as) United States
`a2) Patent Application Publication (0) Pub. No.: US 2014/0051955 Al
`
` Tiaoet al. (43) Pub. Date: Feb. 20, 2014
`
`
`US 20140051955A1
`
`(54) DETECTING DEVICE
`
`(30)
`
`Foreign Application Priority Data
`
`(71) Applicant: Industrial Technology Research
`Institute, Hsinchu (TW)
`
`(TW) oes 102127307
`Jul. 30, 2013)
`Publication Classification
`
`(72)
`
`Inventors: Kuo-Tung Tiao, Hsinchu County (TW);
`(51)
`Int. Cl.
`De
`(2006.01)
`AGIB 5/1455
`Jyh-Chern Chen, New Taipei City
`,
`(52) US.CI
`(TW); Yu-Tang Li, New Taipei City
`CPC vivccccssssssssssessnseeene AGIB 5/14552 (2013.01)
`(TW); Chang-Sheng Chu, Hsinchu City
`USPC
`600/323. 600/322
`(TW); Shuang-Chao Chung, Hsinchu
`County (TW); Chih-Hsun Fan, HsinchyUSPCverre ;
`City (TW); Ming-Chia Li, Taichung
`(57)
`ABSTRACT
`City (TW)
`A detecting device includes at least one detecting module. In
`the detecting module, a light source unit is configured to emit
`a first beam and a second beam. The wavelength ofthe first
`beam is different from that of the second beam. A packaging
`unit is disposed on the light source unit and a light detecting
`unit and on transmission paths of the first beam and the
`second beam from the light source unit. An optical micro-
`structure unit is disposed on the transmissionpathsofthefirst
`beam and the second beam. Thefirst beam and the second
`beam emitted from the light source unit pass through the
`packaging unit to pass the optical microstructure unit to be
`transmitted to a biological tissue, and then pass through the
`optical microstructure unit to pass the packaging unit to be
`transmitted to the light detecting unit in sequence.
`
`(73) Assignee:
`
`Industrial Technology Research
`Institute, Hsinchu (TW)
`
`(21) Appl. No.: 13/970,613
`
`(22)
`
`Filed:
`
`Aug. 20, 2013
`
`+
`as
`Related U.S.Application Data
`(60) Provisional application No. 61/684,819, filed on Aug.
`20, 2012.
`
`
`
`
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`260 200
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`APPLE 1073
`Apple v. Masimo
`IPR2022-01291
`
`1
`
`APPLE 1073
`Apple v. Masimo
`IPR2022-01291
`
`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 1 of 9
`
`US 2014/0051955 Al
`
`210
`a
`212
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`Patent Application Publication
`
`Feb. 20,2014 Sheet 2 of 9
`
`US 2014/0051955 Al
`
`212
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`
`250
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`220
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`260 ~200
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`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 3 of 9
`
`US 2014/0051955 Al
`
`10 660nm
`
`--------- oxyhemoglobin
`
` deoxyhemoglobin
`
`
`
`absorptionrate
`
`0.1
`600
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`:
`
`700
`
`800
`
`900
`
`1000
`
`wavelength
`(nanometer)
`
`FIG. 2
`
`4
`
`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 4 of 9
`
`US 2014/0051955 Al
`
`213
`——_—"——__—
`2131 2132
`
`210a
`Soon
`212
`216a
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`232
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`— 2
`
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`5
`
`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 5 of 9
`
`US 2014/0051955 Al
`
`2350
`—_——_
`232
`234
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`BO}
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`2090
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`250
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`ae
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`50
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`242a 244a
`eredand
`240a
`
`FIG. 3B
`
`6
`
`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 6 of 9
`
`US 2014/0051955 Al
`
`
`
`d
`
`930
`210a
`efTffjfe——s OO
`216a
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`242a 244a
`cee
`240a
`
`FIG. 3C
`
`7
`
`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 7 of 9
`
`US 2014/0051955 Al
`
`20 &200b
`20
` Ef
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`ycf
`]
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`20 902006
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`f
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`232
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`240b
`
`230
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`FIG. 4B
`
`8
`
`8
`
`

`

`Patent Application Publication
`
`US 2014/0051955 Al
`
`Feb. 20,2014 Sheet 8 of 9
`
`110
`
`9
`
`

`

`Patent Application Publication
`
`Feb. 20,2014 Sheet 9 of 9
`
`US 2014/0051955 Al
`
`200
`
`200
`
`FIG. SC
`
`10
`
`

`

`US 2014/0051955 Al
`
`Feb. 20, 2014
`
`DETECTING DEVICE
`
`CROSS-REFERENCE TO RELATED
`APPLICATION
`
`[0001] This application claimsthepriority benefits of U.S.
