U.S. patent application number 16/179516 was filed with the patent office on 2019-03-21 for photoacoustic apparatus.
The applicant listed for this patent is CANON KABUSHIKI KAISHA. Invention is credited to Hiroshi Abe.
Application Number | 20190082967 16/179516 |
Document ID | / |
Family ID | 52777502 |
Filed Date | 2019-03-21 |
United States Patent
Application |
20190082967 |
Kind Code |
A1 |
Abe; Hiroshi |
March 21, 2019 |
PHOTOACOUSTIC APPARATUS
Abstract
A photoacoustic apparatus disclosed in the present specification
includes: a light source configured to emit light; an acoustic wave
transmission unit configured to transmit an acoustic wave to a
specific area; a photoacoustic wave reception unit configured to
receive a photoacoustic wave generated by a subject due to emission
of the light, which is emitted from the light source, to the
subject and configured to output a time-series photoacoustic
signal; an echo reception unit configured to receive an echo
generated due to reflection, in the subject, of the acoustic wave
transmitted from the acoustic wave transmission unit and configured
to output a time-series echo signal; and a processing unit
configured to acquire, based on the time-series photoacoustic
signal and the time-series echo signal, optical property
information in which information a component corresponding to a
reflected wave of the photoacoustic wave generated in the specific
area is reduced.
Inventors: |
Abe; Hiroshi; (Kyoto-shi,
JP) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
CANON KABUSHIKI KAISHA |
Tokyo |
|
JP |
|
|
Family ID: |
52777502 |
Appl. No.: |
16/179516 |
Filed: |
November 2, 2018 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14502040 |
Sep 30, 2014 |
10143382 |
|
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16179516 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
G01N 21/1702 20130101;
G01N 2021/1706 20130101; A61B 5/0095 20130101 |
International
Class: |
A61B 5/00 20060101
A61B005/00; G01N 21/17 20060101 G01N021/17 |
Foreign Application Data
Date |
Code |
Application Number |
Oct 4, 2013 |
JP |
2013-209624 |
Claims
1. A photoacoustic apparatus comprising: a light source configured
to emit light; an acoustic wave transmission unit configured to
transmit an acoustic wave; a photoacoustic wave reception unit
configured to receive a photoacoustic wave generated by emission of
the light, which is emitted from the light source, to a subject and
configured to output a time-series photoacoustic signal; an echo
reception unit configured to receive an echo generated due to
reflection of the acoustic wave transmitted from the acoustic wave
transmission unit and configured to output a time-series echo
signal; and a processing unit configured to acquire initial sound
pressure distribution based on the time-series photoacoustic
signal, acquire echo sound pressure distribution based on the
time-series echo signal, and acquire difference distribution
between the initial sound pressure distribution and the echo sound
pressure distribution.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation, and claims the benefit,
of U.S. patent application Ser. No. 14/502,040, presently pending
and filed on Sep. 30, 2014, and claims the benefit of, and priority
to, Japanese Patent Application No. 2013-209624, filed Oct. 4,
2013, which applications are hereby incorporated by reference
herein in their entireties.
BACKGROUND OF THE INVENTION
Field of the Invention
[0002] The present invention relates to a photoacoustic apparatus
to acquire optical property information by using a photoacoustic
wave.
Description of the Related Art
[0003] A study of an optical imaging apparatus to image information
inside a subject, which information is acquired by emitting light
from a light source such as a laser to the subject such as a living
body and acquired based on the incident light, has been actively
done in a medical field. As one kind of the optical imaging
technique, there is photoacoustic imaging (PAI). In the
photoacoustic imaging, pulsed light generated in a light source is
emitted to a subject and an acoustic wave (typically, ultrasonic
wave) generated in a subject tissue which absorbs energy of the
pulsed light propagated and diffused in the subject is received.
Based on the received signal, imaging of information of the subject
is reconstructed.
[0004] That is, by using a difference between absorptance of
optical energy in an object region such as a tumor and that in
other tissues, an elastic wave (photoacoustic wave) generated when
a region to be inspected absorbs the emitted optical energy and
instantaneously expands is received by a probe. By performing
mathematical analysis processing on this received signal, optical
property information inside the subject, specifically, initial
sound pressure distribution, optical energy absorption density
distribution, absorption coefficient distribution, or the like can
be acquired.
[0005] These pieces of information can also be used, for example,
for a quantitative measurement of a specific substance inside the
subject such as oxygen saturation in blood. Recently, by using the
photoacoustic imaging, a preclinical study to image a blood vessel
image of a small animal or a clinical study to apply this principle
to a diagnosis of a breast cancer or the like has been actively
done ("Photoacoustic Tomography: In Vivo Imaging From Organelles to
Organs", Lihong V. Wang Song Hu, Science 335, 1458 (2012)). In the
photoacoustic imaging, generally, it is desired to image optical
property distribution of an optical absorber inside the
subject.
SUMMARY OF THE INVENTION
[0006] A photoacoustic apparatus disclosed in the present
specification includes: a light source configured to emit light; an
acoustic wave transmission unit configured to transmit an acoustic
wave to a specific area; a photoacoustic wave reception unit
configured to receive a photoacoustic wave generated by a subject
due to emission of the light, which is emitted from the light
source, to the subject and configured to output a time-series
photoacoustic signal; an echo reception unit configured to receive
an echo generated due to reflection, in the subject, of the
acoustic wave transmitted from the acoustic wave transmission unit
and configured to output a time-series echo signal; and a
processing unit configured to acquire, based on the time-series
photoacoustic signal and the time-series echo signal, optical
property information of the subject in which information a
component corresponding to a reflected wave of the photoacoustic
wave generated in the specific area is reduced.
[0007] Further features of the present invention will become
apparent from the following description of exemplary embodiments
(with reference to the attached drawings).
BRIEF DESCRIPTION OF THE DRAWINGS
[0008] FIG. 1 is a schematic view illustrating a photoacoustic
apparatus according to a first embodiment.
[0009] FIG. 2 is a flowchart illustrating an operation flow of the
photoacoustic apparatus according to the first embodiment.
[0010] FIGS. 3A to 3C are views illustrating various signals which
can be acquired in the first embodiment.
[0011] FIG. 4 is a flowchart illustrating an operation flow of a
photoacoustic apparatus according to a second embodiment.
[0012] FIGS. 5A to 5D are views illustrating various kind of
distribution which can be acquired in the second embodiment.
