation between
`the output signal of the infrared ray detector and the bioin-
`formation; a display unit for displaying bioinformation con-
`verted by the computing unit; and a power source for supply-
`ing electrical power for the bioinformation measurement
`device to be in operation.
`[0045] The computing unit may convert the output signal of
`the infrared ray detector to bioinformation, by reading the
`above correlational data from the memory unit and referring
`to it.
`
`[0046] The correlational data showing the correlation
`between the output signal of the infrared ray detector and
`bioinformation can be obtained, for example, by measuring
`the output signal ofthe infrared ray detector on a patient with
`known bioinformation (for example, a blood-sugar level),
`and analyzing the obtained correlation between the output
`signal of the infrared ray detector and the bioinformation.
`[0047]
`In the present invention, for the memory unit, for
`example, a memory such as RAM and ROM may be used.
`[0048]
`For the display unit, for example, a display of liquid
`crystal may be used.
`[0049]
`For the power source, for example, a battery may be
`used.
`
`For the bioinformation as the measurement target of
`[0050]
`the present invention, a glucose concentration (a blood-sugar
`level), a hemoglobin concentration, a cholesterol concentra-
`tion, a neutral fat concentration, and a protein concentration
`may be mentioned.
`[0051] By measuring the infrared light irradiated from a
`living subject, bioinformation, for example, a blood-sugar
`level can be measured. Radiant power W of the infrared
`irradiated light from the living subject is represented by the
`mathematical expression below.
`
`W = s
`
`A2
`A1
`
`a(/I)- W0(T, Mal/MW)
`
`W001, T) = thz
`AS
`{ [exp(hc//\kT) — l] }
`
`’1 w
`(
`
`2-
`/cm pm)
`
`[Mathematical Expression 1]
`
`[Mathematical Expression 2]
`
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`

`US 2009/0270698 A1
`
`Oct. 29, 2009
`
`[0076] The reflectivity is described next. Regarding reflec-
`tivity, an average ofthe reflectivities of all directions has to be
`calculated. However, for simplification, the reflectivity in
`normal incidence is considered. The reflectivity in normal
`incidence is expressed as the following, setting the refractive
`index of air as l:
`
`(”(A) — 1)2 + [(201)
`r(/I) _ (”(A) + 1)2 +k2(/1)
`
`[Mathematical Expression 8]
`
`In the expression, n0») shows the refractive index of
`[0077]
`living subject at wavelength A.
`[0078]
`From the above, the emissivity is expressed as:
`
`8(1) = 1 - r(/\) — [(1)
`
`[Mathematical Expression 9]
`
`_
`_
`
`(rm—1)2 +sz
`_W _
`
`4mm) d
`6Xp(— A
`
`J
`
`[0079] When the concentration of a component in a living
`subject changes, the refractive index and the extinction coef-
`ficient of the living subject change. The reflectivity is low,
`usually about 0.03 in the infrared range, and as can be seen
`from Mathematical Expression 8, it is not much dependent on
`the refractive index and the extinction coeflicient. Therefore,
`even the refractive index and the extinction coefficient change
`with changes in the concentration of a component in living
`subject, the changes in the reflectivity is small.
`[0080] On the other hand, the transmittance depends, as is
`clear from Mathematical Expression 7, heavily on the extinc-
`tion coeflicient. Therefore, when the extinction coeflicient of
`a living subject, i.e., the degree of light absorption by the
`living subject, changes by changes in the concentration of a
`component in a living subject, the transmittance changes.
`[0081] The above clarifies that the radiant power of infrared
`irradiated light from a living subject depends on the concen-
`tration of a component in the living subject. Therefore, a
`concentration of a component in a living subject can be deter-
`mined from the radiant power intensity of the infrared irradi-
`ated light from the living subject.
`[0082] Also, as is clear from Mathematical Expression 7,
`the transmittance is dependent on the thickness of a living
`subject. The smaller the thickness of the living subject, the
`larger the degree of the change in the transmittance relative to
`the change in the extinction coeflicient of the living subject,
`and therefore changes in the component concentration in a
`living subject can be easily detected. Since eardrums have a
`small thickness of about 60 to 100 um, it is suitable for a
`concentration measurement of a component in a living sub-
`ject using infrared irradiated light.