`provisionalapplication Ser. No. 61/684,819, filed on Aug. 20,
`2012 and Taiwan application serial no. 102127307, filed on
`Jul. 30, 2013. The entirety of each of the above-mentioned
`patent applicationsis hereby incorporated by reference herein
`and madea part ofthis specification.
`
` TECHNICAL FIELD
`
`[0002] The technical field relates to a detecting device.
`
`BACKGROUND
`
`[0003] Apparatuses and devices for measuring physiologi-
`cal parameters of organism or human bodybyutilizing vari-
`ous optical principles are gradually matured along with the
`advances in optical-clectronic technologies. Generally, a
`non-invasive measurement can be accomplished by using an
`optical principle measuring technology, which offers impor-
`tant contributions and application values in medicalor bio-
`logicalfield, for it can effectively prevent infections or con-
`tagious diseases.
`[0004] A conventional reflective oximeter is utilized to
`infiltrate an infrared light and a nearinfrared light into human
`body, and measure a light signal being returned. Later, a
`signal processoris utilized to calculate a blood oxygenation
`saturation by comparing absorption proportions of oxyhemo-
`globin (HbO,) and deoxyhemoglobin (Hb) for the infrared
`light and the near infrared light. Two major elements in the
`oximeter include one being a hardware measuring device for
`emitting and receivingthe light signal and convertingthelight
`signal being received into an electrical signal; and another
`one being a display hardware and a software thereof in which
`blood oxygen values can be calculated. Since the measuring
`device often requires to be contacted to surfaces of human
`body, noises may be generated due to movements of the
`human bodyor changesin physiological conditions, which is
`prone to wrong blood oxygen values. Accordingly, the oxime-
`ter usually requires a software to filter out the noises, so as to
`ensure an accuracy of the value being read.
`
`SUMMARY
`
`[0005] One of exemplary embodiments provides a detect-
`ing device configured to detect a physiological parameter ofa
`biological tissue. The detecting device comprises at least one
`detecting module, and the detecting module comprisesa light
`source unit, a light detecting unit, a packaging unit and an
`optical microstructure unit. The light source unit is config-
`ured to emit a first beam and a second beam, in which a
`wavelength ofthefirst beam is different from a wavelength of
`the second beam. The packaging unit is disposed onthe light
`source unit and the light detecting unit and located on trans-
`mission pathsofthefirst beam and the second beam from the
`light source unit. The optical microstructure unit is disposed
`on the transmission paths of the first beam and the second
`beam. The first beam and the second beam emitted from the
`light source unit pass through the packaging unit, pass
`through the optical microstructure unit, are transmitted to a
`biological tissue, pass through the optical microstructure unit,
`pass the packaging unit, and are transmitted to the light
`detecting unit in sequence.
`
`Several exemplary embodiments accompanied with
`[0006]
`figures are described in detail below to further describe the
`disclosure in details.
`
`BRIEF DESCRIPTION OF THE DRAWINGS
`
`[0007] The accompanying drawings are included to pro-
`vide further understanding, and are incorporated in and con-
`stitute a part of this specification. The drawingsillustrate
`exemplary embodiments and, together with the description,
`serve to explain the principles of the disclosure.
`[0008]
`FIG. 1A is a bottom schematic view of a detecting
`device according to an embodimentofthe disclosure.