DESCRIPTION OF THE EMBODIMENTS
[0013] A photoacoustic wave generated in an optical absorber is
transmitted and propagated isotropically with a shape of the
optical absorber as an origin. Then, a probe receives not only a
photoacoustic wave directly propagated thereto from the optical
absorber but also a reflected wave generated due to reflection of
the photoacoustic wave generated in the optical absorber. Since the
reflected wave is not propagated to the probe directly and takes
different time of flight, reconstructed image does not depict a
true optical absorber's figure. Then, decrease in quantitativity of
optical property information acquired from a received signal
including a component corresponding to this reflected wave is
caused.
[0014] The photoacoustic apparatus disclosed in the present
specification uses a received signal of an echo of an acoustic wave
transmitted to a specific area and acquires optical property
information from which a component corresponding to a reflected
wave of a photoacoustic wave generated in the specific area is
reduced. Specifically, since intensity of a photoacoustic wave
generated in a part to which light is directly emitted (such as
skin on surface of subject, acoustic lens arranged on surface of
probe, or the like) is high, intensity of a reflected wave of the
photoacoustic wave also becomes high. Thus, quantitativity of
acquired optical property information is greatly decreased due to
such a reflected wave. In each embodiment, a case where a component
corresponding to a reflected wave of a photoacoustic wave generated
on a surface of a subject is reduced based on a received signal of
an echo will be described. That is, in each embodiment, a surface
of a subject to which light is emitted will be described as a
source of a reflected wave. In the following, an effect in each
embodiment will be described.
[0015] A waveform of a reflected wave generated due to reflection,
by a reflector inside the subject, of a photoacoustic wave
generated on a surface of a subject and a waveform of an echo
generated due to reflection of a transmitted acoustic wave by the
same reflector become similar shapes. Thus, a received signal of
the reflected wave of the photoacoustic wave and a received signal
of the echo become similar signals.
[0016] Thus, by acquiring a difference signal between a received
signal of a photoacoustic wave and a received signal of an echo, a
photoacoustic apparatus according to a first embodiment can reduce
a component corresponding to a reflected wave of the photoacoustic
wave.
[0017] Incidentally, distribution of an initial sound pressure of
when a photoacoustic wave is generated can be acquired from a
received signal of the photoacoustic wave. On the other hand,
similarly to the initial sound pressure distribution, sound
pressure distribution of an echo of when the echo is generated can
be acquired from a received signal of the echo. Then, components
respectively corresponding to a reflected wave of the photoacoustic
wave and an echo, which are by the same reflector, respectively
appear at the same position in the initial sound pressure
distribution and the echo sound pressure distribution.
[0018] Thus, by acquiring difference distribution between initial
sound pressure distribution acquired from a received signal of a
photoacoustic wave and echo sound pressure distribution acquired
from a received signal of an echo, a photoacoustic apparatus
according to a second embodiment can reduce a component
corresponding to a reflected wave of the photoacoustic wave.
[0019] As described, according to a photoacoustic apparatus
disclosed in the present specification, a component corresponding
to a reflected wave of a photoacoustic wave can be reduced. Thus,
according to the photoacoustic apparatus disclosed in the present
specification, decrease in quantitativity of optical property
information due to a component corresponding to a reflected wave of
a photoacoustic wave can be controlled.
[0020] Note that as the optical property information, there are
initial sound pressure distribution of a photoacoustic wave,
optical energy absorption density distribution, absorption
coefficient distribution, concentration distribution of a substance
included in a subject, and the like. Here, a concentration of a
substance is, for example, oxygen saturation, an oxyhemoglobin
concentration, a deoxyhemoglobin concentration, or a total
hemoglobin concentration.
[0021] Also, a reflected wave in the present specification includes
an acoustic wave generated by scattering.
[0022] In the following, embodiments of a photoacoustic apparatus
according to the present invention will be described in detail with
reference to the attached drawings. However, the scope of the
invention is not limited to the illustrated examples.
First Embodiment
[0023] A photoacoustic apparatus according to the present
embodiment will be described with reference to FIG. 1. FIG. 1 is a
view schematically illustrating the photoacoustic apparatus
according to the present embodiment. By acquiring a difference
signal between a received signal of a photoacoustic wave and a
received signal of an echo of a transmitted acoustic wave, the
photoacoustic apparatus according to the present embodiment reduces
a component corresponding to a reflected wave of the photoacoustic
wave.
[0024] In the following, a received signal of a photoacoustic wave
is also referred to as a "photoacoustic signal" and a received
signal of an echo of a transmitted acoustic wave is also referred
to as an "echo signal".
[0025] The photoacoustic apparatus according to the present
embodiment includes a light source 110, an optical system 120, a
transducer array 130, a computer 150 as a processing unit, a
display unit 160, and an input unit 170. Note that the transducer
array 130 includes a function as an acoustic wave transmission unit
configured to transmit an acoustic wave to a subject 100. Also, the
transducer array 130 includes functions as a photoacoustic wave
reception unit configured to receive a photoacoustic wave and an
echo reception unit configured to receive an echo.
[0026] Next, an operation of the photoacoustic apparatus according
to the present embodiment will be described with reference to FIG.
2. Note that the computer 150 controls an operation of each
configuration of the photoacoustic apparatus.
[0027] (S100: Process for Receiving Photoacoustic Wave and
Acquiring Time-Series Photoacoustic Signal)
[0028] First, the light source 110 generates pulsed light 121. The
pulsed light 121 is emitted to the subject 100 through the optical
system 120. Then, the pulsed light 121 is absorbed by an optical
absorber 101 placed inside the subject 100. The optical absorber
101 which has absorbed the pulsed light 121 expands
instantaneously, and thus, a photoacoustic wave 103 is generated.
On the other hand, the pulsed light 121 is absorbed also on a
surface 105 of the subject 100 and a photoacoustic wave is
generated. The photoacoustic wave generated on the surface 105 of
the subject 100 is classified broadly into a photoacoustic wave
104a generated in a direction of the transducer array 130 and a
photoacoustic wave 104b generated in an opposite direction of the
transducer array 130. The photoacoustic wave 104b is propagated in
the subject 100 and reflected by the optical absorber 101, and
thus, a reflected wave 104c is generated. In the present
embodiment, each of the photoacoustic waves 104a and 104b generated
on the surface 105 of the subject 100 is a photoacoustic wave
generated in a part to which the pulsed light 121 is directly
emitted.
[0029] The transducer array 130 receives a photoacoustic wave
including the photoacoustic wave 104a and the reflected wave 104c
and converts the received photoacoustic wave into a time-series
photoacoustic signal S1 (t). The computer 150 performs processing
of amplification and A/D conversion on the time-series
photoacoustic signal S1 (t) output from the transducer array 130
and houses the processed signal into a storage unit 151 in the
computer 150. It is assumed that t indicates time and t=0 is a time
point at which a light source 110 generates the pulsed light 121.
