[0001] The present invention relates to an artificial lung device configured to remove
carbon dioxide contained in blood and add oxygen to the blood.
Background Art
[0002] First, first and second disclosures will be described. In a surgical operation, such as
a heart surgical operation, which is performed after the movement of the heart of a patient is
stopped, an artificial heart-lung circuit is used as a substitute for the functions of the stopped
heart and the lung. An artificial lung device in the artificial heart-lung circuit plays a role of the
lung. As such artificial lung device, an artificial lung device disclosed in PTL 1 is known, for
example.
[0003] The artificial lung device disclosed in PTL 1 includes a housing and a gas exchanger.
The housing is formed in a cylindrical shape, and both end portions of the housing are closed by
headers. The housing is arranged so as to stand such that the headers are located at upper and
lower sides, and the gas exchanger is accommodated in the housing. The gas exchanger is
constituted by a bundle and a tubular core and is configured such that the bundle is wound
around the tubular core. In such artificial lung device, an annular blood passage is formed
between the housing and the tubular core.
[0004] Moreover, a diffusing portion is formed at an upper end portion of the tubular core.
Blood introduced to the tubular core is diffused to the blood passage by the diffusing portion.
The bundle wound around the tubular core is interposed in the blood passage. The bundle is
configured such that a plurality of hollow fibers are arranged in a band shape. Gaps are formed
among the adjacent hollow fibers, and the diffused blood flows through the gaps toward an outlet
port. Moreover, oxygen flows inside the hollow fibers. The hollow fibers remove carbon
dioxide from the blood having contacted the hollow fibers, and adds oxygen to the blood.
[0005] Next, a third disclosure will be described. In a surgical operation, such as a heart
surgical operation, which is performed after the movement of the heart of a patient is stopped, an
artificial heart-lung circuit is used as a substitute for the functions of the stopped heart and the
lung. An artificial lung in in the artificial heart-lung circuit plays a role of the lung. As such
artificial lung, an artificial lung disclosed in PTL 2 is known, for example.
[0006] The artificial lung disclosed in PTL 2 includes a housing and a gas exchanger. A
blood inlet port is formed at a bottom portion of the housing, and a blood outlet port is formed at
3
an outer peripheral surface of the housing. Moreover, a gas exchanger is accommodated in the
housing and adds oxygen to the blood flowing in the housing. Furthermore, a venous blood
tube and an artery tube are attached to the corresponding ports such that the blood flows in and
out from the artificial lung. In the artificial lung configured as above, the blood is introduced
from the vein tube through the blood inlet port into the housing. The introduced blood flows
through the gas exchanger in the housing and is discharged from the blood outlet port to the
artery tube. When the blood flows through the gas exchanger, oxygen is added to the blood.
[0007] Moreover, a fourth disclosure will be described. In a surgical operation, such as a
heart surgical operation, which is performed after the movement of the heart of a patient is
stopped, an artificial heart-lung circuit is used as a substitute for the functions of the stopped
heart and the lung. An artificial lung device in the artificial heart-lung circuit plays a role of the
lung. As such artificial lung device, an artificial lung device disclosed in PTL 3 is known, for
example.
[0008] In the artificial lung device disclosed in PTL 3, a blood inlet is provided in a tubular
device casing so as to extend in an axial direction of the device casing. A heating fluid inflow
pipe which includes a heating fluid inlet and through which a heating fluid flows toward one side
in the axial direction of the device casing and a heating fluid outflow pipe which includes a
heating fluid outlet and through which the heating fluid flows toward the other side in the axial
direction of the device casing are provided so as to extend in the device casing. Moreover, a
blood outlet is provided at an end portion of the device casing which portion is located close to
the blood inlet. Furthermore, a gas exchanger including hollow fibers is provided in the device
casing. According to this configuration, blood enters into the device casing through the blood
inlet, and then, flows around the heating fluid inflow pipe and the heating fluid outflow pipe to
be heated by heat exchange. The heated blood flows around the hollow fibers of the gas
exchanger to be able to obtain oxygen and discharge carbon dioxide into the hollow fibers.
Citation List
Patent Literature
[0009] PTL I: Published Japanese Translation ofPCT Application No. 11-508476
PTL 2: Japanese Patent No. 5418274
PTL 3: Japanese Patent No. 5809438
Summary oflnvention
. Technical Problem
4
[0010] Regarding the first disclosure, the artificia1lung device disclosed in PTL 1 is a
so-called vertical artificial lung device. In addition to such artificial lung device, the following
artificial lung device has also been developed. To be specific, a horizontal artificial lung device
arranged such that a housing thereof is laid in a horizontal direction has also been developed.
In the horizontal artificial lung device, a gas exchanger is also directed in the horizontal direction
in the housing, and an annular blood passage extends in the horizontal direction. The blood
flows through the blood passage, and bubbles are carried together with the blood in some cases.
[00 11] Basically, such bubbles are absorbed by the hollow fibers when contacting the
hollow fibers, and most of the bubbles are removed. However, when a large amount of bubbles
are carried together with the blood, the hollow fibers may not adequately absorb the bubbles.
In such a case, the bubbles which were not absorbed flow toward a ceiling in the housing and are
accumulated in the vicinity of the ceiling. Then, if the bubbles are excessively accumulated,
the bubbles may be carried toward the outlet port by the flow of the blood.
[0012] An object of the present invention is to provide an artificial lung device capable of
removing bubbles carried by blood and preventing the bubbles from being excessively
accumulated.
[0013] Regarding the second disclosure, in conventional artificial lung devices such as the
artificial lung device disclosed in PTL 1, the blood flows through the blood passage of the gaps
in the bundle constituting the gas exchanger, and in some cases, the bubbles are carried together
with the blood. Basically, such bubbles are absorbed by the hollow fibers of the bundle when
contacting the hollow fibers, and most of the bobbles are removed. However, when a large
amount of bubbles are carried together with the blood, the bubbles may not be adequately
absorbed by the hollow fibers in a period in which the blood flows through the gas exchanger.
Then, when the bubbles which were not absorbed by the hollow fibers are excessively
accumulated, the bubbles may be carried toward the outlet port by the flow of the blood.
[0014] Another object of the present invention is to provide an artificial lung device capable
of preventing bubbles, carried by blood, from being excessively accumulated.
[0015] Regarding the third disclosure, in the artificial lung described in PTL 2, a suspending
portion is formed at an upper portion of the housing, and the artificial lung is used by being
suspended in such a manner that the suspending portion is hung on a suspending device or the
like. The artificial lung configured as above constitutes part of the artificial heart-lung circuit
and is used in such a manner that the vein tube and the artery tube attached to the corresponding
ports are connected to corresponding apparatuses. According to the artificial heart-lung circuit,
the blood flows in the circuit. Therefore, as a preparation in advance, the blood passage of the
5
circuit is filled with saline. Therefore, the blood of a patient is diluted by the saline. The
amount of blood differs person to person depending on the weight, physique, and the like of the
patient. When the amount of saline is large relative to the amount of blood, the blood is diluted,
and required blood component concentration of the blood cannot be maintained. Therefore, the
blood component needs to be compensated by blood transfusion. To reduce the amount of
blood used by the blood transfusion, the length of the blood passage in the artificial lung circuit
needs to be shortened as much as possible. For example, this can be realized by reducing the
lengths of the tubes.
[0016] On the other hand, the tubes become long due to the routing of the tubes
corresponding to an arrangement relation between the artificial lung and respective devices.
For example, when the blood inlet port is not directed to an apparatus to which the blood inlet
port is connected, but is directed in an opposite direction, the vein tube needs to be directed to
the apparatus by changing the direction of the vein tube, such as by bending the vein tube in a U
shape, and therefore, the vein tube increases in length by this bending. Regarding this, in PTL
2, the direction of the blood inlet port is changed by, for example, rotating the suspending portion
relative to the suspending device. With this, the vein tube does not have to be bent, and
therefore, the vein tube is shortened as much as possible.
[0017] Similarly, it is preferable that the artery tube be shortened as much as possible.
However, according to the artificial lung ofPTL 2, the following matters occur. To be specific,
in the artificial lung of PTL 2, the blood inlet port and the blood outlet port extend in respective
directions opposite to each other. Therefore, even when the artificial lung is rotated relative to
the suspending device, the two ports are never directed in the same direction. On this account,
when the device to which the blood inlet port is connected and the device to which the blood
outlet port is connected are arranged at the same side of the artificial lung, at least one of the tube
connected to the blood inlet port and the tube connected to the blood outlet port needs to be bent,
for example, and the bent tube increases in length. Moreover, when the degree of bending of
the tube is large, passage resistance becomes large at this bent portion. In this case, the blood
pressure in the tube may increase, and the bloodstream in the tube may stop. Therefore, the
routing of the two tubes needs to be devised.
[0018] Yet another object of the present invention is to provide an artificial lung device
capable of facilitating routing of tubes by which a blood inflow port and a blood outflow port are
connected to corresponding apparatuses.
[0019] Regarding the fourth disclosure, the artificial lung device ofPTL 3 is configured
such that: the blood outlet is provided at an end portion of the device casing which portion is
6
located close to the blood inlet; and the blood having flowed into the device casing flows radially
and spreads concentrically in the casing and flows out from the blood outlet. Therefore, a time
period in which the blood and the heat exchanger contact each other is short, and part of the
blood having entered into the device casing through the blood inlet is not adequately subjected to
the heat exchange and flows out from the blood outlet. On this account, the blood may not be
adequately heated or cooled as a whole.
[0020] Still another object of the present invention is to provide an artificial lung device
capable of adequately heating blood.
Solution to Problem
[0021] The frrst disclosure will be described. An artificial lung device according to the
present invention includes: a housing including a blood inflow port and a blood outflow port and
arranged such that a center axis of the housing is directed in a lateral direction; a gas exchanger
arranged in the housing and configured to perform gas exchange with respect to blood while the
blood flows from the blood inflow port to the blood outflow port; a filter structure arranged
around the gas exchanger; an opposing wall arranged so as to be opposed to a surface of the gas
exchanger; and a space constituted by the opposing wall and/or the filter structure. The
opposing wall includes an inclined surface inclined toward the gas exchanger, and/or the filter
structure includes an inclined surface inclined toward the gas exchanger.
[0022] According to this configuration, the bubbles which flowed through the gas
exchanger but were not absorbed flow to the gas exchanger again in the artificial lung device.
Therefore, a larger amount of bubbles can be absorbed by the gas exchanger. On this account,
the bubbles can be removed in the housing and can be prevented from being excessively
accumulated in the housing.
[0023] Moreover, in the above artificial lung device, the gas exchanger may be formed in a
columnar shape such that a center axis of the gas exchanger is directed in the lateral direction in
the housing. The bubble guide portion may include a straightening surface provided so as to
cross a passage extending from the gas exchanger to the blood outflow port. The straightening
surface may be provided so as to be opposed to an outer peripheral surface of the gas exchanger
and surround the gas exchanger. The straightening surface may include a frrst straightening
surface provided at a relatively lower side and inclined such that a downstream portion of the
frrst straightening surface in a flow direction of the blood is located closer to the outer peripheral
surface of the gas exchanger than an upstream portion of the first straightening surface in the
flow direction of the blood and a second straightening surface provided at a relatively upper side
7
and located closer to the outer peripheral surface of the gas exchanger than the upstream portion
of the first straightening surface, the second straightening surface being inclined differently from
the first straightening surface.
[0024] ln this case, the bubbles received by the upstream portion of the first straightening
surface located at a lower portion of the bubble guide portion approach the outer peripheral
surface of the gas exchanger as the bubbles flow toward the downstream portion along the flow
of the blood. Moreover, the bubbles received by the first straightening surface approach the
outer peripheral surface of the gas exchanger as the bubbles flows upward in the blood toward
the second straightening surface located at the upper side. Therefore, according to the above
configuration, the bubbles can flow out from the gas exchanger, reach the bubble guide portion,
and be guided to the gas exchanger again.
[0025] Moreover, a filter may be provided at the straightening surface.
[0026] According to this configuration, foreign matters can be removed from the blood
received by the straightening surface.
[0027] Moreover, in the above artificial lung device, an opening may be formed at the first
straightening surface, and a filter may be provided at the opening.
[0028] According to this configuration, foreign matters can be removed from the blood
flowing out from the artificial lung device through the blood outflow port. Moreover, since the
filter is provided at not the second straightening surface at the upper side where the bubbles tend
to be accumulated but the first straightening surface at the lower side, the bubbles can be
prevented from passing through the filter.
[0029] Moreover, in the above artificial lung device, the second straightening surface may
be located so as to be spaced apart from the outer peripheral surface of the gas exchanger by a
predetermined distance, and a bubble storing portion may be formed between the second
straightening surface and the outer peripheral surface of the gas exchanger.
[0030] According to this configuration, the bubbles flowing upward along the straightening
surface can be brought into contact with the outer peripheral surface of the gas exchanger before
reaching the second straightening surface. ln addition, when a large amount of bubbles flow,
the bubbles can be temporarily stored in the bubble storing portion that is a space between the
second straightening surface and the outer peripheral surface of the gas exchanger. Moreover,
when a certain amount of bubbles are accumulated in the bubble storing portion, the bubbles can
be drawn into the hollow fiber membrane to be removed.