`[0009]
`FIG. 1B is a schematic cross-sectional view of the
`detecting device of FIG. 1A alongline I-I.
`[0010]
`FIG. 1C is a schematic cross-sectional view of the
`detecting device of FIG. 1A alongline II-II.
`[0011]
`FIG. 2 is an absorption spectrum diagram of oxyhe-
`moglobin and deoxyhemoglobin in human body.
`[0012]
`FIG. 3A is a bottom schematic view of a detecting
`device according to another embodimentof the disclosure.
`[0013]
`FIG. 3B is a schematic cross-sectional view of the
`detecting device of FIG. 3A alongline
`[0014]
`FIG. 3C is a schematic cross-sectional view of the
`detecting device of FIG. 3A alongline IV-IV.
`[0015]
`FIG. 4A and FIG.4Bare bottom schematic views of
`a detecting device according to yet another embodimentof
`the disclosure.
`
`FIG. 5A to FIG. 5C are bottom schematic views of
`[0016]
`detecting devices according to three other embodiments of
`the disclosure.
`
`DETAILED DESCRIPTION OF DISCLOSED
`EMBODIMENTS
`
`FIG. 1A is a bottom schematic view of a detecting
`[0017]
`device according to an embodimentofthe disclosure. FIG. 1B
`is a schematic cross-sectional view of the detecting device of
`FIG.1A alongline I-I. FIG. 1C is a schematic cross-sectional
`view of the detecting device of FIG. 1A along line IJ-II.
`Referring to FIG. 1A to FIG. 1C, a detecting device 100 ofthe
`present embodimentis configured to detect a physiological
`parameterof a biological tissue 50. For instance, the biologi-
`cal tissue 50 is, for example, human or animalskin, and the
`physiological parameter is, for example, a blood oxygen-
`ation. The detecting device 100 comprisesat least one detect-
`ing module 200 (one detecting module 200 is illustrated in the
`present embodimentas an example), and the detecting mod-
`ule 200 comprises a light source unit 210, a light detecting
`unit 220, a packaging unit 230 and an optical microstructure
`unit 240. The light source unit 210 is configured to emit a first
`beam B11 (asillustrated in FIG. 1B) and a second beam B2 (as
`illustrated in FIG. 1C), and a wavelengthofthe first beam B1
`is different from a wavelength of the second beam B2. In the
`present embodiment, the wavelengths of the first beam B1
`and the second beam B2 fall within wavelength ranges of a
`red light and an infrared light. For instance,thefirst beam B1
`is the red light with the wavelength being, for example, 660
`nm; and the second beam B2is the infrared light with the
`wavelength being, for example, 910 nm. Alternatively, in
`another embodiment, the first beam B1 can be the infrared
`light and the second beam B2is the red light. Moreover, in
`other embodiments, the wavelengths ofthe first beam B1 and
`the second beam B2fall within the wavelength range of other
`visible light or other invisiblelight.
`
`11
`
`11
`
`

`

`US 2014/0051955 Al
`
`Feb. 20, 2014
`
`Inthe present embodiment, the light source unit 210
`[0018]
`comprises a first light-emitting element 212 and a second
`light-emitting element 214. Thefirst light-emitting element
`212 is configured to emit the beam B1, and the secondlight-
`emitting element 214 is configured to emit the second beam
`B2. In the present embodiment, the first light-emitting ele-
`ment 212 and the second light-emitting element 214 alter-
`nately emit the first beam B1 and the second beamB2. In the
`present embodiment, the light source unit 210 comprises a
`light-emitting diode, which meansthatthefirst light-emitting
`element 212 and the second light-emitting element 214 are,
`for example,
`light-emitting diodes. However,
`in other
`embodiments, the first light-emitting element 212 and the
`second light-emitting element 214 can also be organic light-
`emitting diodes (OLEDs)orlaser diodes. Furthermore, in the
`present embodiment, the light detecting unit 220 is a light
`detector being, for example, a photodiode.