That is, the computer 150 performs control to start acquiring a
photoacoustic signal at the time point at which the light source
110 generates the pulsed light 121. For example, by controlling
driving of the transducer array 130 or housing, into a memory, of
the photoacoustic signal output from the transducer array 130, the
computer 150 can control acquisition of the photoacoustic
signal.
[0030] Here, the time-series photoacoustic signal S1 (t) will be
described. FIG. 3A is a view illustrating the time-series
photoacoustic signal S1 (t) acquired by a specific transducer.
[0031] An interface signal 301 in the time-series photoacoustic
signal S1 (t) is a received signal of the photoacoustic wave 104a
generated on the surface 105 of the subject 100. Also, an absorber
signal 302 is a received signal of the photoacoustic wave 103
generated in the optical absorber 101. Also, a reflected signal 303
is a received signal of the reflected wave 104c generated due to
reflection, by the optical absorber 101, of the photoacoustic wave
104b generated on the surface 105 of the subject 100. That is, the
reflected signal 303 is a component corresponding to a reflected
wave in the time-series photoacoustic signal S1 (t).
[0032] (S200: Process for Receiving Echo of Transmitted Acoustic
Wave and Acquiring Time-Series Echo Signal)
[0033] In the present process, first, the transducer array 130
transmits an acoustic wave 102a to the subject 100. The acoustic
wave 102a is propagated in an acoustic matching material 140 and
reaches the surface 105 of the subject 100. A part of the acoustic
wave 102a is reflected by the surface 105 of the subject 100 and
becomes a component of an echo 102d and a part of the acoustic wave
102a is transmitted and becomes a component of an acoustic wave
102b. The acoustic wave 102b is reflected by the optical absorber
101 as a reflector and an echo 102c is generated.
[0034] The transducer array 130 receives the echoes 102c and 102d
and converts the received echoes into a time-series echo signal S2
(t). Then, the computer 150 performs processing of amplification
and A/D conversion on the time-series echo signal S2 (t) output
from the transducer array 130 and houses the processed signal into
the storage unit 151 in the computer 150. In the time-series echo
signal S2 (t), it is assumed that t=0 is a time point at which the
transducer array 130 transmits the acoustic wave 102a.
[0035] Here, the time-series echo signal S2 (t) will be described.
FIG. 3B is a view illustrating the time-series echo signal S2 (t)
acquired by a specific transducer. A reflected signal 304 in the
time-series echo signal S2 (t) is a received signal of the echo
102d reflected by the surface 105 of the subject 100. A reflected
signal 305 is a received signal of the echo 102c generated due to
reflection, by the optical absorber 101, of the acoustic wave 102b
transmitted through the surface 105 of the subject 100.
[0036] <Transmission Waveform>
[0037] To make the echo 102c reproduce the reflected wave 104c of
the photoacoustic wave 104b, a transmission waveform of the
transducer array 130 is preferably controlled in such a manner that
a waveform of the acoustic wave 102b and a waveform of the
photoacoustic wave 104b become similar to each other. In the
following, an example of a method for determining a transmission
waveform will be described. Note that a method is not limited to
the following method, as long as a transmission waveform, with
which the waveform of the acoustic wave 102b and the waveform of
the photoacoustic wave 104b become similar to each other, can be
determined.
[0038] First, the computer 150 estimates a waveform of the
photoacoustic wave 104b based on a size or a shape of the surface
105 (source of reflected wave) of the subject 100. In the
photoacoustic wave, a waveform having a different frequency
characteristic is generated depending on a shape of a substance. As
a general solution, it is known that when a shape of the optical
absorber is a slab shape, the waveform becomes a waveform protruded
upward, and in a case of a spherical shape, the waveform becomes an
N-shaped waveform. Thus, from a shape of the source of a reflected
wave, a waveform of the photoacoustic wave generated in the source
of a reflected wave can be estimated.
[0039] Subsequently, the computer 150 can calculate a waveform to
be transmitted from the transducer array 130 by a photoacoustic
wave equation in such a manner that a waveform of the acoustic wave
102b and a waveform of the photoacoustic wave 104b become similar
to each other. Note that according to a waveform to be reproduced,
the computer 150 can arbitrarily calculate a waveform to be
transmitted by the photoacoustic wave equation including the decay
factor or transducer's response function.
[0040] Also, the computer 150 may determine a transmission waveform
of the transducer array 130 based on the time-series photoacoustic
signal S1 (t) acquired in S100.
[0041] The computer 150 can extract a received signal of the
photoacoustic wave 104a from the time-series photoacoustic signal
S1 (t) and can calculate a transmission waveform to reproduce a
waveform of the photoacoustic wave 104b at generation from the
received signal of the photoacoustic wave 104a. Since a
photoacoustic wave is isotropically generated, the photoacoustic
wave 104a and the photoacoustic wave 104b have similar waveforms.
Thus, a transmission waveform to reproduce the photoacoustic wave
104b at the generation can be calculated from the received signal
of the photoacoustic wave 104a. Here, it is preferable that the
computer 150 calculates a transmission waveform in consideration of
a frequency characteristic of a transducer, frequency attenuation
during propagation of an acoustic wave, a transducer response, or
the like.
[0042] Also, based on amplitude, a pulse width, or the like of the
received signal of the photoacoustic wave 104a, the computer 150
may select, from a plurality of transmission waveforms stored in
the storage unit 151 in the computer 150, a transmission waveform
to reproduce a waveform of the photoacoustic wave 104b at the
generation.
[0043] Note that by a method described in the following, a received
signal of the photoacoustic wave 104a can be extracted from the
time-series photoacoustic signal S1 (t) acquired in S100. However,
a method is not limited to the following method as long as a
received signal of an object photoacoustic wave can be
extracted.
[0044] Since the surface 105 of the subject 100 is a part to which
light is directly emitted, amplitude of the photoacoustic wave 104a
becomes relatively large. Thus, the computer 150 can extract, from
the time-series photoacoustic signal S1 (t), a waveform having the
largest amplitude as a received signal of the photoacoustic wave
104a.
[0045] Also, since the surface 105 of the subject 100 is close to
the transducer array 130, the photoacoustic wave 104a reaches the
transducer array 130 prior to the other photoacoustic waves. Thus,
the computer 150 can extract, as a received signal of the
photoacoustic wave 104a, a waveform which has amplitude equal to or
larger than a threshold and is output from the time-series
photoacoustic signal S1 (t) in the beginning.
[0046] Also, the time-series photoacoustic signal S1 (t) may be
displayed on the display unit 160 and an arbitrary waveform may be
selected, as a received signal of the photoacoustic wave 104a, with
the input unit 170 by a user.