[003 I] Moreover, in the above artificial lung device, at least the second straightening
surface of the straightening surface may be constituted by an inner wall surface of the housing.
8
[0032] According to this configuration, positioning accuracy between the second
straightening surface and the outer peripheral surface of the gas exchanger at the time of
assembling can be improved.
[0033] Moreover, in the above artificial lung device, a filter may be provided at the blood
outflow port.
[0034] According to this configuration, foreign matters can be removed from the blood at
the blood outflow port.
[0035] Moreover, in the above artificial lung device, the filter may be formed in a columnar
shape such that a dimension of the filter in a flow direction of the blood in the blood outflow port
is larger than an inner diameter of the blood outflow port.
[0036] According to this configuration, since the volume of the filter can be increased,
foreign matters can be more surely removed from the blood.
[003 7] Moreover, the above artificial lung device may further include a bubble trap portion
provided downstream of the bubble storing portion.
[0038] According to this configuration, for example, even when the bubbles have passed
through the filter, such bubbles can be trapped by the bubble storing portion again.
[0039] Moreover, in the above artificial lung device, the bubble trap portion may include an
air vent port.
[0040] According to this configuration, the bubbles accumulated in the bubble storing
portion can be discharged through the air vent port to the outside.
[0041] The artificial lung device according to the present invention includes: a housing
formed in a tubular shape including both end portions that are closed, the housing including a
blood inflow port and a blood outflow port and arranged such that a center axis of the housing is
directed in a lateral direction; a gas exchanger arranged in the housing and configured to perform
gas exchange with respect to blood while the blood flows from the blood inflow port to the blood
outflow port; a straightening frame including a filter and provided around the gas exchanger; and
a bubble storing portion provided between the straightening frame and the gas exchanger. The
bubble storing portion is located at an upper side of the housing and faces the gas exchanger.
[0042] According to this configuration, the bubble storing portion is located at the upper
side of the housing and faces the gas exchanger so as to be adjacent to the gas exchanger.
Therefore, when the bubbles are accumulated in the space in the bubble storing portion, the
bubbles can be brought into contact with the gas exchanger and can be taken in the gas
exchanger. With this, the bubbles can be prevented from being excessively accumulated in the
bubble storing portion.
9
[0043] Moreover, in the above artificial lung device, the bubble storing portion may include
an inner peripheral surface of the straightening frame and an outer peripheral surface of the gas
exchanger.
[0044] Moreover, in the above artificial lung device, the straightening frame may include an
inclined straightening surface located close to the gas exchanger.
[0045] According to this configuration, the bubbles in the bubble storing portion can be
smoothly guided to and taken in the gas exchanger by the inclined straightening surface included
in the straightening frame.
[0046] The second disclosure will be described. An artificial lung device according to the
present invention includes: a housing including a blood inflow port and a blood outflow port; a
gas exchanger arranged in the housing and configured to perform gas exchange with respect to
blood while the blood flows from the blood inflow port to the blood outflow port; and an
opposing wall arranged so as to be opposed to a surface of the gas exchanger and forming a
space between the opposing wall and the surfuce of the gas exchanger. The surfuce of the gas
exchanger and the opposing wall constitute a bubble guide portion by which bubbles having
flowed through the gas exchanger are guided to the gas exchanger. A separation dimension
between the surface of the gas exchanger and the opposing wall gradually decreases to approach
zero toward a vertically upper side or toward a downstream side in a flow direction of the blood
in the space.
[0047] According to this configuration, since the bubbles which flowed through the gas
exchanger in the artificial lung device but were not absorbed flows toward the gas exchanger
again, a larger amount of bubbles can be absorbed by the gas exchanger. In addition, the
surface of the gas exchanger and the opposing wall which constitute the bubble guide portion
contact each other at the vertically upper side or the downstream side (the separation dimension
becomes zero) or do not contact each other but gradually get close to each other (the separation
dimension approaches zero). Therefore, the bubbles having reached the bubble guide portion
can be more surely guided to the gas exchanger again, and the bubbles can be prevented from
being excessively accumulated in the housing.
[0048] Moreover, in the above artificial lung device, the filter configured to remove foreign
matters in the blood may be provided so as to cross a passage such that part of the surface ofthe
filter contacts the surface of the gas exchanger, the passage being a passage through which the
blood having flowed through the gas exchanger flows toward the blood outflow port. The filter
may constitute the opposing wall.
[0049] According to this configuration, a dedicated opposing wall does not have to be
10
provided, and the filter configured to remove foreign matters in the blood can serve as the
opposing wall. Moreover, since the filter is provided downstream of the gas exchanger in the
flow direction of the blood, the bubbles which remain although having flowed through the gas
exchanger can be surely collected and guided to the gas exchanger again.
[0050] Moreover, in the above artificial lung device, the gas exchanger may be provided
such that part of the surface of the gas exchanger contacts an inner wall surface of the housing,
and the inner wall surface of the housing may constitute the opposing wall.
[0051] According to this configuration, a dedicated opposing wall does not have to be
provided, and the housing originally included can serve as the opposing wall.
[0052] Moreover, the above artificial lung device may further include a heat exchanger
arranged in the housing and configured to adjust a temperature of the blood having flowed into
the heat exchanger through the blood inflow port and deliver to the gas exchanger the blood
having been adjusted in temperature. The gas exchanger may be formed in a tubular shape
surrounding the heat exchanger. A tubular wall may be provided between the heat exchanger
and the gas exchanger so as to separate the heat exchanger and the gas exchanger from each
other. The bubble guide portion may be formed by an inner peripheral surface of the gas
exchanger and a portion of the tubular wall which portion is opposed to the inner peripheral
surface of the gas exchanger.
[0053] According to this configuration, when the gas exchanger is formed in a tubular shape
surrounding the heat exchanger, the bubble guide portion can be provided at the inner peripheral
surface side of the gas exchanger.
[0054] The third disclosure will be described. An artificial lung device of the present
invention includes: a gas exchanger configured to perform gas exchange with respect to blood
which has contacted the gas exchanger; and a housing including a hollow housing main body
accommodating the gas exchanger, a blood inflow port which is formed at the housing main
body and through which the blood flows into the housing main body for the gas exchange with
the gas exchanger, a cylindrical blood outflow port through which the blood in the housing main
body is discharged, and an attaching portion to which the blood outflow port is attached. A
base end-side portion of the blood outflow port is attached to the attaching portion such that the
blood outflow port is rotatable about an axis of the base end-side portion. The blood outflow
port is bent such that a tip end-side portion of the blood outflow port forms a predetermined
angle with respect to the axis of the base end-side portion.
[0055] According to the present invention, since the blood outflow port is bent and is
provided at the housing main body so as to be rotatable, the direction of the blood outflow port
11
can be changed by rotating the blood outflow port regardless of the directions of the housing
main body and the blood inflow port. With this, the arrangement position, direction, and the
like of the artificial lung device can be prevented from being restricted, and the routing of the
tubes connecting the blood inflow port, the blood outflow port, and apparatuses can be
facilitated.
[0056] Moreover, in the above artificial lung device, the attaching portion may be formed in
a substantially cylindrical shape. An inner peripheral surface of the attaching portion may
include an engaging portion. The base end-side portion of the blood outflow port may be
attached to the attaching portion. The base end-side portion of the blood outflow port may
include an engaged portion which is engaged with the engaging portion when the base end-side
portion of the blood outflow port is attached to the attaching portion.
[0057] The blood outflow port receives, from the blood flowing in or introduced to the
blood outflow port, a load acting in such a direction that the blood outflow port is detached from
the attaching portion. However, since the engaging portion and the engaged portion are
engaged with each other as in the above configuration, the blood outflow port can be prevented
from being easily detached from the attaching portion.
[0058] Moreover, in the above artificial lung device, one of the engaging portion and the
engaged portion may be constituted by a plurality of engagement pieces arranged so as to be
spaced apart from each other in a circumferential direction. Each of the engagement pieces
may be formed in a tapered shape that projects inward in a radial direction as the engagement
piece extends upward. The other of the engaging portion and the engaged portion may be
arranged so as to correspond to the engagement pieces, be formed so as to project outward in the
radial direction, and be engaged with the plurality of engagement pieces so as to be located
higher than the plurality of engagement pieces.
[0059] According to this configuration, when attaching the blood outflow port to the
attaching portion, the engaged portion can be guided by a plurality of engagement pieces formed
in a tapered shape. With this, the blood inflow port can be easily attached, and the artificial
lung device can be easily manufactured.
[0060] Moreover, the above artificial lung device may further include first and second
sealing members configured to seal between an outer peripheral surface of the base end-side
portion and an inner peripheral surface of the attaching portion. The first sealing member may
be arranged at a portion of an outer peripheral surface of the base end-side portion of the blood
outflow port which portion is closer to a base end of the blood outflow port than the second
sealing member. Compressibility of the second sealing member may be higher than
12
compressibility of tbe first sealing member.
[0061] In this case, the compressibility of the second sealing member is higher than that of
the first sealing member. Therefore, even if the blood leaks from the first sealing member, the
second sealing member can prevent the blood from leaking to the outside. Moreover, by
lowering the compressibility of the first sealing member, an increase in sliding resistance
generated when rotating the blood outflow port can be suppressed.
[0062] Moreover, in the above artificial lung device, the base end-side portion of the blood
inflow port may project from the housing main body toward one side in an upper-lower direction.
A tip end-side portion of the blood inflow port may be connected to the base end-side portion
through a bent portion and be inclined outward in a radial direction so as to be directed toward
one side in the upper-lower direction relative to the base end-side portion. The blood outflow
port may include a holding portion formed at the bent portion so as to project from the bent
portion toward one side in the upper-lower direction.
[0063] According to this configuration, the blood inflow port can be easily rotated by the
holding portion. Moreover, since the holding portion is formed so as to project, the holding
portion serves as a rib and can improve the rigidity of the blood inflow port. Furthermore,
when the artificial lung device falls in a state where the blood inflow port is located at the lower
side, the holding portion can be made to contact a floor or the like. With this, impact at the time
of the falling can be made to act in the axial direction of the base end-side portion. Since the
base end-side portion is formed along the axial direction, the base end-side portion has high
rigidity. Since the holding portion lands first at the time of the falling, the blood inflow port
can be prevented from breaking.
[0064] An artificial lung device of the present invention includes: a tubular housing
including both ends that are closed; a heat exchanger provided in the housing and configured to
perform heat exchange with respect to blood; a gas exchanger arranged around an axial direction
of the heat exchanger in the housing and configured to be in fluid communication with the heat
exchanger and perform gas exchange with respect to the blood; a heat medium partial chamber
which is arranged between the heat exchanger and the gas exchanger and around the axial
direction of the heat exchanger and through which a heat medium flowing in and out from the
heat exchanger flows; a blood inflow port provided at a first end side of the housing and
configured to be in fluid communication with the heat exchanger; a blood outflow port provided
at the housing and configured to be in fluid communication with the gas exchanger; a medium
inflow port and a medium outflow port which are provided at a second end side of the housing
and are in fluid communication with the heat medium partial chamber; and a bridge structure
13
forming a blood passage through which the blood flows in a radial direction from the heat
exchanger through a second end side of the heat medium partial chamber to the gas exchanger
and a medium passage through which the heat medium flows in the axial direction between the
medium inflow port and the heat medium partial chamber and between the medium outflow port
and the heat medium partial chamber.
[0065] According to the present invention, the blood flows into the blood inflow port
provided at the first end side of the housing, flows through the heat exchanger and the second
end side of the heat medium partial chamber, and flows through the blood passage to the gas
exchanger. With this, the heat exchange with respect to the blood is adequately performed.
Moreover, since the blood inflow port is provided at the first end side of the housing, and the
medium outflow port is provided at the second end side of the housing, sanitation is improved.
[0066] Moreover, an artificial lung device of the present invention includes: a tubular
housing including both ends that are closed, the housing including a blood inflow port, a blood
outflow port, a medium inflow port, and a medium outflow port; a heat exchanger configured to
be in fluid communication with the blood inflow port; and a gas exchanger arranged around the
heat exchanger and configured to be in fluid communication with the heat exchanger. The heat
exchanger includes: a blood chamber configured to be in fluid communication with the blood
inflow port and the blood outflow port and including an end portion; and a heat exchange portion
configured to in fluid communication with the medium inflow port and the medium outflow port,
a heat medium flowing through the heat exchange portion. The heat exchange portion includes
an extending portion arranged so as to extend beyond the end portion of the blood chamber in the
axial direction of the housing.
[0067] According to the present invention, the housing can be prevented from increasing in
size in the radial direction. With this, priming volume can be reduced.
Advantageous Effects oflnvention
[0068] According to the first disclosure, the present invention can provide an artificial lung
device configured to be able to prevent bubbles, carried by blood, form being excessively
accumulated. According to the second disclosure, the present invention can provide an
artificial lung device configured to be able to prevent bubbles, carried by blood, from being
excessively accumulated. According to the third disclosure, the present invention can facilitate
routing of tubes connecting a blood inflow port, a blood outflow port, and apparatuses.