`[0019] The packaging unit 230 is disposed on the light
`source unit 210 andthe light detecting unit 220 and located on
`transmission paths ofthe first beam B1 and the second beam
`B2 from the light source unit 210. In the present embodiment,
`the packaging unit 230 is capable of being penetrated by the
`first beam B1 and the second beam B2. For instance, in the
`present embodiment, the packaging unit 230 is capable of
`being penetrated by the infrared light and the read light.
`However, in other embodiments, the packaging unit 230 can
`also be penetrated bythe infrared light and the visible light.
`Furthermore, in the present embodiment, the packaging unit
`230 comprises a waveguide, which covers the light source
`unit 210 andthe light detecting unit 220. More specifically, in
`the present embodiment, the packaging unit 230 comprises a
`first waveguide 232 and a second waveguide 234. Thefirst
`waveguide 232 covers the light source unit 210, and the
`second waveguide 234 covers the light detecting unit 220.
`[0020] The optical microstructure unit 240 is disposed on
`the transmission paths of the first beam B1 and the second
`beam B2. Thefirst beam B1 and the second beam B2 emitted
`from the light source unit 210 pass through the packaging unit
`230, pass through the optical microstructure unit 240, are
`transmitted to a biological tissue 50, pass through the optical
`microstructure unit 240, pass through the packaging unit 230,
`and are transmittedto the light detecting unit 220 in sequence.
`In the present embodiment, the optical microstructure unit
`240 is a diffractive optical element (DOE) structure. Further-
`more, in the present embodiment, the optical microstructure
`unit 240 is a surface microstructure ofthe packaging unit 230.
`However, in another embodiment, the optical microstructure
`unit 240 can be an optical film, and the optical microstructure
`unit 240 is mounted on the packaging unit 230 (e.g., attached
`to or leaned against the packaging unit 230). In other words,
`the optical microstructure unit 240 can also be a diffractive
`optical element attached to or leaned against the packaging
`unit 230. Furthermore, in other embodiments, the optical
`microstructure unit 240 can also be a holographic optical
`element (HOE), a computer-generated holographic optical
`elementstructure, a fresnel lens structure or a lens grating.
`[0021]
`Inthe present embodiment, the light source unit 210
`and the light detecting unit 220 are located on an identical side
`of the biological tissue 50. More specifically, the first beam
`B1 andthe second beam B2 from the light source unit 210 is
`guided bythe first waveguide 232 to be transmitted to the
`optical microstructure unit 240. In this case,
`the optical
`microstructure unit 240 diffracts the first beam B1 and the
`
`second beam B2. With proper design of the diffractive struc-
`
`ture ofthe optical microstructure unit 240, energies ofthefirst
`beam B1 and the second beam B2 after being diffracted can
`be concentratedinto a diffractive light in one specific diffrac-
`tive order (e.g., the diffractive light in -1 order or +1 order).
`Accordingly, the first beam B1 and the second beam B2 can
`be concentratedly irradiated on the biological tissue 50. For
`instance, the first beam B1 and the second beam B2 can be
`concentratedly irradiated on microvascular in dermis of
`humanskin.Next, the biologicaltissue 50 scatters andreflects
`the first beam B1 and the second beam B2to the optical
`microstructure unit 240. Subsequently, the optical micro-
`structure unit 240 diffracts the first beam B1 and the second
`
`beam B2 to the second waveguide 234, and then the second
`waveguide 234 guides the first beam B1 and the second beam
`B2 to thelight detecting unit 220. With proper design of the
`diffractive structure of the optical microstructure unit 240,
`energies ofthe first beam B1 and the second beam B2 after
`being diffracted can be concentratedinto a diffractive light in
`one specific diffractive order(e.g., the diffractive light in -1
`order or +1 order). Accordingly, the first beam B1 and the
`second beam B2 can be concentratedly irradiated on the light
`detecting unit 220 after being diffracted by the optical micro-
`structure unit 240 and being guided by the second waveguide
`234. As aresult, in the present embodiment, the first beam B1
`and the second beam B2 from the light source unit 210 are
`concentratedly irradiated on the biological tissue 50, and the
`first beam B1 and the second beam B2reflected and scattered
`from the biological tissue 50 are also concentratedly irradi-
`ated on the light detecting unit 220. Therefore, noisesof light
`detected by the light detecting unit 220 can becomeless,
`namely, a signal-noiseratio thereofis higher. Accordingly, an
`electrical signal converted from light detected by the light
`detecting unit 220 can be more correctly and accurately in
`respondtolight intensities ofthe first beam B1 and the second
`beam B2, so as to effectively reduce an error rate of the
`detecting device 100 thereby improving accuracy and reli-
`ability of the detecting device 100. In the present embodi-
`ment, a pitch between the optical microstructures in the opti-
`cal microstructure unit 240 (e.g., a pitch between two
`adjacent ring shapestrips in the optical microstructure unit
`240 depicted in FIG. 1A, namely,a pitch between two adja-
`cent strips in the diffractive optical element) falls,
`for
`example, within a range from 0.05 to 100 um.