[0047] Also, initial sound pressure distribution P1 (r) acquired
from the time-series photoacoustic signal S1 (t) by a method which
will be described later may be displayed on the display unit 160
and an arbitrary position of the initial sound pressure
distribution P1 (r) may be specified with the input unit 170 by a
user. Accordingly, a received signal of the photoacoustic wave 104a
can be extracted. For example, a plurality of photoacoustic
signals, which is used to reconstruct an initial sound pressure at
a specified position, can be averaged and selected as a received
signal of the photoacoustic wave 104a. Also, among the plurality of
photoacoustic signals, which is used to reconstruct an initial
sound pressure at a specified position, a waveform of an arbitrary
photoacoustic signal can be selected as a received signal of the
photoacoustic wave 104a. Note that it is preferable that a
photoacoustic signal output from a transducer which anticipates a
specified position in a direction of high directionality is
selected as a received signal of the photoacoustic wave 104a.
[0048] Also, the transducer 130 may form the acoustic wave 102b by
forming a great number of virtual point sound sources along a shape
of the source of a reflected wave by using a known method such as
an acoustic radiation force impulse (ARFI) described in "Acoustic
radiation force impulse imaging of myocardial radio-frequency
ablation: initial in vivo results", Fahey et al., IEEE Transactions
on Ultrasonics, Ferroelectrics and Frequency Control, Volume 52,
Issue 4, April 2005 Page(s): 631-641. Here, based on shape
information acquired by a shape acquisition unit, the computer 150
can determine positions to form the virtual point sound sources.
The computer 150 can control a transmission waveform of the
transducer array 130 in such a manner that the virtual point sound
sources can be formed in determined positions.
[0049] <Propagation Path>
[0050] Note that as a matter of convenience, in FIG. 1, the
acoustic wave 102b and the echo 102c, and the photoacoustic wave
104b and the reflected wave 104c are illustrated in different
propagation paths. However, the acoustic waves preferably include
similar propagation paths in such a manner that a waveform of the
reflected wave 104c and a waveform of the echo 102c become similar
to each other. Thus, the computer preferably controls arrangement
of the optical system 120 and the transducer array 130 and a
transmission direction of the acoustic wave 102a in such a manner
that a position to which the pulsed light 121 is emitted and a
position to which the acoustic wave 102a is transmitted become
similar to each other.
[0051] Also, a deviation between a position of the transducer array
130 to receive a photoacoustic wave in S100 and a position of the
transducer array 130 to receive an echo in S200 is preferably
small. By making the transducer array 130 placed in such a manner,
the reflected wave 104c and the echo 102c are output in similar
received signals.
[0052] (S300: Process for Acquiring Difference Signal Between
Time-Series Photoacoustic Signal and Time-Series Echo Signal)
[0053] In this process, a difference signal S3 (t) between the
time-series photoacoustic signal S1 (t) acquired in S100 and the
time-series echo signal S2 (t) acquired in S200 is acquired. For
example, by subtracting the time-series echo signal S2 (t) from the
time-series photoacoustic signal S1 (t), the difference signal S3
(t) illustrated in FIG. 3C is acquired.
[0054] According to FIG. 3C, it can be understood that the
reflected signal 303 in the time-series photoacoustic signal S1 (t)
is reduced as a result of the subtraction of the time-series echo
signal S2 (t) from the time-series photoacoustic signal S1 (t). On
the other hand, an absorber signal 302 due to the photoacoustic
wave 103 generated in the optical absorber 101 is also reproduced
by the difference signal S3 (t). Thus, by acquiring the difference
signal S3 (t) between the time-series photoacoustic signal S1 (t)
and the time-series echo signal S2 (t), the reflected signal 303
(component corresponding to reflected wave of photoacoustic wave)
can be selectively reduced.
[0055] Note that as a method for performing differential
processing, subtraction in signals of time base data has been
performed. However, any method can be used as long as a difference
between signal components at predetermined reception time can be
acquired. For example, a difference signal may be acquired by the
following manner. That is, by using a Fourier space, a window
function of a time interval, a center of which is a position (time)
of a waveform to be subtracted, is multiplied by S1 (t) and S2 (t)
and is Fourier-transformed, and then, the same frequency spectrum
component is subtracted and inverse Fourier transform is performed.
When a wavelet space is used as a base space, between the signals
which are wavelet-transformed S1 (t) and S2 (t), a signal
coefficient which is in the same time interval is subtracted and
inversely transformed, and thus, a difference signal can be
acquired.
[0056] <Deviation Correction of Reception Time>
[0057] In the present embodiment, it is assumed that in the
time-series photoacoustic signal S1 (t), a time point at which the
pulsed light 121 is emitted is t=0 (reference) and in the
time-series echo signal S2 (t), a time point at which the acoustic
wave 102a is transmitted is t=0 (reference). However, practically,
a period of time from the time point at which the acoustic wave
102a is transmitted to the time point at which the acoustic wave
102a reaches the surface 105 of the subject 100 does not become
zero. In this case, reception time of the reflected signal 303
(received signal of reflected wave 104c) in the time-series
photoacoustic signal S1 (t) and reception time of the reflected
signal 305 (received signal of echo 102c) in the time-series echo
signal S2 (t) are not identical. Thus, a correction to deviate a
reference of the reception time of the time-series photoacoustic
signal S1 (t) or the time-series echo signal S2 (t) may be
performed in such a manner that a difference in the reception time
of the reflected signals becomes small. That is, to make a
difference in the reception time of the echo small, a difference
signal may be acquired after the time-series photoacoustic signal
S1 (t) or the time-series echo signal S2 (t) is corrected. Also,
correction is preferably performed in such a manner that the
reception time of the reflected signals becomes identical.
[0058] Here, the computer 150 can calculate time of flight of an
acoustic wave from arrangement of the transducer array 130 and the
subject 100 and can calculate deviation time of a reference.
[0059] Also, the computer 150 may determine a signal, which is
similar to the reflected signal 303, from the time-series echo
signal S2 (t) and may deviate a reference in such a manner that a
difference in the reception time of these signals becomes small.
Alternatively, the computer 150 may determine a signal, which is
similar to the reflected signal 305, from the time-series
photoacoustic signal S1 (t) and may deviate a reference in such a
manner that a difference in the reception time of these signals
becomes small. Here, the computer 150 can determine a similar
signal by means to use a cross-correlation such as template
matching.
[0060] Note that as a method for determining the reflected signal
303 from the time-series photoacoustic signal S1 (t), a signal
similar to an antiphase waveform of the interface signal 301 is
extracted. Also, by selecting the signal similar to the antiphase
waveform of the interface signal 301 from the time-series echo
signal S2 (t), it is also possible to extract the reflected signal
305.
[0061] Note that when deviation time of a reference is in a degree
which can be ignored in reduction of a component corresponding to a
reflected wave of a time-series photoacoustic signal, it is not
necessary to deviate the reference.