`[0083]
`In the following, embodiments ofthe present inven-
`tion are described by referring to the figures.
`
`Embodiment l
`
`FIG. 1 is a perspective illustration showing an exter-
`[0084]
`nal view of a bioinforrnation measurement device 100 of
`Embodiment l.
`
`[0085] The bioinformation measurement device 100
`includes a main body 102, and an insertion portion 104 pro-
`
`[0052] The respective symbols in the above expressions
`represent the following.
`[0053] W: Radiant Power of The Infrared Irradiated Light
`From Living Subject
`[0054]
`60»): Emissivity of Living Subject at Wavelength A
`[0055] WO(}»,T): Spectral Radiant Emittance of Blackbody
`at wavelength A, and temperature T
`[0056]
`h: Plank’s constant (h:6.625><10'34 (W-Sz))
`[0057]
`c: Light Velocity (c:2.998x1010(cm/s))
`[0058]
`A 1, A2: Wavelength (pm) of Infrared Irradiated Light
`from Living Subject
`[0059]
`T: Temperature (K) of Living Subject
`[0060]
`S: Detected Area (cmz)
`[0061]
`k: Boltzmann constant
`[0062] As is clear from Mathematical Expression 1, when
`detected area S is constant, radiant power W of the infrared
`irradiated light from a living subject depends on emissivity
`60») of the living subject at wavelength 2». Based on Kirch-
`hofl’s law of radiation, emissivity equals absorptivity at the
`same temperature and the same wavelength.
`ammo»)
`[Mathematical Expression 3]
`
`In Mathematical Expression 3, 0.0») represents the
`[0063]
`absorptivity of a living subject at wavelength A.
`the
`[0064] Therefore, upon considering the emissivity,
`absorptivity may be considered. Based on the law of conser-
`vation of energy, absorptivity, transmittance, and reflectivity
`satisfy the following relation.
`a(x)+r(x)+z(x):1
`
`[Mathematical Expression 4]
`
`[0065] The respective symbols in the above expression rep-
`resent the following.
`[0066]
`r0»): Reflectivity of Living Subject at wavelength A
`[0067]
`t0»): Transmittance of Living Subject at wavelength
`
`A [
`
`0068] Therefore, the emissivity can be expressed as, by
`using the transmittance and the reflectivity:
`6(k):a(}t):l—r(}t)—l(}t)
`[Mathematical Expression 5]
`
`[0069] The transmittance is expressed as the ratio of the
`amount ofincident light to the amount ofthe transmitted light
`that was transmitted through the measurement subject. The
`amount of incident light and the amount of the transmitted
`light upon being transmitted through the measurement sub-
`ject are shown with Lambert-Beer law.
`
`4mm)
`1,01) = 10(A)exp[— Td]
`
`[Mathematical Expression 6]
`
`[0070] The respective symbols in the above expression rep-
`resent the following.
`[0071]
`It: Amount of the Transmitted Light
`[0072]
`I0: Amount of Incident Light
`[0073]
`d: Thickness of Living Subject
`[0074]
`k0»): Extinction Coefficient of living subject at
`Wavelength A.
`The extinction coefficient of living subject is a coeflicient
`showing the light absorption by living subject.
`[0075] Therefore, the transmittance can be expressed as:
`
`
`47rk (/1)
`[(A) = exp(— A
`
`d]
`
`[Mathematical Expression 7]
`
`IPR2017—003 15
`
`CONDITIONAL MOTION TO AMEND
`
`VALENCELL, INC.
`EXHIBIT 2117 — PAGE 13
`
`IPR2017-00315
`CONDITIONAL MOTION TO AMEND
`
`VALENCELL, INC.
`EXHIBIT 2117 - PAGE 13
`
`

`

`US 2009/0270698 A1
`
`Oct. 29, 2009
`
`vided on the side face of the main body 102. The main body
`102 includes a display 114 for displaying the measurement
`results ofthe concentration of a component in a living subject,
`a power source switch 101 for ON/OFF of a power source of
`the bioinformation measurement device 100, and a measure-
`ment start switch 103 for starting the measurement. At the
`insertion portion, a first light inlet 105 for introducing infra-
`red light irradiated from an ear cavity into the bioinforrnation
`measurement device 100, and two second light inlets 106 are
`provided.