`
`FIG. 2 is an absorption spectrum diagram of oxyhe-
`[0022]
`moglobin and deoxyhemoglobin in humanbody. Referring to
`FIG. 1A to FIG. 1C and FIG.2, the detecting device 100 ofthe
`present embodiment can be used to detect a blood oxygen-
`ation of microvascular in dermis of human skin. In view of
`FIG. 2, it can be known that the absorption spectrums of
`oxyhemoglobin and deoxyhemoglobin are different,
`thus
`absorption rates of oxyhemoglobin and deoxyhemoglobin for
`the red light with the wavelength of 660 nm (i.e.the first beam
`B1) and theinfrared light with the wavelength of 910 nm (i.e.
`the second beam B2)are different. For the red light with the
`wavelength of 660 nm,the absorption rate for deoxyhemo-
`globin is higher than the absorption rate for oxyhemoglobin.
`However, for the infrared light with the wavelength of 910
`nm,the absorption rate for oxyhemoglobinis higher than the
`absorption rate for deoxyhemoglobin. Therefore, when a con-
`centration ratio between oxyhemoglobin and deoxyhemoglo-
`bin in microvascular gets higher, a light
`intensity ratio
`betweenthe first beam B1 and the second beam B2is higher.
`On the contrary, when the concentration ratio between oxy-
`hemoglobin and deoxyhemoglobin in microvascular gets
`
`12
`
`12
`
`

`

`US 2014/0051955 Al
`
`Feb. 20, 2014
`
`lower, the light intensity ratio betweenthe first beam B1 and
`the second beam B2is lower. Accordingly, the blood oxygen-
`ation in the biological tissue 50 can be obtained by calculating
`the light intensities of the first beam B1 and the second beam
`B2 measuredbythe light detecting unit 220.
`[0023]
`Inthe present embodiment, the detecting device 100
`further comprises a calculating unit 110 electrically con-
`nectedto the light detecting unit 220. The light detecting unit
`220 convertsthe first beam B1 andthe second beam B2 being
`detected into an electrical signal E, and the calculating unit
`110 calculates the physiological parameter (the blood oxy-
`genation as in the present embodiment) according to the
`electrical signal E. Moreover, in the present embodiment,
`since the first beam B1 and the second beam B2 arealter-
`
`by the light detecting unit 220 being higher, the detecting
`device 100 can serve as the oximeter with higher accuracy and
`reliability. Moreover, as the signal-noise ratio being higher,it
`is not required for the calculating unit 110 to adopt complex
`algorithmsto reduce the noise, such that manufacturing cost
`and calculation time of the calculating unit 110 can also be
`lowered.