[0062] Also, the time point at which the acoustic wave 102a reaches
the surface 105 of the subject 100 may be set as t=0 in the
time-series echo signal S2 (t). That is, the computer 150 may
perform control in such a manner that acquisition of an echo signal
is started at the time point at which the acoustic wave 102a
reaches the surface 105 of the subject 100. For example, the
computer 150 can control the acquisition of an echo signal by
controlling driving of the transducer array 130 or housing, into a
memory, of an echo signal output from the transducer array 130.
[0063] Also, the computer 150 may delete, from the time-series echo
signal S2 (t), an echo signal acquired before the acoustic wave
102a reaches the surface 105 of the subject 100.
[0064] By the above method, it is possible to make the reception
time of the reflected waves identical.
[0065] <Weighting>
[0066] Incidentally, there is a case where intensity of the
photoacoustic wave 104a generated on the surface 105 of the subject
100 and that of the acoustic wave 103a transmitted from the
transducer array 130 are different from each other. In such a case,
it is preferable that a difference between the time-series
photoacoustic signal and the time-series echo signal is calculated
and the difference signal S3 (t) is acquired after weighting is
performed on the time-series photoacoustic signal S1 (t) or the
time-series echo signal S2 (t). By performing such weighting
processing, a component corresponding to a reflected wave in the
time-series photoacoustic signal S1 (t) can be reduced further
greatly.
[0067] The following equation is an equation expressing an example
of the described weighting processing.
S3(t)=S1(t)-a.times.S2(t) (1)
[0068] Here, a is a weighting coefficient. The weighting
coefficient a is a value which reduces a difference between an
amplitude value of a photoacoustic signal corresponding to a
reflected wave generated due to reflection of a photoacoustic wave
by a reflector and an amplitude value of an echo signal
corresponding to an echo generated due to reflection of the
transmitted acoustic wave by the same source of a reflected wave.
The weighting coefficient a can be arbitrarily set by a user or a
computer.
[0069] Signals having a high correlation with the time-series
photoacoustic signal S1 (t) and the time-series echo signal S2 (t)
are likely to be received signals of the reflected waves reflected
by a specific reflector. Thus, it is preferable that the computer
150 sets the weighting coefficient a with which a difference in
amplitude of the signals having a high correlation with the
time-series photoacoustic signal S1 (t) and the time-series echo
signal S2 (t) becomes small. Also, the computer 150 preferably sets
the weighting coefficient a with which amplitude of the signals
having a high correlation becomes identical.
[0070] In an example of the weighting expressed in the equation 1,
the weighting is performed by multiplying the time-series echo
signal S2 (t) by a weighting coefficient. Note that in the present
embodiment, the weighting may be performed by multiplying the
time-series photoacoustic signal S1 (t) by a weighting coefficient
or the weighting may be performed by multiplying both of the
time-series photoacoustic signal S1 (t) and time-series echo signal
S2 (t) by a weighting coefficient. However, to maintain
quantitativity of optical property information which can be
acquired from the time-series photoacoustic signal S1 (t), only the
time-series echo signal S2 (t) is preferably multiplied by a
weighting coefficient.
[0071] Also, it is preferable that the weighting processing is
performed after the above-described correction of a reference is
performed in order to make it easier to compare amplitude of the
signals.
[0072] Also, to selectively reduce a component corresponding to a
reflected wave from the time-series photoacoustic signal S1 (t), a
time-series echo signal on which envelope detection is performed
may be used as a mask of the time-series photoacoustic signal S1
(t). That is, the computer 150 may acquire a difference signal
between the time-series photoacoustic signal S1 (t) masked by the
time-series echo signal on which the envelope detection is
performed and the time-series echo signal S2 (t). Also, a
binarization signal, in which a case where an amplitude value of
the echo signal on which the envelope detection is performed is
equal to or higher than a predetermined threshold is one and the
rest of the cases is zero, may be used as a mask of the time-series
photoacoustic signal S1 (t).
[0073] Incidentally, in the present embodiment, the interface
signal 301 is reduced by acquiring a difference signal with the
reference signal 304. Note that by replacing the reduced interface
signal with the interface signal 301 stored in the storage unit
151, the computer 150 can restore the interface signal 301. Also,
by adding an antiphase signal of the reflected signal 304 to the
reduced interface signal, the computer 150 can restore the
interface signal 301.
[0074] (S400: Process for Acquiring Optical Property Information
from Difference Signal S3 (t))
[0075] The computer 150 acquires optical property information based
on the difference signal S3 (t) acquired in S300. As described,
since the difference signal S3 (t) is a signal in which a component
corresponding to a reflected wave of the photoacoustic wave is
reduced, a component corresponding to the reflected wave of the
photoacoustic wave is also reduced in the optical property
information acquired based on the difference signal S3 (t).
[0076] In the present process, the computer 150 can perform
reconstruction processing by using the difference signal S3 (t) and
can form initial sound pressure distribution as the optical
property information. As reconstruction algorithm, for example,
back projection in a time domain or a Fourier domain, delay-and-sum
(DAS), or the like generally used in tomography technique is used.
Also, when it is possible to spend a long period of time on
reconstruction, an image reconstruction method such as an inverse
problem analysis method by iteration processing can also be used.
Note that when the time-series photoacoustic signal S1 (t) is
acquired by serially scanning a transducer array focused in S100,
high dimensional initial sound pressure distribution can be formed
without the reconstruction. In this case, it is not necessary for
the computer 150 to perform the reconstruction processing.
[0077] Note that by acquiring light quantity distribution, in the
subject 100, of the light emitted to the subject 100 in S100 and
correcting the initial sound pressure distribution with the light
quantity distribution, the computer 150 can acquire absorption
coefficient distribution as the optical property information.
Moreover, the computer 150 can acquire, by using light of a
plurality of wavelengths, absorption coefficient distribution
corresponding to each of the wavelengths. By using the absorption
coefficient distribution, the computer 150 can acquire, as the
optical property information, a concentration of a substance
included in the subject 100.
[0078] Subsequently, the computer 150 acquires image data to be
displayed on the display unit 160 based on the acquired optical
property information. Then, the computer 150 displays the image
data on the display unit 160. A user can use the image data of the
optical property information displayed on the display unit 160 for
diagnosis and the like.
[0079] Note that in the present embodiment, image data is formed
from optical property information and is displayed on the display
unit 160, but information to be displayed on the display unit 160
is not limited thereto. For example, a value of optical property
information at a specific position may be displayed on the display
unit 160. In this case, a user may input a position by using the
input unit 170 and a value of optical property information at the
input position may be displayed on the display unit 160.