According to the fuurth disclosure, the present invention can provide an artificial lung device
capable of adequately heating blood.
14
BriefDescription of Drawings
[0069] FIG. 1 is a front view showing appearance of an artificial lung device according to
the present embodiment of the first disclosure.
FIG. 2 is a front sectional view showing the artificial lung device of FIG. 1 in the
frrst disclosure.
FIG. 3 is a perspective view showing a straightening frame included in the artificial
lung device of FIG. 1 in the first disclosure.
FIG. 4 is a partial sectional view showing the straightening frame of the artificial
lung device according to Embodiment 2 of the frrst disclosure.
FIG. 5 is a partial sectional view showing a blood outflow port ofthe artificial lung
device according to Embodiment 3 of the first disclosure.
FIG. 6 is a front sectional view showing the artificial lung device according to
Embodiment l of the second disclosure.
FIG. 7 is a side sectional view taken along line II-II in the artificial lung device of
FIG. 6 in the second disclosure.
FIG. 8 is a side sectional view showing the artificial lung device according to
Embodiment 2 of the second disclosure.
FIG. 9 is a front sectional view showing the artificial lung device according to
Embodiment 3 of the second disclosure.
FIG. l 0 is a front sectional view showing the artificial lung device according to
Embodiment 4 of the second disclosure.
FIG. 11 is a front sectional view showing the artificial lung device according to
Embodiment 5 of the second disclosure.
FIG. 12 is a front sectional view showing the artificial lung device according to
Embodiment 6 of the second disclosure.
FIG. l3 is a front sectional view showing the artificial lung device according to
Embodiment 7 of the second disclosure.
FIG. 14 is a front sectional view showing the artificial lung device according to
Embodiment 8 of the second disclosure.
FIG. 15 is a front view showing the artificial lung device according to Modified
Example l of the second disclosure.
FIG. 16 is a front view showing the artificial lung device according to Modified
Example 2 of the second disclosure.
15
FIG 17 is a front view showing the artificial lung device according to Reference
Example 1 of the second disclosure.
FIG 18 is a front view showing appearance of the artificial lung device of the
present embodiment of the third disclosure.
FIG 19 is a sectional view showing the artificial lung device ofFICi 18 in the third
disclosure.
FIG 20 is an enlarged sectional view showing a region XI ofFICi 19 in the third
disclosure.
FIG 21 is a sectional view showing that a tip end of the blood outflow port is
directed toward a right side on the paper surface in the artificial lung device of FIG. 19 in the
third disclosure.
FIGS. 22A and 22B are front views showing that the blood outflow port of the
artificial lung device ofFICi 18 in the third disclosure is directed in various directions. FIG
22A is a front view showing that the tip end of the blood outflow port is directed toward a near
side. FIG 22B is a front view showing that the tip end of the blood outflow port is directed
toward a deep side.
FIG 23 is an enlarged sectional view showing the blood outflow port and its vicinity
in the artificial lung device according to another embodiment of the third disclosure.
FIG 24 is a front view showing appearance of the artificial lung device according to
one embodiment of the fourth disclosure of the present invention.
FIG 25 is a front sectional view showing the artificial lung device of FIG. 24 in the
fourth disclosure.
FIG 26 is a perspective sectional view showing part of the artificial lung device of
FIG. 24 in the fourth disclosure.
FIG 27 is a perspective view showing a middle tube of FIG. 25 in the fourth
disclosure.
FIG 28A is a front view showing the middle tube of FIG. 27 in the fourth disclosure.
FIG. 28B is a side view showing one side of the middle tube ofFICi 28A. FIG 28C is a side
view showing the other side of the middle tube ofFICi 28A.
FIG 29 is a perspective view showing an inner tube ofFICi 25 in the fourth
disclosure.
Description of Embodiments
[0070] Hereinafter, artificial lung devices according to embodiments of frrst to fourth
16
disclosures of the present invention will be described with reference to the drawings. It should
be noted that each artificial lung device described below is merely one embodiment of the
present invention, and the present invention is not limited to the embodiments. Additions,
deletions, and modifications may be made within the scope of the present invention.
[0071] Embodiment 1 to 3 of the first disclosure will be described.
[0072] Embodiment 1 of First Disclosure
FIG 1 is a front view showing appearance of an artificial lung device 1 of the
present embodiment. FIG 2 is a front sectional view showing the artificial lung device 1 of FIG
1. In a surgical operation performed after the movement of the heart of a patient is stopped, the
artificial lung device 1 shown in FIGS. 1 and 2 is used as a substitute for the function of the lung
of the patient. Therefore, the artificial lung device 1 has a gas exchange function of removing
carbon dioxide contained in blood of the patient and adding oxygen to the blood; and a heat
exchange function of adjusting the temperature of the blood. The artificial lung device 1
having such functions is of a so-called horizontal type and includes a housing 2, an inner tube 3,
and a middle tube 4.
[0073] The housing 2 is formed in a substantially cylindrical shape including both end
portions that are closed. The housing 2 includes an internal space 2a (see FIG 2)
accommodating the inner tube 3 and the middle tube 4. Specifically, the housing 2 includes a
housing main body 11, a suspending portion 13, and two cap portions 14 and 15.
[0074] The housing main body 11 is formed in a substantially cylindrical shape, and the
suspending portion 13 is provided at an outer peripheral surface of an upper portion of the
housing main body 11. The suspending portion 13 is arranged at a middle portion of the
housing main body 11 which portion is located at a middle position in a direction along an axis
11a of the housing main body 11. The suspending portion 13 extends in a radially outward
direction from the outer peripheral surface of the upper portion of the housing main body 11.
The suspending portion 13 is formed in, for example, a substantially columnar shape and is
suspended in such a manner that a tip end-side portion thereof is attached to an external
suspending device (not shown). Therefore, the housing main body 11 can be suspended
through the suspending portion 13, and the axis 11a of the suspended housing main body 11
extends in a horizontal direction.
[0075] The housing main body 11 includes opening end portions at both sides in the
direction along the axis 11a. The opening end portion at one side (left side in FIG 2) is closed
by the cap portion 14, and the opening end portion at the other side (right side in FIG 2) is
closed by the cap portion 15. Each of the cap portions 14 and 15 is formed in a substantially
17
circular plate shape. It should be noted that in the following description, for convenience of
explanation, regarding the direction along the axis 11a of the housing main body 11, a side where
the cap portion 14 is located is referred to as a left side, and a side where the cap portion 15 is
located is referred to as a right side.
[0076] As shown in FIG. 1, a gas supply port 18 is formed at the cap portion 14. The gas
supply port 18 is formed in a substantially cylindrical shape and projects to the left side in the
direction along the axis lla from the vicinity of an outer peripheral edge of the cap portion 14.
The gas supply port 18 is connected to an external gas supply device (not shown) through a gas
supply tube. Oxygen-containing gas supplied from the gas supply device is introduced through
the gas supply port 18 into the housing 2.
[0077] A gas discharge port 19 is formed at the cap portion 15. The gas discharge port 19
is formed in a substantially cylindrical shape and projects to the right side in the direction along
the axis 11a from the vicinity of an outer peripheral edge of the cap portion 15. The gas
discharge port 19 is connected to the external gas supply device through a gas discharge tube.
The gas supplied through the gas supply port 18 into the housing 2 is discharged through the gas
discharge port 19 and is returned to the gas supply device.
[0078] A blood inflow port 16 is formed in the vicinity of a central axis (axis which
substantially coincides with the axis lla of the housing main body 11) of the cap portion 14.
The blood inflow port 16 is formed in a substantially cylindrical shape and projects from a lower
side of the central axis of the cap portion 14 in a left and obliquely downward direction. A
venous blood tube (not shown) is connected to the blood inflow port 16, and venous blood is
introduced through the venous blood tube and the blood inflow port 16 into the housing main
body 11.
[0079] A blood outflow port 17 is formed at a position of a lower portion (portion opposite
to the suspending portion 13) of the outer peripheral surface ofthe housing main body 11 which
position is located at the left side of a center of the artificial lung device 1 in the direction along
the axis lla. More specifically, the blood outflow port 17 includes a port attaching portion 17a
and a port main body portion 17b. The port attaching portion 17a is formed in a substantially
cylindrical shape. The port attaching portion 17a is provided at the lower portion of the outer
peripheral surface of the housing main body 11 and projects downward. The port main body
portion 17b is inserted into the port attaching portion 17a from a lower side. The port main
body portion 17b is formed in a substantially cylindrical shape. The port main body portion
17b projects downward from a lower end of the port attaching portion 17a and is bent in an
obliquely downward direction at a tip side of the lower end of the port attaching portion 17a.
18
An arterial blood tube (not shown) is connected to the blood outflow port 17 (port main body
portion 17b ). The arterial blood generated in the artificial lung device I is delivered through
the arterial blood tube to an outside.
[0080] A medium inflow port 20 and a medium outflow port 21 are provided at the cap
portion 15. The medium inflow port 20 and the medium outflow port 21 are arranged so as to
sandwich a central axis of the cap portion 15 and be spaced apart from each other in an
upper-lower direction. The two ports 20 and 21 do not necessarily have to be spaced apart from
each other in the upper-lower direction and may be arranged so as to be spaced apart from each
other in a left-right direction. Each of the two ports 20 and 21 is formed in a substantially
cylindrical shape and projects from the cap portion 15 toward the right side in the direction along
the axis lla. The medium inflow port 20 is connected to a medium supply tube (not shown),
and a heat medium, such as hot water or cold water, from the medium supply tube is introduced
through the medium inflow port 20 into the housing 2. The medium outflow port 21 is
connected to a medium discharge tube (not shown), and the heat medium in the housing 2 is
discharged through the medium outflow port 21 and the medium discharge tube to the outside of
the housing 2.
[0081] The inner tube 3 and the middle tube 4 are accommodated in the internal space 2a of
the housing 2 so as to be coaxial with each other. A heat exchange chamber 3c, a gas exchange
chamber 45, and the like are formed by the irmer tube 3 and the middle tube 4.
[0082] An outer diameter of the middle tube 4 is smaller than an irmer diameter of the
housing main body 11. The middle tube 4 is arranged at the housing main body 11 such that a
center axis of the middle tube 4 and a center axis of the housing main body 11 coincide with each
other. With this, a ring-shaped space is formed between an outer peripheral surface of the
middle tube 4 and an inner peripheral surface of the housing main body 11, and this ring-shaped
space constitutes the gas exchange chamber 45. A hollow fiber body (gas exchanger) 43 is
provided in the gas exchange chamber 45.
[0083] The hollow fiber body 43 is formed in a substantially cylindrical shape (or a
columnar shape including an internal space) and is constituted by a plurality of hollow fibers.
Specifically, the hollow fiber body 43 is configured such that a mat-shaped hollow fiber
membrane (bundle) formed by making a plurality of hollow fibers intersect with each other and
laminating the plurality of hollow fibers on each other is wound around the outer peripheral
surface of the middle tube 4. The hollow fiber membrane is wound such that the thickness of
the hollow fiber body 43 substantially coincides with an interval between the middle tube 4 and
the housing main body 11. To be specific, the hollow fiber body 43 is formed along the irmer
19
peripheral surface of the housing main body 11 such that an outer peripheral surface of the
hollow fiber body 43 contacts the inner peripheral surface of the housing main body 11 over the
substantially entire periphery.
[0084] An annular sealing member 50 is provided in a region located at the left side of the
gas exchange chamber 45. The sealing member 50 forms a gas inflow space 52 together with
an inner peripheral surface of the cap portion 14, and the gas supply port 18 communicates with
the gas inflow space 52. Moreover, an annular sealing member 51 is provided in a region
located at the right side of the gas exchange chamber 45. The sealing member 51 forms a gas
outflow space 53 together with an inner peripheral surface of the cap portion 15, and the gas
discharge port 19 communicates with the gas outflow space 53.
[0085] The hollow fiber body 4 3 is provided so as to be sandwiched between the sealing
member 50 and the sealing member 51 from the left and right sides. The sealing member 50
seals between the middle tube 4 and the housing 2 at the left side of the gas exchange chamber
45 in an entire circumferential direction. Moreover, the sealing member 51 seals between the
middle tube 4 and the housing 2 at the right side of the gas exchange chamber 45 in the entire
circumferential direction. According to this configuration, the gas inflow space 52
communicating with the gas supply port 18 and the gas outflow space 53 communicating with
the gas discharge port 19 communicate with each other through inner holes of the plurality of
hollow fibers constituting the hollow fiber body 43.