`[0086] The first light inlet 105 is provided at an end (end
`portion) of the insertion portion 104, and is directed toward
`the eardrum upon the insertion portion 1 04 is inserted into the
`ear cavity. The two second light inlets 106 are provided on the
`side faces of the insertion portion 104.
`[0087] Next, an internal structure of the main body of the
`bioinformation measurement device 100 is described by
`using FIG. 2, FIG. 3, and FIG. 4. FIG. 2 is a diagram showing
`a configuration of a bioinforrnation measurement device 100
`of Embodiment l ; FIG. 3 is a perspective illustration showing
`the insertion portion 104 and a shutter 109 ofthe bioinforma-
`tion measurement device 100 of Embodiment l ; and FIG. 4 is
`a perspective illustration of an optical filter wheel 107 of the
`bioinformation measurement device 100 of Embodiment 1.
`
`In FIG. 3, a chopper is omitted.
`[0088]
`Inside the main body of the bioinformation mea-
`surement device 100, a chopper 118, a shutter 109, an optical
`filter wheel 107, an infrared ray detector 108, a preliminary
`amplifier 130, a band-pass filter 132, a synchronous demodu-
`lator 134, a low-pass filter 136, an analog/digital converter
`(hereinafter abbreviated as A/D converter) 138, a microcom-
`puter 110, a memory 112, a display 114, a power source 116,
`a timer 156, and a buzzer 158 are included. In this arrange-
`ment, the microcomputer 110 corresponds to the computing
`unit of the present invention.
`[0089] The power source 116 supplies an alternating cur-
`rent (AC) or a direct current (DC) to the microcomputer 110.
`For the power source 116, batteries are preferably used.
`[0090] The chopper 118 has functions of chopping the light
`irradiated from the eardrum 202, i.e., the first infrared light
`introduced into the main body 102 through a first optical
`guide path 302 provided in the insertion portion 104 from the
`first light inlet 105 and the second infrared light introduced
`into the main body 102 through a second optical guide path
`304 provided in the insertion portion 104 from the second
`light inlet 106; and converting the first and the second infrared
`light into high-frequency infrared ray signals. The operation
`ofthe chopper 118 is controlled based on control signals from
`the microcomputer 110.
`[0091] The infrared light chopped by the chopper 118
`reaches the shutter 109.
`
`[0092] The shutter 109 has functions of controlling the
`optical path of the infrared light introduced into the main
`body 102. The shutter 109 includes, as shown in FIG. 3, a first
`shield plate 404 with a first aperture 402 corresponding to the
`optical guide path 302, a second shield plate 408 with two
`second apertures 406 corresponding to the second optical
`guide paths 304, a first motor 414 for driving the first shield
`plate 404 to slide along a first guide 410, and a second motor
`416 for driving the second shield plate 408 to slide along a
`second guide 412.
`[0093] By driving the second motor 416 and sliding the
`second shield plate 408 along with the second guide 412 from
`the position shown in FIG. 3 in the direction of arrow A, the
`
`first infrared light introduced by the first optical guide path
`302 is blocked by the second shield plate 408, and only the
`second infrared light introduced by the second optical guide
`paths 304 reaches the optical filter wheel 107 through the
`second apertures 406.
`[0094] On the other hand, by driving the first motor 414 and
`sliding the first shield plate 404 along with the first guide 410
`from the position shown in FIG. 3 in the direction of arrow A,
`the second infrared light introduced by the second optical
`guide paths 304 is blocked by the first shield plate 404, and
`only the first infrared light introduced by the first optical
`guide path 3 02 reaches the optical filter wheel 107 through the
`first aperture 402. With such an arrangement, the infrared
`light reaching the optical filter wheel 107 can be switched
`between the first infrared light and the second infrared light.
`The operation of the shutter 109 is controlled based on the
`control signal from the microcomputer 110. The shutter 109
`corresponds to the optical path control unit of the present
`invention.