[0080] As described, according to the photoacoustic apparatus
according to the present embodiment, a component corresponding to a
reflected wave of the photoacoustic wave can be reduced from the
time-series photoacoustic signal. Thus, optical property
information in which decrease in quantitativity due to the
component corresponding to the reflected wave of the photoacoustic
wave is controlled can be acquired.
[0081] Note that the present embodiment can also be applied to a
case of reducing a component corresponding to a reflected wave of a
photoacoustic wave of a high sound pressure generated by direct
emission of light not only to the surface 105 of the subject 100
but also to a member like an acoustic lens.
[0082] In the following, each configuration of the photoacoustic
apparatus according to the present embodiment will be
described.
[0083] (Subject 100 and Optical Absorber 101)
[0084] These are not what configures a part of the photoacoustic
apparatus of the present invention but will be described in the
following. The photoacoustic apparatus of the present invention has
been made mainly for a diagnosis of a malignant tumor, a blood
vessel disease, or the like of a human or an animal, a follow-up of
a chemical treatment, or the like. Thus, as a subject, a living
body, specifically an object region of diagnosis, such as a breast,
a neck, or a stomach of a human body or an animal is assumed.
[0085] Also, an optical absorber inside the subject is what having
a relatively high absorption coefficient inside the subject. For
example, when a human body is a measurement object, a malignant
tumor, which includes a great amount of oxyhemoglobin,
deoxyhemoglobin, or methemoglobin or a great number of blood
vessels or new blood vessels including a great amount thereof,
becomes an object of the optical absorber. In addition, a plaque on
a carotid artery wall or the like also becomes the object.
[0086] (Light Source 110)
[0087] A light source is preferably a pulsed light source which can
generate pulsed light of an order of a several nano seconds to a
several micro seconds. Specifically, in order to generate a
photoacoustic wave effectively, a pulse width around ten nano
seconds is used. As the light source, a light emitting diode or the
like can be used instead of a laser. As the laser, various lasers
such as a solid-state laser, a gas laser, a dye laser, and a
semiconductor laser can be used. A wavelength of a light source to
be used is preferably a wavelength with which light is propagated
inside the subject. Specifically, when the subject is a living
body, the wavelength is 500 nm to 1200 nm.
[0088] (Optical System 120)
[0089] The optical system 120 is a member to lead, to the subject
100, light emitted from a light source while making the light into
an intended light distribution shape. The optical system 120
includes an optical part such as a lens or a mirror, an optical
waveguide such as an optical fiber, and the like. For example, an
optical part is a mirror to reflect light, a lens to collect and
increase light and to change a shape thereof, a diffuser panel to
diffuse light, or the like. Any kind of optical system 120 can be
used as long as the light emitted from the light source is emitted
to a subject in an intended shape. Note that it is preferable that
light is expanded to an area of a certain degree instead of being
collected by a lens in terms of safety to a living body and of a
wider diagnosis area. Also, to make it easier to transmit an
acoustic wave to an area to which light is emitted, the optical
system 120 is configured in such a manner as to light directly
below the transducer array 130.
[0090] (Transducer Array 130)
[0091] As a transducer used for the transducer array 130, any
transducer such as what uses a piezoelectric phenomenon, optical
resonance, a change in capacitance, or the like can be used as long
as an acoustic wave can be transmitted/received.
[0092] Note that by including a transmission/reception function of
an acoustic wave like the present embodiment, the transducer array
130 can easily receive an acoustic wave in the same area and can
easily conserve space, for example. However, functions of an
acoustic wave transmission unit, a photoacoustic wave reception
unit, and an echo reception unit may be respectively included in
different transducer arrays.
[0093] (Acoustic Matching Material 140)
[0094] The acoustic matching material 140 is not what configures a
part of the photoacoustic apparatus of the present invention but
will be described. The acoustic matching material 140 is a material
provided between the subject 100 and the transducer array 130 to
perform acoustic matching of the subject 100 and the transducer
array 130. As the acoustic matching material 140, for example, a
gel including water, oil, alcohol, or the like is used.
[0095] (Computer 150)
[0096] As the computer 150, a typical workstation or the like is
used. Correction processing, image reconstruction processing, or
the like is performed by software programmed in advance. Note that
in the present embodiment, various kinds of processing executed by
the computer 150 may be different apparatuses.
[0097] Also, instead of the software processing performed in a
workstation, a property such as acoustic impedance of a subject, or
optical property information can be acquired by hardware
processing.
[0098] A calculation unit 152 in the computer 150 can perform
predetermined processing on an electric signal output from the
transducer array 130.
[0099] The calculation unit 152 typically includes an element such
as a CPU, a GPU, or an A/D converter or a circuit such as an FPGA,
or an ASIC. Note that the calculation unit 152 does not necessarily
include only one element or circuit and may include a plurality of
elements or circuits. Also, processing performed by the calculation
unit 152 may be executed by any element or circuit.
[0100] Also, the calculation unit 152 can control an operation of
each configuration of the photoacoustic apparatus. For example, the
calculation unit 152 can control time point for emitting pulsed
light generated in the light source and can control time point for
transmitting/receiving an electric signal with the pulsed light as
a trigger signal. By controlling a transmission phase of each
transducer in the transducer array 130, the calculation unit 152
can arbitrarily control a wave front of the acoustic wave
transmitted by the transducer array 130.
[0101] Also, the storage unit 151 in the computer 150 typically
includes a storage medium such as a ROM, a RAM, or a hard disk.
Note that the storage unit 151 does not necessarily include only
one storage medium and may include a plurality of storage
media.
[0102] Also, it is preferable that the computer 150 can perform
pipeline processing of a plurality of signals simultaneously.
Accordingly, a period of time before the optical property
information is acquired can be reduced.
[0103] Note that processing performed by the computer 150 can be
stored in the storage unit 151 as a program to be executed by the
calculation unit 152. The storage unit 151 into which the program
is stored is a non-transitory storage medium.
[0104] (Display Unit 160)
[0105] The display unit 160 is an apparatus to display optical
property information output from a signal processing apparatus. As
the display unit 160, any type of display such as a liquid crystal
display, a plasma display, an organic electroluminescence display,
or an FED can be employed. Note that the display unit 160 may be
provided separately from the photoacoustic apparatus of the present
invention.
[0106] (Input Unit 170)
[0107] The input unit 170 is a member with which a user can specify
information in order to input the information into the computer
150. As the input unit 170, a keyboard, a mouse, a touch panel, a
dial, a button, or the like can be used. When a touch panel is
employed as the input unit 170, the display unit 160 may double as
the input unit 170.