[0086] In the hollow fiber body 43, gaps are provided among the plurality of hollow fibers
constituting the hollow fiber body 43. In the gas exchange chamber 45, blood flows through
the gaps. Specifically, the blood introduced to the gas exchange chamber 45 flows through the
gaps in the hollow fiber body 43 and flows from the right side to the left side in the direction
along the axis lla while contacting the hollow fibers. Oxygen-rich gas flows from an external
gas supply device through the gas supply port 18 and the gas inflow space 52 into the inner holes
of the hollow fibers. Therefore, when the blood having high carbon dioxide concentration
contacts the hollow fibers, gas exchange is performed between the blood and the gas in the
hollow fibers. With this, carbon dioxide is removed from the blood, and oxygen is added to the
blood. As above, the blood flows to the left side in the direction along the axis lla in the gas
exchange chamber 45 while being subjected to the gas exchange. On the other hand, the gas
flowing through the inner holes of the hollow fibers flows to the right side while being subjected
to the gas exchange, and returns to the external gas supply device through the gas outflow space
53 and the gas discharge port 19.
[0087] A downstream (left) portion of the gas exchange chamber 45 is larger in diameter in
20
the radially outward direction than the other portion of the gas exchange chamber 45.
Specifically, as shown in FIG. 2, a ring-shaped recess 54 that is recessed in the radially outward
direction is formed on an inner peripheral surface of a left portion of the housing main body II.
The diameter of a left portion of the recess 54 is substantially constant. On the other hand, a
right portion of the recess 54 tapers toward the right side, i.e., the right portion of the recess 54 is
formed in a tapered shape. The sealing member 50 is arranged at a middle portion of the recess
54. A portion of the recess 54 which portion is located at the right side of the sealing member
50 is formed in a tapered shape as described above. An outer peripheral space 55 formed
between the recess 54 and the hollow fiber body 43 is formed so as to surround the hollow fiber
body 43, and a lower portion of the outer peripheral space 55 communicates with the blood
outflow port 17. According to this configuration, the blood having been subjected to the gas
exchange in the gas exchange chamber 45 is introduced to the outer peripheral space 55 and then
flows into the blood outflow port 17.
[0088] A filter structure having an annular shape along the outer peripheral space 55 is
provided in the outer peripheral space 55. The filter structure includes a straightening frame 56.
The straightening frame 56 guides bubbles, carried together with the blood flowing through the
gas exchange chamber 45 while being subjected to the gas exchange, toward the hollow fiber
body 43 again and makes the bubbles be taken in the hollow fibers. Details will be described
later.
[0089] An air vent port 57 through which the outer peripheral space 55 communicates with
the outside is provided at an upper portion of the housing main body II. The air vent port 57
discharges, to the outside, the bubbles accumulated in an upper portion (bubble trap portion) of
the outer peripheral space 55. The bubble trap portion is provided downstream of a
below-described bubble storing portion 70 and is provided so as to be able to store the bubbles.
In the present embodiment, such bubble trap portion is constituted by the recess 54 (especially a
portion of the recess 54 which portion is located at an upper side of the hollow fiber body 43).
An outside opening end of the air vent port 57 is basically covered with a cap member (not
shown). Therefore, the bubbles and the blood are not discharged through the air vent port 57
except for when the bubbles are discharged.
[0090] The middle tube 4 includes a middle tube main body portion 40 and a bridge portion
41. The middle tube main body portion 40 is formed in a cylindrical shape and forms the gas
exchange chamber 45 at the outside of the middle tube main body portion 40. The inner tube 3
forming the heat exchange chamber 3c is accommodated in an inner space of the middle tube
main body portion 40. The bridge portion 41 forms heat medium passages and a blood passage
21
which three-dimensionally intersect with each other. The heat medium which flows in and out
from the heat exchange chamber 3c flows through the heat medium passage, and the blood
which flows from the heat exchange chamber 3c toward the gas exchange chamber 45 flows
through the blood passage.
[0091] As shown in FIG. 2, a tube bundle 32 is inserted into and arranged in the heat
exchange chamber 3c in the inner tube 3 such that an axial direction of the tube bundle 32
coincides with an axial direction of the inner tube 3. The tube bundle 32 is an assembly of a
plurality of heat exchange pipes. The heat exchange pipes are long and small-diameter tubes
made of a material, such as stainless steel, having high heat conductivity. The blood from the
blood inflow port 16 flows into the heat exchange pipes through left openings of the heat
exchange pipes.
[0092] An outer diameter ofthe inner tube 3 is smaller than an inner diameter of the middle
tube 4. The inner tube 3 is positioned relative to the middle tube 4 such that an axis of the inner
tube 3 coincides with the axis of the middle tube 4. With this, an annular heat medium chamber
3 5 through which the heat medium flows is formed between an outer peripheral surface ofthe
inner tube 3 and an inner peripheral surface of the middle tube 4. The heat medium chamber 35
is divided into a first heat medium partial chamber 33 located at an upper side and a second heat
medium partial chamber 34 located at a lower side. The first heat medium partial chamber 33
at the upper side communicates with the medium outflow port 21 through one heat medium
passage of the bridge portion 41. The second heat medium partial chamber 34 at the lower side
communicates with the medium inflow port 20 through another heat medium passage of the
bridge portion 41.
[0093] As shown in FIG. 2, a pair of tube supporting bodies 32a each having a circular plate
shape are provided in the inner tube 3. An outer diameter of each tube supporting body 32a
substantially coincides with an inner diameter of the inner tube 3. The tube supporting body
32a located at the left side is inserted into a left end of the inner tube 3, and the tube supporting
body 32a located at the right side is inserted into a right end of the inner tube 3. Left ends of
the heat exchange pipes constituting the tube bundle 32 are respectively inserted into a plurality
of holes radially provided at the tube supporting body 32a located at the left side, and right ends
of the heat exchange pipes constituting the tube bundle 32 are respectively inserted into a
plurality of holes radially provided at the tube supporting body 32a located at the right side.
[0094] With this, both opening end portions of the inner tube 3 are sealed by the pair of tube
supporting bodies 32a, and both ends of each heat exchange pipe of the tube bundle 32 are open
at both end sides of the inner tube 3. Left openings of the heat exchange pipes of the tube
22
bundle 32 communicate with the blood inflow port 16, and right openings of the heat exchange
pipes of the tube bundle 32 communicate with the gas exchange chamber 45 through the blood
passage of the bridge portion 41.
[0095] Moreover, a plurality of through holes are formed at each of upper and lower
portions of the inner tube 3. The inside of the inner tube 3 and the first heat medium partial
chamber 33 located at the upper side communicate with each other through the through holes of
the upper portion of the inner tube 3, and the inside of the inner tube 3 and the second heat
medium partial chamber 34 located at the lower side communicate with each other through the
through holes of the lower portion of the inner tube 3. Therefore, the heat medium having
flowed into the medium inflow port 20 enters into the inner tube 3 (heat exchange chamber 3c)
through the second heat medium partial chamber 34 located at the lower side, flows through gaps
of the heat exchange pipes of the tube bundle 32, and then flows through the first heat medium
partial chamber 33 located at the upper side and the medium outflow port 21 to the outside.
[0096] According to the above artificial lung device I, venous blood taken out from a vein
enters into the housing 2 through the blood inflow port 16 and enters into the heat exchange
chamber 3c through the left openings of the heat exchange pipes of the tube bundle 32. The
blood in the heat exchange chamber 3c flows through the right openings of the heat exchange
pipe and the bridge portion 41, enters into the gas exchange chamber 45 from the right side of
the gas exchange chamber 45, flows through the gas exchange chamber 45 to the left side, and is
delivered through the blood outflow port 17 to the outside.
[0097] During this, in the heat exchange chamber 3c, heat exchange is performed between
the heat medium having flowed through the medium inflow port 20 and the second heat medium
partial chamber 34 into the heat exchange chamber 3c and the blood flowing in the heat
exchange pipes of the tube bundle 32. Moreover, in the gas exchange chamber 45, the gas
exchange is performed between the blood flowing through the gaps of the hollow fiber body 43
and the oxygen-rich gas flowing through the inner holes of the hollow fibers. Thus, the
temperature of the blood having flowed into the artificial lung device I is adjusted to a
predetermined temperature. In addition, carbon dioxide in the blood is reduced, and oxygen is
added to the blood. With this, the blood as arterial blood flows out through the blood outflow
port 17.
[0098] The artificial lung device I is of a horizontal type, and the blood flowing through the
gas exchange chamber 45 flows in a substantially horizontal direction. In some cases, a small
amount of bubbles having entered into the gas exchange chamber 45 from somewhere is mixed
with the blood flowing through the gas exchange chamber 45. Such bubbles are basically
23
absorbed when being brought into contact with the hollow fibers of the hollow fiber body 43,
and most of the bubbles are removed. However, in some cases, the bubbles are not adequately
absorbed in the hollow fibers while the blood flows through the hollow fiber body 43 once.
Therefore, the artificial lung device 1 according to the present embodiment includes the
straightening frame 56 by which a larger amount of bubbles are absorbed by the hollow fiber
body43.
[0099] FIG 3 is a perspective view showing the straightening frame 56 included in the
artificial lung device 1. The straightening frame 56 constitutes a bubble guide portion
configured to guide the bubbles, which have flowed through the hollow fiber body 43 by the
flow of the blood without being absorbed, toward the hollow fiber body 43 again. As shown in
FIG. 3, the straightening frame 56 has a substantially annular shape and a substantially trnncated
cone shape.
[0100] Specifically, the straightening frame 56 includes a first opening 60 located at the left
side and having a relatively small diameter and a second opening 6llocated at the right side and
having a relatively large diameter. Each of the first opening 60 and the second opening 61 has a
circular shape. When the straightening frame 56 is assembled to the artificial lung device 1, the
position of an upper end 60b of the first opening 60 in the upper-lower direction and the position
of an upper end 6lb of the second opening 61 in the upper-lower direction are substantially the
same as each other, but a lower end 60c of the first opening 60 is located higher than a lower end
61 c of the second opening 61. Moreover, the first opening 60 and the second opening 61 are
spaced apart from each other in a left-right direction by a predetermined distance and are
connected to each other by a straightening surface 62 that is a curved surface. Therefore, the
straightening frame 56 has such a trnncated cone shape that a center line 60a of the first opening
60 is located higher than a center line 6la of the second opening 61.
[0101] As shown in FIG. 2, the straightening frame 56 is provided in the outer peripheral
space 55 such that: the first opening 60 located at the left side is fixed to the sealing member 50;
and the second opening 61 located at the right side contacts the inner peripheral surface of the
housing main body 11. As a result, the straightening surface 62 is provided in the outer
peripheral space 55 so as to cross a passage extending from the gas exchange chamber 45 toward
the blood outflow port 17. The straightening surface 62 is provided so as to be opposed to the
outer peripheral surface of the hollow fiber body (gas exchanger) 43 and surround the hollow
fiber body 43. As shown in FIG 2, an upper portion of the straightening frame 56 is located
substantially right under an opening of the air vent port 57 which opening is located close to the
outer peripheral space 55, and a lower portion of the straightening frame 56 is located
24
substantially right above an opening of the blood outflow port 17 which opening is located close
to the outer peripheral space 55.
[0102] Moreover, the straightening surface 62 includes a first straightening surface 63 and a
second straightening surface 64. The first straightening surface 63 is provided at a relatively
lower side and is inclined such that a downstream portion (left portion in FIG. 2) 63b of the first
straightening surface 63 in a flow direction of the blood is located closer to the outer peripheral
surface of the hollow fiber body 43 than an upstream portion (right portion in FIG 2) 63a of the
first straightening surface 63 in the flow direction of the blood. Moreover, one or a plurality of
openings 65 are formed at the first straightening surface 63, and filters 66 are provided at the
respective openings 65. The filters 66 provided at the first straightening surface 63 are spaced
apart from the outer peripheral surface of the hollow fiber body 43 and face an upstream side in
the flow direction of the blood. With this, the blood having flowed through the hollow fiber
body 43 flows through the filters 66 toward the blood outflow port 17. The filters 66 remove
predetermined foreign matters mixed in the blood flowing through the filters 66, and known
blood filters may be used. It should be noted that the filter structure may not include the
straightening frame 56 and may be constituted by only the filter 66.
[0103] On the other hand, the second straightening surface 64 is provided at a relatively
upper side. The second straightening surface 64 is located closer to the outer peripheral surface
of the hollow fiber body 43 than the upstream portion 63a of the first straightening surface 63
and has a different inclination relative to the outer peripheral surface from the first straightening
surface 63. In the present embodiment, in a sectional view, an upper end portion of the second
straightening surface 64 forms a surface substantially parallel to the outer peripheral surfuce of
the hollow fiber body 43. It should be noted that the second straightening surface 64 is also
located so as to be spaced apart from the outer peripheral surface of the hollow fiber body 43.
As shown in FIG 2, the bubble storing portion 70 is formed between the second straightening
surface 64 and the outer peripheral surfuce of the hollow fiber body 43. It should be noted that
a filter is not provided at the second straightening surface 64. Moreover, the second
straightening surface 64 is located higher than a portion which is located at the lower side of the
straightening surface 62 and provided with one or a plurality of openings 65 (filters 66).
According to this configuration, as compared to a case where the straightening frame 56 includes
a filter at the upper side of the straightening surface 62, the bubbles can be more surely
accumulated at the upper side of the second straightening surface 64 where the bubbles tend to
be accumulated, and the bubbles can be more effectively prevented from flowing to the
downstream side of the filters.