`
`In the optical filter wheel 107, as shown in FIG. 4, a
`[0095]
`first optical filter 121, a second optical filter 122, and a third
`optical filter 123 are put in a ring 127. In an example shown in
`FIG. 4, a disk-like member is formed by putting the first
`optical filter 121, the second optical filter 122, and the third
`optical filter 123, all of which are fan-shaped, in the ring 127,
`and a shaft 125 is provided at the center of the disk-like
`member.
`
`[0096] By rotating this shaft 125 following the arrow in
`FIG. 4, the optical filter for the infrared light chopped by the
`chopper 118 to passes through can be switched between the
`first optical filter 121, the second optical filter 122, and the
`third optical filter 123. The rotation of the shaft 125 is con-
`trolled by the control signal from the microcomputer 1 1 0. The
`optical filter wheel 107 corresponds to the dispersive element
`of the present invention.
`[0097] The optical filter may be made by any known meth-
`ods without particular limitation. For example, vapor depo-
`sition methods may be used. The optical filter may be made by
`the vacuum deposition method, making a layer offor example
`ZnS, MgFZ, and PbTe on a base plate using Si or Ge.
`[0098] The infrared light transmitted through the first opti-
`cal filter 121, the second optical filter 122, and the third
`optical filter 123 reaches the infrared ray detector 108 includ-
`ing a detection region 126. The infrared light that reached the
`infrared ray detector 108 enters the detection region 126, and
`is converted to an electric signal corresponding to the inten-
`sity of the infrared light entered.
`[0099] The rotation of the shaft 125 of the optical filter
`wheel 107 is preferably synchronized with the operation of
`the chopper 118, and controlled so that the shaft 125 is rotated
`to 120 degrees while the chopper 118 is closed. With such an
`arrangement, when the chopper 118 is opened next time, the
`optical filter for the infrared light chopped by the chopper 1 18
`to pass through can be switched to the next optical filter.
`[0100] Also, the operation of the shutter 109 is preferably
`synchronized with the rotation ofthe shaft 125, and the opera-
`tion of the shutter 109 is controlled so that the infrared light
`passing through the shutter 109 is switched between the first
`infrared light and the second infrared light every three opera-
`tions of the shaft 125 to a revolution of 360 degrees.
`[0101] By controlling the rotation of the shaft 125 and the
`operation of the shutter 109 in such a manner, the infrared
`light reaching the infrared ray detector 108 can be switched in
`the following order: the first infrared light that is transmitted
`
`IPR2017—003 15
`
`CONDITIONAL MOTION TO AMEND
`
`VALENCELL, INC.
`EXHIBIT 2117 — PAGE 14
`
`IPR2017-00315
`CONDITIONAL MOTION TO AMEND
`
`VALENCELL, INC.
`EXHIBIT 2117 - PAGE 14
`
`

`

`US 2009/0270698 A1
`
`Oct. 29, 2009
`
`through the first optical filter 121, the first infrared light that
`is transmitted through the second optical filter 122, the first
`infrared light that is transmitted through the third optical filter
`123, the second infrared light that is transmitted through the
`first optical filter 121, the second infrared light that is trans-
`mitted through the second optical filter 122, and the second
`infrared light that is transmitted through the third optical filter
`123.
`
`[0102] The electric signal outputted from the infrared ray
`detector 108 is amplified by the preliminary amplifier 130. In
`the amplified electric signal, the signal outside the center
`frequency,
`i.e.,
`the frequency band of the chopping,
`is
`removed by the band-pass filter 132. Based on this, noise
`caused by statistical fluctuation such as thermal noise can be
`minimized.
`
`[0103] The electric signal filtered by the band-pass filter
`132 is demodulated to DC signal by the synchronous
`demodulator 134, by synchronizing and integrating the chop-
`ping frequency of the chopper 118 and the electric signal
`filtered by the band-pass filter 132.
`[0104]
`In the electric signal demodulated by the synchro-
`nous demodulator 134, the signal in the high—frequency band
`is removed by the low-pass filter 136. Based on this, noise is
`further removed.
`
`[0105] The electric signal filtered by the low-pass