Second Embodiment
[0108] In the second embodiment, echo sound pressure distribution
is acquired from a time-series echo signal and initial sound
pressure distribution is acquired from a time-series photoacoustic
signal. Also, difference distribution between the echo sound
pressure distribution and the initial sound pressure distribution
is acquired. In the difference distribution acquired in the present
embodiment, compared to the initial sound pressure distribution
acquired from the time-series photoacoustic signal, a component
corresponding to a reflected wave of a photoacoustic wave is
reduced. In the following, the present embodiment will be described
with reference to an apparatus similar to the photoacoustic
apparatus according to the first embodiment.
[0109] An operation method of the photoacoustic apparatus according
to the present embodiment will be described with reference to FIG.
4. Note that in a flow illustrated in FIG. 4, in respect to
processing similar to the processing illustrated in FIG. 2, the
same reference sign is assigned and detail description will not be
repeated.
[0110] First, in the present embodiment, processes S100 and S200
are performed and a time-series photoacoustic signal S1 (t) and a
time-series echo signal S2 (t) are acquired.
[0111] (S500: Process for Acquiring Initial Sound Pressure
Distribution Based on Time-Series Photoacoustic Signal)
[0112] Subsequently, based on the time-series photoacoustic signal
S1 (t), a computer 150 acquires initial sound pressure distribution
P1 (r) which is an example of optical property information. Here,
the computer 150 acquires the initial sound pressure distribution
P1 (r) from the time-series photoacoustic signal S1 (t) by a method
for acquiring optical property information from a difference signal
S3 (t), the method being described in S400.
[0113] FIG. 5A is a view illustrating an example of the initial
sound pressure distribution P1 (r) acquired from the time-series
photoacoustic signal S1 (t). A vertical axis indicates a depth of a
subject 100 and the depth of the subject 100 becomes larger in a
downward direction. Note that in the present embodiment, light is
emitted from an upside of the drawing and a photoacoustic wave is
received in the upside of the drawing.
[0114] An area with high contrast (white area) which is in a
shallow position in FIG. 5A illustrates initial sound pressure
distribution 401 indicating a surface 105 of the subject 100 to
which light is directly emitted, and in a deep part thereof,
initial sound pressure distribution 402 indicating an optical
absorber 101 is illustrated. In a further deeper part, initial
sound pressure distribution 403 indicating a virtual image formed
from a received signal of a reflected wave 104c is illustrated.
[0115] (S600: Process for Acquiring Echo Sound Pressure
Distribution Based on Time-Series Echo Signal)
[0116] Subsequently, the computer 150 acquires echo sound pressure
distribution P2 (r) based on the time-series echo signal S2
(t).
[0117] The computer 150 according to the present embodiment
acquires the echo sound pressure distribution P2 (r) in such a
manner that a position of the initial sound pressure distribution
403 indicating a virtual image in FIG. 5A and a position of the
echo sound pressure distribution P2 (r) acquired from the
time-series echo signal S2 (t) become identical. That is, by using
an echo signal corresponding to reception time of a photoacoustic
signal used to acquire an initial sound pressure in a specific
minimum unit, an echo sound pressure in a specific minimum unit is
acquired. For example, the computer 150 acquires the echo sound
pressure distribution P2 (r) from the time-series echo signal S2
(t) on the assumption that an echo is generated in the subject 100
simultaneously when an acoustic wave 102a reaches the surface 105
of the subject 100. That is, in consideration of propagation time
from time when the acoustic wave 102a reaches the surface 105 of
the subject 100 to time when an echo reaches a transducer array
130, the echo sound pressure in each minimum unit is acquired from
the time-series echo signal. Accordingly, it is possible to make a
coordinate in the initial sound pressure distribution P1 (r), at
which coordinate an initial sound pressure corresponding to a
reflected wave 104b appears, and a coordinate in the echo sound
pressure distribution P2 (r), at which coordinate an echo sound
pressure corresponding to an echo 102b appears, identical.
[0118] On the other hand, generally, in a case of acquiring a B
mode image from a time-series echo signal, the B mode image is
acquired in consideration of propagation time in each minimum unit
of when transmission/reception is performed between the transducer
array 130 and a position in a minimum unit to be imaged. However,
the B mode image acquired by this method and the initial sound
pressure distribution 403 indicating a virtual image in FIG. 5A are
not identical, and thus, even when a difference therebetween is
acquired, there is not much effect to reduce a reflected wave
component of the time-series photoacoustic signal.
[0119] FIG. 5B is a view illustrating the echo sound pressure
distribution P2 (r) acquired from the time-series echo signal S2
(t) by a method corresponding to the present embodiment. An area
with high contrast (white area) in a shallow position of FIG. 5B is
echo sound pressure distribution 404 indicating the surface 105 of
the subject 100, and in a deep part thereof, echo sound pressure
distribution 406 indicating the optical absorber 101 is
illustrated. Note that in the present embodiment, an acoustic wave
is transmitted from an upside in the drawing and an echo is
received in the upside in the drawing.
[0120] When FIGS. 5A and 5B are compared, it can be understood that
the initial sound pressure distribution 403 indicating the virtual
image in FIG. 5A and the echo sound pressure distribution 406
indicating the optical absorber 101 in FIG. 5B are identical. On
the other hand, strong echo sound pressure distribution is not seen
in an area 405 in which the initial sound pressure distribution 402
indicating the optical absorber 101 has appeared in FIG. 5A. That
is, in the area 405, there is no echo sound pressure distribution
which is identical to the initial sound pressure distribution 402
indicating the optical absorber 101.
[0121] On the other hand, a B mode image acquired from the
time-series echo signal S2 (t) by a general acquiring method of a B
mode image is illustrated in FIG. 5C as a comparison example. An
area with high contrast (white area) in a shallow position in FIG.
5C is a B mode image 407 indicating the surface 105 of the subject
100 and in a deep part thereof, a B mode image 408 indicating the
optical absorber 101 is illustrated.
[0122] When FIGS. 5A and 5C are compared, in an area 409 in which
the initial sound pressure distribution 403 indicating the virtual
image has appeared in FIG. 5A, no B mode image is seen. That is, in
the area 409, there is not a B mode image identical to the initial
sound pressure distribution 403 indicating the virtual image.
[0123] (S700: Process for Acquiring Differential Sound Voltage
Distribution Between Initial Sound Pressure Distribution and Echo
Sound Pressure Distribution)
[0124] Subsequently, the computer 150 acquires difference
distribution P3 (r) between the initial sound pressure distribution
P1 (r) acquired in S500 and the echo sound pressure distribution P2
(r) acquired in S600.