25
[0104] The straightening frame 56 according to the present embodiment is an example in
which when the straightening surface 62 is substantially equally divided into four regions that
are upper and lower portions and portions each between the upper and lower portions, the filters
66 are provided at three regions other than the upper portion. However, the positions where the
filters 66 are provided are not limited to these. Each filter 66 can be provided at a suitable
position and range other than the second straightening surface 64 that is the upper portion.
[0 1 05] In the artificial lung device 1 including the straightening frame 56, the blood having
flowed through the hollow fiber body 43 of the gas exchange chamber 45 flows through the
filters 66 of the straightening frame 56 to the blood outflow port 17. At this time, the bubbles
mixed in the blood are received by the straightening surface 62 of the straightening frame 56.
The bubbles flow along the first straightening surface 63 from the upstream portion 63a to the
downstream portion 63b or flow upward by buoyancy. As a result, in the process of flowing
from the upstream portion 63a of the first straightening surface 63 to the downstream portion 63b
of the first straightening surfuce 63, the bubbles approach the hollow fiber body 43. In addition,
in the process of flowing upward from the first straightening surface 63 to the second
straightening surface 64 by the buoyancy, the bubbles approach the hollow fiber body 43.
Therefore, in the artificial lung device 1, the bubbles contained in the blood having flowed
through the hollow fiber body 43 once can be made to flow toward the hollow fiber body 43
again by the straightening frame 56 and can be absorbed by the hollow fiber body 43.
[0106] Moreover, the artificial lung device 1 includes the bubble storing portion 70 between
the second straightening surface 64 and the outer peripheral surface of the hollow fiber body 43.
Therefore, even if a large amount of bubbles flow, the bubbles can be temporarily stored in the
bubble storing portion 70. It should be noted that the first straightening surface 63 has a
function of mainly guiding the bubbles to the hollow fiber body 43 (making the bubbles flow
toward the hollow fiber body 43), and the second straightening surface 64 has a function of
temporarily storing the guided bubbles and bringing the bubbles into contact with the hollow
fiber body 43. Therefore, the second straightening surface 64 does not have to be accurately
parallel to the outer peripheral surface of the hollow fiber body 43.
[0 1 07] Embodiment 2 according to First Disclosure
FIGS. 4A and 4B are sectional views each showing a straightening frame 56A of an
artificial lung device lA according to Embodiment 2. More specifically, FIG 4A is a sectional
view showing portions including the entire straightening frame 56A in the artificial lung device
lA, and FIG 4B is a sectional view showing portions including the upper portion of the
straightening frame 56 A in the artificial lung device lA. The straightening frame 56A of the
26
artificial lung device !A includes a second straightening surface 64A at least a part of which is
formed by an inner wall surface of the housing main body 11.
[0 1 08] To be specific, Embodiment 1 has described a case where the entire straightening
frame 56 is configured as a separate member independently from the housing main body 11.
However, the configuration of the straightening frame 56 is not limited to this. More
specifically, in the artificial lung device lA shown in FIG 48, a wall portion 71 extends from a
right end of an upper portion of the recess 54 of the housing main body 11 to the inside of the
outer peripheral space 55 along the outer peripheral surface of the hollow fiber body 43. An
inner peripheral surface 71A of the wall portion 71 constitutes (part of) a straightening surface
62A, and especially, an upper portion of the inner peripheral surface 71A constitutes the second
straightening surface 64A.
[0 1 09] Moreover, as shown in FIG 4A, a width of the straightening frame 56A in the
left-right direction in a front view is substantially constant from its upper portion to its lower
portion. A projection amount of the wall portion 71 toward the left side decreases as the wall
portion 71 extends from the upper portion to the lower portion. A portion 72 of the
straightening frame 56 A other than a portion constituted by the wall portion 71 is constituted as a
separate member from the housing main body 11. A component corresponding to the first
straightening surface 63 of Embodiment 1 is mainly constituted by the portion 72, and the filter
66 is provided at an opening (not shown) formed at the portion 72.
[0 11 0] It should be noted that in the straightening frame 56A, a boundary between the
portion constituted by the wall portion 71 and the portion 72 other than the above portion is set
as a boundary line extending in a circumferential direction in the example of FIG 4A. However,
the boundary is not limited to this and may be set arbitrarily. Moreover, part of the
straightening frame 56 A is constituted by the wall portion 71, but the entire straightening frame
56A(except for the filter 66) may be constituted by the wall portion 71. It should be noted that
in Embodiments 1 and 2 according to the first disclosure, a space is formed by an inside surface
of the housing main body 11 (more specifically, an inside surface of the recess 54) as an
opposing wall, an inside surface of the filter structure, and an outside surface of the hollow fiber
body 43, and constitutes the bubble storing portion 70 or the bubble guide portion. In this case,
the opposing wall may be provided at the filter structure.
[0 111] According to this configuration, the positioning of the second straightening surface
64A and the outer peripheral surface of the hollow fiber body 43 when assembling the artificial
lung device 1A can be more easily performed with a high degree of accuracy.
[0112] Embodiment 3 according to First Disclosure
27
FIGS. 5A and 5B are sectional views showing the blood outflow port 17 of an
artificial lung device 1B according to Embodiment 3. The following will describe a case where
instead of or in addition to the filters 66 of the straightening frame 56 or 56A of Embodiment 1
or 2, a filter is provided at a different position.
[0113] As with Embodiments 1 and 2, the blood outflow port 17 shown in FIG 5A includes
the port attaching portion 17a and the port main body portion 17b. A filter 66A having a flat
plate shape is provided at an opening of the port attaching portion 17a so as to cover the opening,
the opening being located close to the inside of the housing main body 11. A periphery of the
filter 66A may be fixed by a fixing member which is a member different from the filter 66A and
fixes the filter 66A to the housing.
[0114] Moreover, as with Embodiments 1 and 2, the blood outflow port 17 shown in FIG.
5B includes the port attaching portion 17a and the port main body portion 17b. A filter 66B
having a columnar shape is provided inside the port attaching portion 17a. The filter 66B has
an outer diameter that is substantially equal to an inner diameter of the port attaching portion 17a
and is inserted into the port attaching portion 17a so as to contact an inner peripheral surface of
the port attaching portion 17a with almost no gap. Moreover, the size of the filter 66B in the
flow direction of the blood in the blood outflow port 17 is larger than an inner diameter of the
blood outflow port 17.
[0115] According to these filters 66A and 66B, foreign matters can be removed from the
blood in the blood outflow port 17. Moreover, since the filter 66B shown in FIG 5B can easily
secure a large volume, a larger amount of foreign matters can be removed from the blood.
[0116] The following will describe Embodiments 1 to 8, Modified Examples 1 and 2, and
Reference Example 1 according to the second disclosure.
[0117] Embodiment 1 according to Second Disclosure
FIG 6 is a front sectional view showing the configuration of an artificial lung device
1001AofEmbodiment 1. FIG. 7 is a side sectional view taken along line II-II in the artificial
lung device 100 1A shown in FIG 6. In a surgical operation performed after the movement of
the heart of a patient is stopped, the artificial lung device 100 1A shown in FIGS. 6 and 7 is used
as a substitute for the function of the lung of the patient. Therefore, the artificial lung device
lOOlA has a gas exchange function of removing carbon dioxide contained in the blood of the
patient and adding oxygen to the blood and a heat exchange function of adjusting the
temperature of the blood. The artificial lung device 100 lAin Embodiment 1 is of a so-called
horizontal type and includes a housing 1002 and an inner tube 1003.
[0118] The housing 1002 is formed in a substantially cylindrical shape including both end
28
portions that are closed. The housing 1002 includes an internal space 1002a accommodating
the inner tube 1003. Moreover, the housing 1002 includes a housing main body 1010, a
suspending portion 1011, and two cap portions 1012 and 1013.
[0119) The housing main body 1010 is formed in a substantially cylindrical shape, and the
suspending portion 1011 is provided at an outer peripheral surface of an upper portion of the
housing main body 1010. The suspending portion 1011 is arranged at a substantially middle
portion of the housing main body 1010 which portion is located at a substantially middle position
in a direction along an axis 10 lOa of the housing main body 1010. The suspending portion
1011 extends in the radially outward direction from the outer peripheral surface of the upper
portion of the housing main body 1010. The suspending portion 1011 is formed in, for example,
a substantially columnar shape and is suspended in such a manner that a tip end-side portion
thereof is attached to an external suspending device (not shown). Therefore, the housing main
body 1010 can be suspended through the suspending portion 1011, and the axis 1010a of the
suspended housing main body 1010 extends in a horizontal direction.
[0120] The housing main body 1010 includes opening end portions at both sides in the
direction along the axis 101 Oa. The opening end portion at one side (left side in FIG 6) is
closed by the cap portion 1012, and the opening end portion at the other side (right side in FIG
6) is closed by the cap portion 1013. Each of the cap portions 1012 and 1013 is formed in a
substantially circular plate shape. It should be noted that in the following description, for
convenience of explanation, regarding the direction along the axis 101 Oa of the housing main
body 1010, a side where the cap portion 1012 is located is referred to as a left side, and a side
where the cap portion 1013 is located is referred to as a right side.
[0121] As shown in FIG. 6, a gas supply port 1014 is formed at the cap portion 1012. The
gas supply port 1014 is formed in a substantially cylindrical shape and projects to the left side in
the direction along the axis 101 Oa from the vicinity of an outer peripheral edge of the cap portion
1012. The gas supply port 1014 is connected to an external gas supply device (not shown)
through a gas supply tube. Oxygen-containing gas supplied from the gas supply device is
introduced through the gas supply port I 014 into the housing 1002.
[0122] A gas discharge port 1015 is formed at the cap portion 1013. The gas discharge
port 1015 is formed in a substantially cylindrical shape and projects to the right side in the
direction along the axis 1010a from the vicinity of an outer peripheral edge of the cap portion
1013. The gas discharge port 1015 is connected to the external gas supply device through a gas
discharge tube. The gas supplied through the gas supply port 1014 into the housing 1002 is
discharged through the gas discharge port 1015 and is returned to the gas supply device.
29
[0123] A blood inflow port 1016 is formed in the vicinity of a central axis (axis which
substantially coincides with the axis 1010a of the housing main body 1010) of the cap portion
1012. The blood inflow port 1016 is formed in a substantially cylindrical shape and projects
from a lower side of the central axis of the cap portion 1012 in a left and obliquely downward
direction. A venous blood tube (not shown) is connected to the blood inflow port 1016, and
venous blood is introduced through the venous blood tube and the blood inflow port 1016 into
the housing main body 1010.
[0124] A blood outflow port 1017 is formed at a position of a lower portion (portion
opposite to the suspending portion 1013) of the outer peripheral surface of the housing main
body 1010 which position is located at the left side of a center of the artificial lung device 100 1A
in the direction along the axis 10 lOa. More specifically, the blood outflow port 1017 includes a
port attaching portion 1017a and a port main body portion 1017b. The port attaching portion
10 17a is formed in a substantially cylindrical shape. The port attaching portion 10 17a is
provided at the lower portion of the outer peripheral surface of the housing main body 1011 and
projects downward. The port main body portion 10 17b is inserted into the port attaching
portion 10 17a from a lower side. The port main body portion 10 17b is formed in a
substantially cylindrical shape. The port main body portion 1017b projects downward from a
lower end of the port attaching portion 10 17a and is bent in an obliquely downward direction at a
tip side of the lower end of the port attaching portion 10 17a. The port main body portion 10 17b
is rotatable relative to the port attaching portion 1017a about a center axis of the port attaching
portion 10 17a. Therefore, an outflow opening of the port main body portion 10 17b can be
directed in various directions. An arterial blood tube (not shown) is connected to the blood
outflow port 1017 (port main body portion 10 17b ). The arterial blood generated in the artificial
lung device 1001Ais delivered through the arterial blood tube to an outside.
[0125] A medium inflow port and a medium outflow port (both not shown) are provided at
the cap portion 1013. The medium inflow port and the medium outflow port are arranged so as
to sandwich a central axis of the cap portion 1013 and be spaced apart from each other. The
medium inflow port is connected to a medium supply tube (not shown), and a heat medium, such
as hot water or cold water, from the medium supply tube is introduced through the medium
inflow port into the housing 1002. The medium outflow port is connected to a medium
discharge tube (not shown), and the heat medium in the housing 1002 is discharged through the
medium outflow port and the medium discharge tube to the outside of the housing 1002.
[0126] The inner tube 1003 is accommodated in the internal space 1002a of the housing
1002 so as to be substantially coaxial with the housing main body 1010. The internal space
30
1002a of the housing 1002 is divided into a heat exchange chamber 1020, a gas exchange
chamber 1021, and the like by the inner tube 1003. Specifically, the internal space of the inner
tube 1003 constitutes the heat exchange chamber 1020. Moreover, a ring-shaped space between
the inner tube 1003 and the housing main body 1010 is further divided into a small-diameter
ring-shaped space and a large-diameter ring-shaped space by a below-described tubular filter
structure 1030. The small-diameter ring-shaped space constitutes the gas exchange chamber
1021, and the large-diameter ring-shaped space constitutes the blood outflow space 1022. A
hollow fiber body (gas exchanger) 1040 is provided in the gas exchange chamber 1021.