`
`converting material 216a. The first light-emitting element
`212 has a light-emitting surface 213 and configured to emit an
`original beam BO from the light-emitting surface 213. The
`wavelength converting material 216a covers a first portion
`2131 ofthe light-emitting surface 213, and exposes a second
`portion 2132 of the light-emitting surface 213. Therein, at
`least a part of the original beam BO emitted by the first
`portion 2131 is converted into the second beam B2 by the
`wavelength converting material 216a, and the first beam B1 is
`formed by the original beam BO emitted by the second por-
`tion 2132. In the present embodiment, a wavelength of the
`original beam BO is identical to the wavelength of thefirst
`beam B1. In other words, since the original beam BO emitted
`by the second portion 2132 does not pass through the wave-
`length converting material 216a, the original beam BO ofsaid
`nately emitted, the light intensity detected by the light detect-
`portion is the first beam B1. In the present embodiment, the
`ing unit 220 whenthefirst beam B1 being emitted is the light
`wavelength converting material 216a is, for example, a phos-
`intensity of thefirst beam B1, andthe light intensity detected
`phor. However, in other embodiments, thefirst portion 2131
`by the light detecting unit 220 when the second beam B2
`and the second portion 2132 can also be covered with two
`being emitted is the light intensity of the second beam B2.
`different wavelength converting materials, so as to covert the
`According to above-said method,the calculating unit 110 can
`original beam B0 intothefirst beam B1 and the second beam
`then determine whenis the electrical signal E representing the
`B2, respectively. In this case, the wavelength of the original
`light intensity of the first beam B1, and whenis the electrical
`beam B0 is smaller than the wavelengthofthefirst beam B1,
`signal E representing the light intensity of the second beam
`and is smaller than the wavelength of the second beam B2.
`B2. In other words, the calculating unit 110 obtains the light
`intensity of the first beam B1 andthe light intensity of the
`[0029]
`Furthermore, in the present embodiment, a light
`second beam B2 in a mannerof time multiplexing.
`detecting unit 220@ comprisesafirst light detector 222a and
`[0024]
`In the present embodiment, since the signal-noise
`a secondlight detector 224a. An optical microstructure unit
`ratio of the first beam B1 and the second beam B2 measured
`240a transmitsthefirst beam B1 from the biological tissue 50
`to the first light detector 222a, and the optical microstructure
`unit 240a transmits the second beam B2 from the biological
`tissue 50 to the second light detector 224a. In the present
`embodiment, the optical microstructure unit 240@ comprises
`a first optical microstructure 242a and a secondoptical micro-
`structure 244a. Thefirst optical microstructure 242a is dis-
`posed on the transmission pathsofthe first beam B1 and the
`second beam B2 from the light source unit 210a, and is
`configured to transmitthe first beam B1 and the second beam
`B2 from the light source unit 210a to the biologicaltissue 50.
`The second optical microstructure 244a is disposed on the
`transmission paths of the first beam B1 and the second beam
`B2 from the biologicaltissue 50, and is configuredto transmit
`the first beam B1 and the second beam B2 from the biological
`tissue 50 to the light detecting unit 220a.
`[0030] More specifically, the first optical microstructure
`242a concentrates the first beam B1 and the second beam B2
`from the first waveguide 232 towards different directions, so
`as to be irradiated on the biological tissue 50. Furthermore,
`the first beam B1 and the second beam B2 from the biological
`tissue 50 are concentrated by the second optical microstruc-
`ture 244a towardsthefirst light detector 222a and the second
`light detector 224a, respectively. In other words, the first
`beam B1 and the second beam B2 can be detected bythefirst
`light detector 222a and the second light detector 224a,
`respectively, thus the light source unit 210a@ can simulta-
`neously emit the first beam B1 and the second beam B2. In
`other words, the light detecting unit 220a@ detects the first
`beam B1 and the second beam B2 in a manner ofspatial
`multiplexing.
`[0031]
`In the present embodiment, the first light detector
`222a and the second light detector 224a are, for example,
`photodiodes, andthefirst optical microstructure 242a and the
`second optical microstructure 244a are, for example, a dif-
`fractive optical element (DOE) structures. Furthermore, in
`the present embodiment,the first optical microstructure 242a
`
`In the present embodiment, the detecting module
`[0025]
`200 further comprises an outer cover 260 covering the light
`source unit 210, the light detecting unit 220 and the packaging
`unit 230. The outer cover 260 is capable of blocking an
`ambient light from the outside, so as to prevent the light
`detecting unit 220 from generating noises due to influence of
`the ambient light. Accordingly,the signal-noise ratio detected
`by the light detecting unit 220 can be further improved.