[0125] <Weighting>
[0126] Incidentally, there is a case where intensity of the
photoacoustic wave 104b generated on the surface 105 of the subject
100 and that of the acoustic wave 102a transmitted from the
transducer array 130 are different from each other. In such a case,
it is preferable that a difference between the initial sound
pressure distribution and the echo sound pressure distribution is
calculated and the difference distribution P3 (r) is acquired after
weighting is performed on the initial sound pressure distribution
P1 (r) or the echo sound pressure distribution P2 (r). By
performing such weighting processing, a component corresponding to
a reflected wave in the initial sound pressure distribution P1 (r)
can be greatly reduced.
[0127] The following equation is an equation expressing an example
of the described weighting processing.
P3(r)=P1(r)-A.times.P2(r) (2)
[0128] Here, A is a weighting coefficient. The weighting
coefficient A can be arbitrarily set by a user or a computer to
reduce a difference between an initial sound pressure value
corresponding to a reflected wave generated due to reflection of a
photoacoustic wave by a reflector and an echo sound pressure value
at the same position.
[0129] For example, a user specifies an arbitrary area with the
input unit 170 in respect to the initial sound pressure
distribution P1 (r) or the echo sound pressure distribution P2 (r)
displayed on the display unit 160. Subsequently, the computer 150
can set, as the weighting coefficient A, a value with which a
difference between the initial sound pressure and the echo sound
pressure in the area specified by the user becomes small. Also, the
computer 150 can set, as the weighting coefficient A, a value with
which a difference between an average initial sound pressure value
in the specified area and an average echo sound pressure value in
the specified area becomes small.
[0130] Also, it may be possible for a user to set, with the input
unit 170, a weighting coefficient while checking the difference
distribution displayed on the display unit 160. Thus, the display
unit 160 preferably includes the input unit 170 with which a
weighting coefficient can be input. For example, the display unit
160 may be a touch panel which doubles as the input unit 170.
[0131] Note that in an example of the weighting expressed in the
equation 2, the weighting is performed by multiplying the echo
sound pressure distribution P2 (r) by a weighting coefficient. Note
that in the present embodiment, the weighting may be performed by
multiplying the initial sound pressure distribution P1 (r) by a
weighting coefficient or the weighting may be performed by
multiplying both of the initial sound pressure distribution P1 (r)
and echo sound pressure distribution P2 (r) by a weighting
coefficient. However, to maintain quantitativity of optical
property information acquired from the initial sound pressure
distribution P1 (r), only the echo sound pressure distribution P2
(r) is preferably multiplied by a weighting coefficient.
[0132] In the present embodiment, the echo sound pressure
distribution P2 (r) is multiplied by the weighting coefficient
a=0.4 and the difference distribution P3 (r) is acquired. An
example of difference distribution acquired as a result of such
processing is illustrated in FIG. 5D. In FIG. 5D, difference
distribution 410 indicating the surface 105 of the subject 100,
difference distribution 411 indicating the optical absorber 101,
and an area 412 in which a virtual image has appeared in FIG. 5A
are illustrated. As it can be seen from FIG. 5D, the initial sound
pressure distribution 413 indicating the virtual image is reduced
in the area 412 and cannot be seen. On the other hand, the optical
absorber 101 is not reduced greatly and can be seen as the
difference distribution 411. That is, according to the present
embodiment, initial sound pressure distribution indicating a
virtual image, which is by a reflected wave component of the
photoacoustic wave, can be reduced selectively.
[0133] <Deviation Correction of Reception Time>
[0134] Incidentally, when signals do not appear at the same time
due to positional deviation or the like of a subject, an effect to
reduce a component corresponding to a reflected wave of the
photoacoustic wave may be deteriorated in a method described in the
first embodiment. Thus, in the second embodiment, the initial sound
pressure distribution and the echo sound pressure distribution may
be acquired in a minimum unit larger than a product of reception
sampling time and a speed of sound in the subject. That is, an
initial sound pressure and an echo sound pressure in a certain
minimum unit may be acquired from a plurality of pieces of sampling
data. Accordingly, components corresponding to a photoacoustic wave
and an echo, which are generated by the same reflector respectively
in an initial sound pressure and an echo sound pressure in a
certain minimum unit, become more likely to be included. Thus, even
when a reflected wave of the photoacoustic wave and an echo do not
appear at the same time, a component corresponding to the reflected
wave of the photoacoustic wave can be reduced by acquiring
difference distribution between the initial sound pressure
distribution and the echo sound pressure distribution. Note that
when reception sampling time of the photoacoustic signal and that
of the echo signal are different from each other, it is preferable
to acquire the initial sound pressure distribution and the echo
sound pressure distribution by a product of longer reception
sampling time and a speed of sound in the subject.
[0135] Note that the computer 150 acquires light quantity
distribution, of light emitted to the subject 100 in S100, in the
subject 100 and corrects difference distribution by the light
quantity distribution, and thus, absorption coefficient
distribution as optical property information can be acquired. Also,
by using light of a plurality of wavelengths, the computer 150 can
acquire absorption coefficient distribution corresponding to each
wavelength. By using the absorption coefficient distribution, the
computer 150 can acquire, as the optical property information, a
concentration of a substance included in the subject 100.
[0136] As described, in the difference distribution acquired in the
present embodiment, a component corresponding to a reflected wave
of the photoacoustic wave is reduced compared to the initial sound
pressure distribution acquired from the time-series photoacoustic
signal. That is, according to the photoacoustic apparatus according
to the present embodiment, optical property information, in which
decrease in quantitativity due to a component corresponding to a
reflected wave of the photoacoustic wave is controlled, can be
acquired.
OTHER EMBODIMENTS
[0137] Embodiments of the present invention can also be realized by
a computer of a system or apparatus that reads out and executes
computer executable instructions recorded on a storage medium
(e.g., non-transitory computer-readable storage medium) to perform
the functions of one or more of the above-described embodiment(s)
of the present invention, and by a method performed by the computer
of the system or apparatus by, for example, reading out and
executing the computer executable instructions from the storage
medium to perform the functions of one or more of the
above-described embodiment(s). The computer may comprise one or
more of a central processing unit (CPU), micro processing unit
(MPU), or other circuitry, and may include a network of separate
computers or separate computer processors. The computer executable
instructions may be provided to the computer, for example, from a
network or the storage medium. The storage medium may include, for
example, one or more of a hard disk, a random-access memory (RAM),
a read only memory (ROM), a storage of distributed computing
systems, an optical disk (such as a compact disc (CD), digital
versatile disc (DVD), or Blu-ray Disc (BD).TM.), a flash memory
device, a memory card, and the like.
[0138] While the present invention has been described with
reference to exemplary embodiments, it is to be understood that the
invention is not limited to the disclosed exemplary embodiments.
The scope of the following claims is to be accorded the broadest
interpretation so as to encompass all such modifications and
equivalent structures and functions.
* * * * *