[0127] The hollow fiber body 1040 is formed in a substantially cylindrical shape (or a
columnar shape including an internal space) and is constituted by a plurality of hollow fibers.
Specifically, the hollow fiber body 1040 is configured such that a mat-shaped hollow fiber
membrane (bundle) formed by making the plurality of hollow fibers intersect with each other
and laminating the plurality of hollow fibers on each other is wound around an outer peripheral
surfuce of the inner tube 1003. It should be noted that the bundle does not have to be directly
wound around the outer peripheral surface of the inner tube 1003, but a cylindrical core member
which is externally fitted to the inner tube 1003 may be prepared, and the bundle may be wound
around the core member and then externally fitted to the inner tube 1003 together with the core
member.
[0128] An annular sealing member 1050 is provided in a region located at the left side of
the gas exchange chamber 1021 and the blood outflow space 1022 so as to be externally fitted to
a left end portion of the hollow fiber body 1040. The sealing member 1050 forms a gas inflow
space 1052 together with an inner peripheral surface of the cap portion 1012 and a left end
surface of the hollow fiber body 1040, and the gas supply port 1014 communicates with the gas
inflow space 1052. Moreover, an annular sealing member 1051 is provided in a region located
at the right side of the gas exchange chamber 1021 and the blood outflow space 1022 so as to be
externally fitted to a right end portion of the hollow fiber body 1040. The sealing member 1051
forms a gas outflow space 1053 together with an inner peripheral surface of the cap portion 1013
and a right end surface of the hollow fiber body 1040, and the gas discharge port I 015
communicates with the gas outflow space 1053.
[0129] The hollow fiber body 1040 is provided so as to extend between the gas inflow space
1052 and the gas outflow space 1053. The sealing member 1050 seals between the hollow fiber
body 1040 and the housing 1002 in the entire circumferential direction at the left side of the
blood outflow space 1022, and the sealing member 1051 seals between the hollow fiber body
1040 and the housing 1002 in the entire circumferential direction at the right side of the blood
31
outflow space 1022. According to this configuration, the gas inflow space 1052
communicating with the gas supply port 1014 and the gas outflow space 1053 communicating
with the gas discharge port 1015 communicate with each other through the inner holes of the
plurality of hollow fibers constituting the hollow fiber body 1040.
[0130) In the hollow fiber body 1040, gaps are provided among the plurality of hollow
fibers constituting the hollow fiber body 1040. In the gas exchange chamber 1021, blood flows
through the gaps. Specifically, the blood introduced to the gas exchange chamber 1021 flows
through the gaps in the hollow fiber body 1040 and flows in the radially outward direction about
the axis 1010a while contacting the hollow fibers. Oxygen-rich gas flows from an external gas
supply device through the gas supply port 1014 and the gas inflow space 1052 into the inner
holes of the hollow fibers. Therefore, when the blood having high carbon dioxide
concentration contacts the hollow fibers, gas exchange is performed between the blood and the
gas in the hollow fibers. With this, carbon dioxide is removed from the blood, and oxygen is
added to the blood. As above, the blood flows in the radially outward direction in the gas
exchange chamber 1021 while being subjected to the gas exchange. On the other hand, the gas
flowing through the inner holes of the hollow fibers flows to the right side while being subjected
to the gas exchange, and returns to the external gas supply device through the gas outflow space
1053 and the gas discharge port 1015.
[0 131) As described above, the internal space of the inner tube 1003 constitutes the heat
exchange chamber 1020. Medium pipe passages (not shown) are provided in the heat exchange
chamber 1020. The medium inflow port is connected to first ends of the medium pipe passages,
and the medium outflow port is connected to second ends of the medium pipe passages. The
medium pipe passages are long and small-diameter pipe members made of a material, such as
stainless steel, having high heat conductivity. A plurality of through holes 1 003a which
penetrate the inner tube 1003 from inside to outside are provided at a wall portion of the inner
tube 1003 over the entire periphery. The blood having flowed through the blood inflow port
1016 flows through gaps of the medium pipe passages and the through holes 1003a of the inner
tube 1003 to the gas exchange chamber 1021. As above, the blood flows radially from the heat
exchange chamber 1020 to the gas exchange chamber 1021. While the blood flows through the
heat exchange chamber 1020, the medium for temperature adjustment flows through the medium
pipe passages from the medium inflow port. Therefore, the temperature of the blood which has
contacted the medium pipe passages is adjusted to a suitable temperature. It should be noted
that a heat exchanger provided in the heat exchange chamber 1020 is not limited to the medium
pipe passages and is only required to be provided such that the blood having flowed through the
32
blood inflow port 1016 is subjected to the heat exchange through the heat exchanger and is then
subjected to the gas exchange by the hollow fiber membrane.
[0 132] According to the above artificial lung device 100 lA, venous blood taken out from a
vein enters into the housing 1002 through the blood inflow port 1016, flows through the heat
exchange chamber 1020 inside the inner tube 1003, the through holes 1003a of the inner tube
1003, the gas exchange chamber 1021 outside the inner tube 1003, the filter structure 1030, and
the blood outflow space 1022 in this order, and is delivered through the blood outflow port 1017
to the outside.
[0133] During this, in the heat exchange chamber 1020, the blood is subjected to heat
exchange with the heat medium flowing through the medium pipe passages as described above,
and therefore, the temperature of the blood is adjusted to a suitable temperature. Moreover, in
the gas exchange chamber 1021, the gas exchange is performed between the blood flowing
through the gaps of the hollow fiber body 1040 and the oxygen-rich gas flowing through the
inner holes of the hollow fibers. Thus, temperature ofthe blood having flowed into the
artificial lung device lOOlA is adjusted to a predetermined temperature. In addition, carbon
dioxide in the blood is reduced, and oxygen is added to the blood. With this, the blood as
arterial blood flows out through the blood outflow port I 017.
[0134] The artificial lung device IOOlA includes a bubble guide portion 1090 as a
component which makes the hollow fibers absorb a larger amount of gas, such as bubbles,
flowing together with the blood. To be specific, the artificial lung device 100 lA includes an
opposing wall which is arranged so as to be opposed to a surface I 041 of the hollow fiber body
I 040 and forms a space (bubble storing portion) 1091 between the opposing wall and the surface
I 041. A separation dimension D I between the surface I 041 of the hollow fiber body I 040 and
the opposing wall gradually decreases to become zero toward a vertically upper side. The
surface I 041 of the hollow fiber body I 040 and the opposing wall which are formed such that
the separation dimension D 1 gradually decreases to zero constitute the bubble guide portion
I 090 configured to guide the bubbles, which has flowed through the hollow fiber body 1040, to
the hollow fiber body 1040 again. Moreover, in the artificial lung device I 00 lA, the filter
structure I 030 constitutes the above opposing wall. Details will be described below.
[0135] The filter structure 1030 of the artificial lung device IOOIA has a function of
removing foreign matters in the blood. As shown in FIGS. 6 and 7, the filter structure 1030 is
provided so as to cross a passage through which the blood having flowed through the hollow
fiber body 1040 flows toward the blood outflow port 1017. More specifically, the filter
structure 1030 is formed in a cylindrical shape, and an inner diameter Rl of the filter structure
33
1030 is larger than an outer diameter R2 of the cylindrical hollow fiber body 1040. Then, the
filter structure 1030 is arranged eccentrically with respect to the hollow fiber body 1040
similarly formed in a cylindrical shape. Therefore, a portion of an inner peripheral surface
1031 of the filter structure 1030 which portion corresponds to an upper portion of the filter
structure 1030 is in contact with a portion of an outer peripheral surface 1041 of the hollow fiber
body 1040 which portion corresponds to an upper portion of the hollow fiber body 1040.
[0 136] As a result, the space 1091 is formed between the outer peripheral surface 1041 of
the hollow fiber body 1040 and the inner peripheral surface 1031 of the filter structure 1030
which constitutes the opposing wall opposed to the outer peripheral surface 1041. As shown in
FIG. 7, the separation dimension Dl between the outer peripheral surface 1041 of the hollow
fiber body 1040 and the inner peripheral surface 1031 of the filter structure 1030 gradually
decreases toward the vertically upper side and becomes zero at a contact portion 1 090a where the
outer peripheral surface 1041 of the hollow fiber body 1040 and the inner peripheral surface
1031 ofthe filter structure 1030 contact each other. According to the artificial lung device
IOOIA of Embodiment 1, the bubble guide portion 1090 is constituted by the outer peripheral
surface 1041 of the hollow fiber body 1040 and the inner peripheral surface 1031 of the filter
structure 1030 which are formed such that the separation dimension D 1 gradually decreases to
zero. In other words, in Embodiment I according to the second disclosure, a space is
constituted by the inside surface of the filter structure and the outside surface of the hollow fiber
body 1040 and constitutes the bubble storing portion 1091 or the bubble guide portion.
[0137] According to the artificial lung device IOOIA configured as above, even when there
are bubbles which flowed through the hollow fiber body 1040 but were not absorbed, such
bubbles flow upward in the bubble guide portion 1090 along the inner peripheral surface I 031 of
the filter structure 1030 or the outer peripheral surface 1041 of the hollow fiber body 1040 by
buoyancy. Then, since the space 1091 included in the bubble guide portion 1090 gradually
decreases in width toward the upper side, the bubbles flowing upward are gradually and strongly
pressed against the hollow fiber body 1040. On this account, a larger amount of bubbles can be
absorbed by the hollow fiber body 1040, and therefore, the bubbles can be prevented from being
excessively accumulated in the housing 1002.
[0138] It should be noted that a sectional shape of the filter structure 1030 is not limited to a
circular shape shown in FIG. 7 and may be, for example, an oval shape, an elliptical shape, or a
droplet shape. Furthermore, as long as the separation dimension D 1 between the outer
peripheral surfuce 1041 of the hollow fiber body 1040 and the inner peripheral surface 1031 of
the filter structure 1030 gradually decreases to approach zero toward the vertically upper side as
34
described above (i.e., as long as the bubble guide portion 1090 is included), the configuration of
the other portion of the filter structure 1030 is not especially limited.
[0 139] Embodiment 2 according to Second Disclosure
FIG 8 is a side sectional view showing an artificial lung device 100 lB according to
Embodiment 2. Hereinafter, portions of the artificial lung device 100 lB which portions are
different from those of the artificial lung device lOOIA will be mainly described. It should be
noted that in FIG 8, reference signs obtained by adding I 00 to the reference signs used in the
explanation of the artificial lung device I 00 lA are used for the components of the artificial lung
device 100 lB which components correspond to the components of the artificial lung device
lOOlA in terms of at least the functions.
[0140] As shown in FIG. 8, the artificial lung device 100 lB is of a so-called horizontal type
and includes a housing 1102 and an inner tube 1103. The housing 1102 includes a substantially
cylindrical housing main body 1110, a suspending portion 1111, and two cap portions (not
shown). The suspending portion 1111 is connected to an upper portion of the housing main
body 1110, and the two cap portions close both end openings of the housing main body 1110.
[0 141] The inner tube 1103 is accommodated in an internal space 11 02a of the housing 1102
so as to be located at an upper side eccentrically with respect to a center axis of the housing main
body 1110. Moreover, a cylindrical hollow fiber body (gas exchanger) 1140 is provided so as
to be coaxially and externally fitted to the inner tube 1103. A portion of a surface 1141 of the
hollow fiber body 1140 which portion corresponds to an upper portion of the hollow fiber body
1140 is in contact with a portion of an inner wall surface 111 Ob of the housing main body 1110
which portion corresponds to an upper portion of the housing main body 1110.
[0142] As a result, a space (bubble storing portion) 1191 is formed between the outer
peripheral surface 1141 of the hollow fiber body 1140 and the inner wall surface Ill Ob of the
housing main body 1110 which constitutes an opposing wall opposed to the outer peripheral
surface 1141. As shown in FIG 8, a separation dimension D2 between the outer peripheral
surface 1141 of the hollow fiber body 1140 and the inner wall surface 1110b of the housing main
body 1110 gradually decreases toward a vertically upper side and becomes zero at a contact
portion 1190a where the outer peripheral surface 1141 of the hollow fiber body 1140 and the
inner wall surface 1110b of the housing main body 1110 contact each other. In the artificial
lung device lOOlB according to Embodiment 2, a bubble guide portion 1190 is constituted by the
outer peripheral surface 1141 of the hollow fiber body 1140 and the inner wall surface 111 Ob of
the housing main body 1110 which are formed such that the separation dimension D2 gradually
decreases to zero. In other words, in Embodiment 2 according to the second disclosure, a space
35
is constituted by the inner wall of the housing, the inside surface of the filter structure 1130, and
the outside surface of the hollow fiber body 1140 and constitutes the bubble guide portion 1190.
[0143] The internal space 1102a of the housing 1102 accommodates a filter structure 1130.