`[0026]
`Furthermore, in the present embodiment, the detect-
`ing module 200 further comprisesa light separating unit 250
`which separates the first waveguide 232 and the second
`waveguide 234. The light separating unit 250 can effectively
`preventthe first beam B1 and the second beam B2 from the
`light source unit 210 from being transmitted to the light
`detecting unit 220 without being irradiated on the biological
`tissue 50, so as to further improve the signal-noiseratio.
`[0027]
`FIG. 3A is a bottom schematic view of a detecting
`device according to another embodimentof the disclosure.
`FIG. 3B is a schematic cross-sectional view of the detecting
`device of FIG. 3A along line II-III. FIG. 3C is a schematic
`cross-sectional view ofthe detecting device of FIG. 3A along
`line IV-IV. Referring to FIG. 3 to FIG. 3C,a detecting device
`100a of the present embodimentis similar to the detecting
`device 100 depicted in FIG. 1A, in which identical reference
`numerals indicate identical or similar components, and the
`difference between the twois described as below.
`
`Ina detecting module 200a of the detecting device
`[0028]
`100a of the present embodiment, a light source unit 210a
`comprisesa first light-emitting element 212 and a wavelength
`
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`US 2014/0051955 Al
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`Feb. 20, 2014
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`and the second optical microstructure 244aare, for example,
`surface microstructures of the first waveguide 232 and the
`second waveguide 234, respectively. However, in another
`embodiment, the first optical microstructure 242a and the
`second optical microstructure 244a can be twoopticalfilms,
`which are mountedonthe first waveguide 232 and the second
`waveguide 234, respectively (e.g., attached to or leaned
`against the first waveguide 232 and the second waveguide
`234, respectively). In other words,thefirst optical microstruc-
`ture 242a and the second optical microstructure 244a can also
`be two diffractive optical elements which are attached to or
`leaned against
`the first waveguide 232 and the second
`waveguide 234, respectively. Furthermore, in other embodi-
`ments, the first optical microstructure 242a@ and the second
`optical microstructure 244a can also be holographic optical
`elements (HOEs), computer-generated holographic optical
`elementstructures, fresnel lens structures or a lens gratings.
`In the present embodiment, a pitch betweenthefirst optical
`microstructure 242a and the second optical microstructure
`244a (e.g., a pitch between two adjacentarc shapestrips in the
`first optical microstructure 242a and the second optical
`microstructure 244a depicted in FIG. 3A, namely, a pitch
`between two adjacentstrips in the diffractive optical element)
`falls, for example, within a range from 0.05 to 100 um.
`[0032]
`In the present embodiment, with proper design of
`the diffractive structure of the first optical microstructure
`242a, energies ofthefirst beam B1 and the second beam B2
`from the first waveguide 232 can be concentrated into a dif-
`fractive light in one specific diffractive order(e.g., -1 order or
`+1 order). Therefore, the first beam B1 and the second beam
`B2 can be concentratedly irradiated towards different direc-
`tions and on different positions of the biological tissue 50.
`Next, the second optical microstructure 244a can concentrate
`the energiesofthe first beam B1 and the second beam B2 from
`the biological tissue 50 into a diffractive light in one specific
`diffractive order (e.g., -1 order or +1 order). Therefore, the
`first beam B1 and the second beam B2 from the biological
`tissue 50 can be concentrated onthefirst light detector 222a
`and the second light detector 224a, respectively. Accordingly,
`the signal-noise ratio detected by the detecting device 100a
`can be effectively improved thereby improving accuracy and
`reliability of the detecting device 100a.
`[0033]
`Inthe present embodiment, the calculating unit 110
`can receive an electrical signal E1 from thefirst light detector
`222a andan electrical signal E2 from the secondlight detec-
`tor 224a. Therein, the electrical signal E1 correspondsto the
`light intensity ofthe first beam B1, and theelectrical signal E2
`correspondsto the light intensity of the second beam B2.