The filter structure 1130 is formed in a rectangular plate shape in plan view, and a middle portion
1132 of the filter structure 1130 which portion is located at a middle position in a front-rear
direction is formed in a curved shape so as to project downward in side view. An upper surface
of the middle portion 1132 of the filter structure 1130 is in contact with the surface 1141 of the
lower portion of the hollow fiber body 1140. A front end 1133 of the filter structure 1130 is in
contact with a portion of the inner wall surface 1110b of the housing main body 1110 which
portion is located at a front side and in the vicinity of a middle position in the upper-lower
direction. A rear end 1134 of the filter structure 1130 is in contact with a portion of the inner
wall surface 111 Ob of the housing main body 1110 which portion is located at a rear side and in
the vicinity of a middle position in the upper-lower direction. It should be noted that the
configuration of the filter structure 1130 is not limited to the above configuration, and another
configuration may be adopted as long as the filter structure 1130 is provided so as to cross a
passage through which the blood having flowed through the hollow fiber body 1140 flows
toward the blood outflow port.
[0144] According to the artificial lung device lOOlB, venous blood taken out from a vein
enters into the housing 1102 through the blood inflow port (not shown), flows through a heat
exchange chamber 1120 inside the inner tube 1103, through holes 1103a of the inner tube 1103, a
gas exchange chamber 1121 outside the inner tube 1103, the filter structure 1130, and a blood
outflow space 1122 in this order, and is delivered as arterial blood through the blood outflow port
(not shown) to the outside. During this, as with the artificial lung device 1001A, the
temperature of the blood is adjusted in the heat exchange chamber 1120, and carbon dioxide is
removed from the blood and oxygen is added to the blood in the gas exchange chamber 1121.
[0145] Moreover, as described above, the artificial lung device 1001B includes the bubble
guide portion 1190. Therefore, even when there are bubbles which flowed through the hollow
fiber body 1140 but were not absorbed, such bubbles flow upward in the bubble guide portion
1190 along the inner wall surface 111 Ob of the housing main body 1110 or the outer peripheral
surface 1141 of the hollow fiber body 1140 by buoyancy. Then, since the space 1191 included
in the bubble guide portion 1190 gradually decreases in width toward the upper side, the bubbles
flowing upward are gradually and strongly pressed against the hollow fiber body 1140. On this
account, a larger amount of bubbles can be absorbed by the hollow fiber body 1140, and
therefore, the bubbles can be prevented from being excessively accumulated in the housing 1102.
36
[0146] Embodiment 3 according to Second Disclosnre
FIG 9 is a front sectional view showing an artificial lung device 1001 C according to
Embodiment 3. Hereinafter, portions of the artificial lung device !OO!C which portions are
different from those of the artificial lung device !OO!A will be mainly described. It should be
noted that in FIG 9, reference signs obtained by adding 200 to the reference signs used in the
explanation of the artificial lung device 100 !A are used for the components of the artificial lung
device 1001 C which components correspond to the components of the artificial lung device
100 !A in terms of at least the functions.
[0147] As shown in FIG. 9, the artificial lung device 1001C is of a so-called horizontal type
and includes a housing 1202, an inner tube 1203, and a middle tube 1204. The middle tube
1204 is smaller in diameter than the housing 1202 and larger in diameter than the inner tube
1203. The inner tube 1203 and the middle tube 1204 are accommodated in an internal space
1202a of the housing 1202 so as to be arranged substantially coaxially with each other.
[0148] The inside of the inner tube 1203 constitutes a heat exchange chamber 1220. A
tube bundle 1260 is arranged in the heat exchange chamber 1220 such that an axial direction of
the tube bundle 1260 coincides with an axial direction of the inner tube 1203. The tube bundle
1260 is an assembly of a plurality of heat exchange pipes. The pipes are made of a material,
such as stainless steel, having high heat conductivity. The blood from a blood inflow port 1216
flows in the pipes through left openings of the pipes.
[0149] An annular heat medium chamber 1261 is formed between the inner tube 1203 and
the middle tube 1204. The heat medium chamber 1261 is divided into a first heat medium
chamber 1262 located at the lower side and a second heat medium chamber 1263 located at the
upper side. A medium inflow port 1218 communicates with the first heat medium chamber
1262, and a medium outflow port 1219 communicates with the second heat medium chamber
1263. Moreover, a plurality of through holes 1264 are formed at each of upper and lower
portions of the inner tube 1203. Furthermore, the tube bundle 1260 in the inner tube 1203 is
supported such that gaps are formed among the heat exchange pipes.
[0150] Therefore, the medium having flowed through the medium inflow port 1218 flows
through the first heat medium chamber 1262 and the through holes 1264 of the lower portion of
the inner tube 1203 to the inside of the inner tube 1203. Then, the medium flows through the
gaps of the plurality of heat exchange pipes constituting the tube bundle 1260 and the through
holes 1264 of the upper portion of the inner tube 1203 to the second heat medium chamber 1263
and further flows therefrom through the medium outflow port 1219 to the outside. On the other
hand, the blood having flowed through the blood inflow port 1216 flows through the inner holes
37
of the heat exchange pipes of the tube bundle 1260. Therefore, during this, the heat exchange
between the blood and the medium is performed, and thus, the temperature of the blood is
adjusted to a suitable temperature. It should be noted that the present embodiment is not
limited to the configuration in which the through holes 1264 are provided at the upper and lower
portions of the inner tube 1203. For example, the through holes 1264 may be provided at
opposing positions of a side portion ofthe inner tube 1203 such that the medium flows in a
direction from a paper surface near side to a paper surface deep side or in a direction from the
paper surface deep side to the paper surface near side.
[0151] The blood having been adjusted in temperature in the heat exchange chamber 1220
flows out through right openings of the tube bundle 1260, flows in the radially outward direction
in the vicinity of a right end of the inner tube 1203, and reaches a gas exchange chamber 1221
formed outside and around the middle tube 1204. More specifically, the gas exchange chamber
1221 is formed between the middle tube 1204 and a housing main body 1210, and a tubular
hollow fiber body (gas exchanger) 1240 is provided in the gas exchange chamber 1221 so as to
be externally fitted to the middle tube 1204.
[0152] The hollow fiber body 1240 includes a plurality of hollow fibers. Left openings of
the inner holes of the hollow fibers communicate with a gas supply port 1214, and right openings
of the inner holes of the hollow fibers communicate with a gas discharge port 1215. Moreover,
gaps are provided among the hollow fibers, and the blood flows through the gaps. To be
specific, the blood having flowed out from the heat exchange chamber 1220 flows into the gas
exchange chamber 1221 from the right side of the gas exchange chamber 1221 and flows
through the gaps of the hollow fiber to the left side. During this, oxygen-rich gas flows through
the inner holes of the hollow fibers, and gas exchange is performed between the blood and the
gas. As a result, carbon dioxide is removed from the blood, and oxygen is added to the blood.
[0153] A recess 1265 is formed at a left portion of an inner peripheral surface of the housing
main body 1210 so as to be larger in diameter than the other portion of the inner peripheral
surface of the housing main body 1210. The recess 1265 is located so as to surround a left
portion of the hollow fiber body 1240. A filter structure 1230 having an annular shape and a
tnmcated cone shape is arranged between the recess 1265 and the hollow fiber body 1240. The
filter structure 1230 is arranged so as to cross a passage through which the blood having flowed
through the hollow fiber body 1240 flows toward a blood outflow port 1217. Therefore, a
space defmed by the recess 1265 and the hollow fiber body 1240 is divided into two spaces by
the filter structure 1230, and one of the two spaces which communicates with the blood outflow
port 1217 constitutes a blood outflow space 1222.
38
[0154] Therefore, as described above, foreign matters in the blood having been subjected to
the gas exchange in the gas exchange chamber 1221 are removed when the blood flows through
the filter structure 1230. The blood which has become the arterial blood as above flows
through the blood outflow space 1222 and the blood outflow port 1217 to the outside. In other
words, in Embodiment 3 according to the second disclosure, a space is constituted by the inner
wall (first opposing wall) of the housing main body 1210, the inside surface of the filter structure
1230, and the outside surface of the hollow fiber body 1240 and constitutes a first bubble storing
portion or a first bubble guide portion. In this case, the first opposing wall may be provided at
the filter structure.
[0155] In the artificial lung device lOOlC, a space (second bubble guide portion 1290) is
constituted by the middle tube 1204 and the hollow fiber body 1240. More specifically, as
shown in FIG 9, a reduced-diameter portion 1266 is formed at a middle portion of the middle
tube 1204 which portion is located at a middle position in the left-right direction. The
reduced-diameter portion 1266 is reduced in diameter so as to be smaller in diameter than the
other portion of the middle tube 1204. The reduced-diameter portion 1266 is provided so as to
surround the middle portion of the middle tube 1204. The blood between the reduced-diameter
portion 1266 and the hollow fiber body 1240 flows to the left side as with the blood in the
hollow fiber body 1240. Moreover, a left portion of the reduced-diameter portion 1266
constitutes a tapered portion 1267 which has a tapered sectional contour so as to increase in
diameter toward the left side, and a right portion of the reduced-diameter portion 1266
constitutes a tapered portion 1268 which has a tapered sectional contour so as to increase in
diameter toward the right side.
[0156] The bubble guide portion 1290 is constituted by the left tapered portion 1267 of the
reduced-diameter portion 1266 of the middle tube 1204 and the hollow fiber body 1240. To be
specific, the left tapered portion 1267 constitutes a second opposing wall according to the present
invention. The tapered portion 1267 is located so as to be opposed to an inner surface 1241 of
the hollow fiber body 1240 and forms a space (second bubble storing portion) 1291 between the
tapered portion 1267 and the inner surface 1241 of the hollow fiber body 1240. Moreover, a
separation dimension D3 between an outer surface 1267a of the tapered portion 1267 and the
inner surface 1241 of the hollow fiber body 1240 gradually decreases to become zero toward a
downstream side (i.e., the left side) in the flow direction of the blood in the space 1291. In the
artificial lung device lOOlC, the bubble guide portion 1290 is formed as a ring-shaped groove
surrounding the middle tube 1204. In other words, in Embodiment 3 according to the second
disclosure, a space is constituted by the inner wall (second opposing wall) of the housing main
39
body 1210 and the inner surface of the hollow fiber body 1240 and constitutes the second bubble
storing portion 1290 or the second bubble guide portion 1291.
[0157] According to this configuration, even when there are bubbles which flowed through
the hollow fiber body 1240 but were not absorbed, such bubbles move in the bubble guide
portion 1290 toward the downstream side in the flow direction of the blood along the outer
peripheral surface 1267a of the tapered portion 1267 or the inner peripheral surfuce 1241 ofthe
hollow fiber body 1240. Since the space 1291 included in the bubble guide portion 1290
gradually decreases in width toward the downstream side, the bubbles moving toward the
downstream side are gradually pressed against the hollow fiber body 1240. On this account, a
larger amount of bubbles can be absorbed by the hollow fiber body 1240, and therefore, the
bubbles can be prevented from being excessively accumulated in the housing 1202.
[0158] It should be noted that in FIG 9, the reduced-diameter portion 1266 is formed to
have a trapezoidal section but is not limited to this. For example, the reduced-diameter portion
1266 may be formed to have a triangular section including an oblique side which increases in
diameter toward the downstream side in the flow direction of the blood or may be formed to
have a circular-arc section.
[0159] Embodiment 4 according to Second Disclosure
FIG 10 is a front sectional view showing an artificial lung device 100 1D according
to Embodiment 4. Hereinafter, portions of the artificial lung device 1001D which portions are
different from those of the artificial lung device 100 lA will be mainly described. It should be
noted that in FIG 10, reference sigos obtained by adding 300 to the reference sigos used in the
explanation of the artificial lung device 100 1A are used for the components of the artificial lung
device 100 1D which components correspond to the components of the artificial lung device
100 1A in terms of at least the functions.
[0160] As shown in FIG. 10, the artificial lung device 1001D includes a box-shaped housing
1302. The housing 1302 includes: a rectangular and tubular housing main body 1310 including
left and right openings; a suspending portion 1311 connected to an upper portion of the housing
main body 131 0; and two cap portions 1312 and 1313 which respectively close the left and right
openings of the housing main body 1310. The artificial lung device 1001D is configured such
that in an internal space 1302a of the housing 1302, the blood flows in the left-right direction, the
heat medium flows in the front-rear direction, and the gas flows in the upper-lower direction.
Hereinafter, details of such configuration will be described.
[0161] The artificiallung device 1001D includes: a blood inflow port 1316 into which the
venous blood flows; and a blood outflow port 1317 from which the blood having been adjusted
40
in temperature and subjected to the gas exchange in the artificial lung device 100 lD flows out as
the arterial blood. The blood inflow port 1316 is provided at a position of the right cap portion
1313 which position is located lower than a middle position in the upper-lower direction. The
blood outflow port 1317 is provided at a position of the left cap portion 1314 which position is
located lower than a middle position in the upper-lower direction. It should be noted that in FIG.
10, the position of the blood inflow port 1316 and the position of the blood outflow port 1317
coincide with each other in the upper-lower direction. However, the present embodiment is not
limited to this. The positions of the blood inflow port 1316 and the blood outflow port 1317 in
the upper-lower direction or the front-rear direction may be made different from each other.