`[0034]
`In the present embodiment,the first optical micro-
`structure 242a and the secondoptical microstructure 244a are
`twoseparate structures. However, in other embodiments, the
`first optical microstructure 242a and the second optical
`microstructure 244a can also be manufactured on the same
`
`the outer cover 260 and covering the first waveguide 232 and
`the second waveguide 234. The optical microstructure unit
`2405 can comprise a diffractive optical elementstructure, a
`holographic optical element, a computer-generated holo-
`graphic elementstructure, a fresnel lens structure or a lens
`grating.
`FIG. 5A to FIG. 5C are bottom schematic views of
`[0036]
`detecting devices according to three other embodiments of
`the disclosure. Referring to FIG. 5A to FIG. 5C, detecting
`devices 100c, 100d and 100e are similar to the detecting
`device 100 depicted in FIG.1A,the differences therebetween
`is described as below. Each of the detecting devices 100c,
`100d and 100e comprises a plurality of detecting modules
`200, and the detecting modules 200 are arranged a two-
`dimensional array. Therein, detailed structure of each of the
`detecting modules 200 is identical to the detecting module
`200 depicted in FIG. 1A, thus related description are not
`repeated hereinafter. The detailed structure of each of the
`detecting modules 200 is not illustrated again in FIG. 5A to
`FIG.5C,and said detailed structure can refer to FIG. 1A and
`related description thereof.
`[0037]
`In FIG. 5A,the detecting modules 200 are arranged
`in the two-dimensional array, and the detecting modules are
`fixed on a connecting piece 120. In FIG. 5B, the detecting
`modules 200 are arranged in a two-dimensional array of
`dislocation (e.g., a cellular two-dimensional array), and the
`detecting modules are fixed on a connecting piece 120. In
`FIG. 5C, the detecting modules 200 are arranged in the cir-
`cular array, and the detecting modules are fixed on a connect-
`ing piece 120e. The connecting pieces 120 and 120e can bea
`flexible connecting piece, so that the detecting modules 200
`can be bended along a shape of skin and to be attached on
`different positions of skin. Accordingly, physiological
`parameters(e.g., the blood oxygenation)at different positions
`ofhuman body can be simultaneously monitored. Ifa number
`of the detecting module 200 is dense enough to form a physi-
`ological parameter image(e.g., a blood oxygenation image),
`a distribution status of the physiological parameter can be
`obtained. Shapes of the connecting pieces 120 and 120e may
`vary according to different shapes of the two-dimensional
`array. For instance, the connecting piece 120 is a rectangular
`shape, and the connecting piece 120e is a circular shape.
`However, in other embodiments, the detecting modules 200
`can also be arranged in the two-dimensional array of other
`shapes, and the connecting pieces can also be of other shapes.
`In addition, the calculating unit 110 is electrically connected
`to the detecting modules 200 so as to perform calculations
`according to the light intensities detected by the detecting
`modules 200.
`
`[0038] Moreover, the detecting modules 200 in the detect-
`ing devices 100c, 100d, 100¢ can be replaced by the detecting
`modules 200a or 2006 in the previous embodiments, or the
`detecting modules in other embodiments.
`[0039]
`In summary, in the detecting device of the embodi-
`ment of the disclosure, the optical microstructure unit is
`adopted to have the first beam and the second beam concen-
`tratedly irradiated on the biological tissue, and the optical
`microstructure unit is utilized to have thefirst beam and the
`
`optical film.
`[0035] FIG.4A and FIG.4B are bottom schematic views of
`a detecting device according to yet another embodiment of
`the disclosure. Referring to FIG. 4A and FIG.4B, a detecting
`device 1005 of the present embodiment is similar to the
`detecting device 100 depicted in FIG. 1B and FIG.1C,and the
`second beam from the biological tissue concentratedly irra-
`difference between the twois described asbelow.Inadetect-
`diated on the light detecting unit. Therefore, the signal-noise
`ratios ofthe first beam and the second beam measured bythe
`light detecting unit are higher. Accordingly, the detecting
`device ca