[0162] Moreover, the artificial lung device 1001D includes: a gas supply port 1314 into
which oxygen-rich gas used for the gas exchange with the blood flows; and a gas discharge port
1315 from which the gas having been subjected to the gas exchange flows out. The gas supply
port 1314 is provided at an upper portion of the left cap portion 1312, and the gas discharge port
1315 is provided in the vicinity of a middle position of a bottom wall of the housing main body
1310. An upper portion of the internal space 1302a of the housing 1302 constitutes a gas
inflow space 1352 communicating with the gas supply port 1314, and a lower portion of the
internal space 1302a constitutes a gas outflow space 1353 communicating with the gas discharge
port 1315. Each of the gas inflow space 1352 and the gas outflow space 1353 forms a space
shape that is flat in the upper-lower direction. A heat exchange chamber 1320, a gas exchange
chamber 1321, and a blood outflow space 1322 are formed between the gas inflow space 1352
and the gas outflow space 1353.
[0163] A hollow fiber body (gas exchanger) 1340 having a rectangular solid shape is
provided between the gas inflow space 1352 and the gas outflow space 1353. A dimension of
the hollow fiber body 1340 in the front-rear direction is equal to an inside dimension of the
housing main body 1310 in the front-rear direction, and a dimension of the hollow fiber body
1340 in the left-right direction is smaller than a distance between inner surfaces of the cap
portions 1312 and 1313. Therefore, front and rear surfaces of the hollow fiber body 1340 are
respectively in contact with front and rear inner surfaces of the housing main body 1310. On
the other hand, the hollow fiber body 1340 is provided in the vicinity of a middle position in the
left-right direction so as to be separated from the cap portions 1312 and 1313 in the left-right
direction.
[0164] Then, a sealing member 1350 is provided so as to connect between an upper end
portion of the hollow fiber body 1340 and inner surfaces of the cap portions 1312 and 1313, and
a sealing member 1351 is provided so as to connect between a lower end portion of the hollow
41
fiber body 1340 and the inner surfaces of the cap portions 1312 and 1313. Therefore, a lower
portion of the gas inflow space 1352 is defmed by an upper end portion oftbe hollow fiber body
1340 and an upper end portion of the sealing member 1350, and an upper portion of tbe gas
outflow space 1353 is defined by a lower end portion of the hollow fiber body 1340 and a lower
end portion of the sealing member 1351.
[0165] Moreover, a plurality of hollow fibers constituting the hollow fiber body 1340
extend substantially in tbe upper-lower direction. Upper end portions of the plurality of hollow
fibers are open at the gas inflow space 1352, and lower end portions of the plurality of hollow
fibers are open at the gas outflow space 1353. Therefore, the gas having flowed into the gas
supply port 1314 enters from the gas inflow space 1352 through upper end openings of the
hollow fibers of the hollow fiber body 1340 into the inner holes of tbe hollow fibers of the
hollow fiber body 1340, flows through lower end openings of the hollow fibers of the hollow
fiber body 1340 to the gas outflow space 1353, and is discharged through tbe gas discharge port
1315 to the outside. Moreover, gaps exist among tbe hollow fibers, and tbe blood flows
through the gaps. Then, the gas exchange is performed between tbe blood flowing through the
gaps and tbe gas flowing through the inner holes of the hollow fibers. Therefore, a space in
which the hollow fiber body 1340 is provided constitutes the gas exchange chamber 1321.
[0 166] The heat exchange chamber 1320 is formed in a space located at the right side of the
hollow fiber body 1340, i.e., a space defmed by a right side surface of the hollow fiber body
1340, an inner surface of the right cap portion 1313, a lower surface of the sealing member 1350,
and an upper surface of the sealing member 1351.
[0167] A tube bundle 1360 constituted by an assembly of a plurality of heat exchange pipes
is arranged in the heat exchange chamber 1320 such tbat axes of tbe pipes extend in the
front-rear direction. The tube bundle 1360 is provided so as to block between tbe blood inflow
port 1316 and the hollow fiber body 1340. A medium inflow port (not shown) is provided at
one of front and rear walls oftbe housing main body 1310 and communicates with openings of a
first end of the tube bundle 1360. A medium outflow port (not shown) is provided at the other
of the front and rear walls of the housing main body 1310 and communicates with openings of a
second end of the tube bundle 1360.
[0 168] Therefore, the heat medium having flowed into the medium inflow port enters into
the pipes from tbe openings of the first end of the tube bundle 1360 and flows inside the pipes.
The heat medium flows out from the openings of the second end of tbe tube bundle 1360 and
then flows out through the medium outflow port to the outside. Moreover, gaps are provided
among tbe heat exchange pipes, and the blood flows through the gaps. Then, the heat exchange
42
is performed between the blood flowing through the gaps and the medium flowing through the
pipes. Therefore, a space in which the tube bundle 1360 is provided constitutes the heat
exchange chamber 1320.
[0169] Moreover, a filter structure 1330 and the blood outflow space 1322 are provided in a
space located at the left side of the hollow fiber body 1340, i.e., a space defmed by a left side
surface of the hollow fiber body 1340, an inner surface of the left cap portion 1312, the lower
surface of the sealing member 1350, and the upper surface of the sealing member 1351.
[0170] To be specific, the filter structure 1330 having a rectangular sheet shape is provided
along the left side surface of the hollow fiber body 1340. It should be noted that the filter
structure 1330 is bent such that an upper portion thereof projects toward the left side. In other
words, an upper end 1331 of the filter structure 1330 is in contact with the left side surface of an
upper portion of the hollow fiber body 1340, and a lower end 1332 of the filter structure 1330 is
in contact with the left side surface of a lower portion of the hollow fiber body 1340. Moreover,
a bent portion 1333 of the filter structure 1330 is provided at a predetermined position located
higher than a middle position in the upper-lower direction, and the bent portion 1333 is located
away from the left side surface of the hollow fiber body 1340 toward the left side. Therefore,
as shown in FIG. 10, a space defined by the hollow fiber body 1340 and the filter structure 1330
has a triangular shape having apexes that are the upper end 13 31, the lower end 13 3 2, and the
bent portion 1333. It should be noted that the shape of the filter structure 1330 is not limited to
the triangular shape and may be a dome shape that projects in a circular-arc shape toward the left
side. Moreover, as shown in FIG. 10, a lower portion of the filter structure 1330 may be
provided close to the left side surface of the hollow fiber body 1340. However, the present
embodiment is not limited to this. The lower portion of the filter structure 1330 may have such
a shape as to extend in the lower direction without contacting the left side surface of the hollow
fiber body 1340 or may have such a shape as to spread toward the left side away from the left
side surface of the hollow fiber body 1340.
[0171] Moreover, a space located at the left side of the filter structure 1330 in the space
located at the left side of the hollow fiber body 1340 constitutes the blood outflow space 1322,
and the blood outflow space 1322 communicates with the blood outflow port I 317. Therefore,
after foreign matters in the blood having flowed through the gas exchange chamber 1321 are
removed by the filter structure 1330, the blood flows through the blood outflow space 1322 and
is discharged through the blood outflow port 1317 to the outside.
[0172] In the artificial lung device lOOlD, a bubble guide portion 1390 is constituted by the
filter structure 1330 and the hollow fiber body 1340. Specifically, as shown in FIG. 10, the
43
filter structure 1330 includes an inclined surface 1334 at a portion connecting the upper end 1331
and the bent portion 1333. The inclined surface 1334 constitutes the opposing wall according
to the present invention. To be specific, the inclined surface 1334 is located so as to be opposed
to a left side surface 1341 of the hollow fiber body 1340 and forms a space (bubble storing
portion) 1391 between the inclined surface 1334 and the left side surface 1341 of the hollow
fiber body 1340. Moreover, a separation dimension D4 between a right side surface 1334a of
the inclined surface 1334 and the left side surface 1341 of the hollow fiber body 1340 gradually
decreases to become zero toward the vertically upper side.
[0173] According to this configuration, even when there are bubbles which flowed through
the hollow fiber body 1340 but were not absorbed, such bubbles flow upward in the bubble guide
portion 1390 along the right side surface 1334a of the inclined surface 1334 of the filter structure
1330 or the left side surface 1341 of the hollow fiber body 1340 by buoyancy of the bubbles.
Since the space 1391 included in the bubble guide portion 1390 gradually decreases in width
toward the upper side, the bubbles flowing upward gradually approach the hollow fiber body
1340. On this account, a larger amount of bubbles can be absorbed by the hollow fiber body
1340, and therefore, the bubbles can be prevented from being excessively accumulated in the
housing 1302.
In other words, in Embodiment 4 according to the second disclosure, a space is
constituted by the inside surface of the filter structure 1330 and the outer surface of the hollow
fiber body 1340 and constitutes the bubble guide portion 1390 or the bubble storing portion
1391.
[0174] Embodiment 5 according to Second Disclosure
FIG 11 is a front sectional view showing an artificial lung device 100 1E according
to Embodiment 5. Hereinafter, portions of the artificial lung device lOOlE which portions are
different from those of the artificial lung device 100 lD will be mainly described. It should be
noted that in FIG 11, reference signs each obtained by replacing "3" that is the third digit (except
for the alphabetical letter) in the reference signs used in the explanation of the artificial lung
device 1001D with "4" are used for the components of the artificial lung device lOOlE which
components correspond to the components of the artificial lung device 1 OOlE in terms of at least
the functions.
[0175] As shown in FIG. 11, the artificial lung device lOOlE includes a box-shaped housing
1402. The housing 1402 includes: a rectangular and tubular housing main body 1410 including
left and right openings; a suspending portion 1411 connected to an upper portion of the housing
main body 141 0; and two cap portions 1412 and 1413 which respectively close the left and right
44
openings of the housing main body 1410.
[0176] As with the artificial lung device !OOlD, the artificial lung device lOOlE is
configured such that in an internal space 1402a of the housing 1402, the blood flows in the
left-right direction, the heat medium flows in the front-rear direction, and the gas flows in the
upper-lower direction. To be specific, the blood flows into a blood inflow port 1416 connected
to the right cap portion 1413, flows in the left direction, flows through a heat exchange chamber
1420, a gas exchange chamber 1421, a filter structure 1430, and a blood outflow space 1422 in
this order, and flows to the outside through a blood outflow port 1417 connected to the left cap
portion 1412. The heat medium enters into openings of a first end of a tube bundle 1460
through a medium inflow port (not shown), flows inside the pipes in the front-rear direction,
flows out through openings of a second end of the tube bundle 1460, and flows through a
medium outflow port (not shown) to the outside. The gas for the gas exchange flows into a gas
inflow space 1452 through a gas supply port 1414located at the upper side, enters into inner
holes of hollow fibers of a hollow fiber body 1440 through upper end openings of the inner holes
of the hollow fibers, flows through lower end openings of the inner holes of the hollow fibers
into a gas outflow space 1453, and is discharged through a gas discharge port 1415 to the
outside.
[0177] It should be noted that: the blood flows through gaps of the pipes of the tube bundle
1460 in the heat exchange chamber 1420, and while flowing through the gaps of the pipes, the
temperature of the blood is adjusted; and the blood flows through the gaps of the hollow fibers of
the hollow fiber body 1440 in the gas exchange chamber 1421, and while flowing through the
gaps of the hollow fibers, the blood is subjected to the gas exchange. Moreover, the blood
having flowed through the hollow fiber body 1440 further passes through the filter structure
1430 arranged at the left side of the hollow fiber body 1440 (i.e., at the downstream side of the
hollow fiber body 1440 in the flow direction of the blood) and then flows through the blood
outflow space 1422 to the blood outflow port 1417.
[0178] An inner surface 1470 of the left cap portion 1412 is located so as to be opposed to a
left side surface 1441 of the hollow fiber body 1440. It should be noted that a portion of the
inner surface 1470 which portion extends from a lower end to a predetermined position PI
located higher than a middle position in the upper-lower direction constitutes a vertical surface
1471 extending substantially along the vertical direction. On the other hand, an upper portion
of the inner surface 14 70 which portion is located higher than the position Pl constitutes an
inclined surfuce 1472 which extends toward the right side as it extends upward. Therefore, a
separation dimension between the vertical surface 1471 located at the lower side in the inner
45
surface 1470 of the cap portion 1412 and the hollow fiber body 1440 is substantially constant at
any position in the upper-lower direction. On the other hand, a separation dimension D5
between the inclined surface 1472located at the upper side of the position P1 and the hollow
fiber body 1440 gradually decreases to become zero toward the vertically upper side. A space
(bubble storing portion) 1491 is formed between the inclined surface 1472 and the hollow fiber
body 1440. Therefore, the inclined surface 14 72 constitutes the opposing wall according to the
present invention, and a bubble guide portion 1490 is constituted by the inclined surface 1472
and the left side surface 1441 of the hollow fiber body 1440.
[0179] The filter structure 1430 is formed in a rectangular flat sheet shape. The filter
structure 1430 is provided such that: an upper end thereof is located at a portion (connection
portion where the vertical surface 1471 and the inclined surface 1472 are connected to each
other) of the inner surface 1470 of the cap portion 1412 which portion corresponds to the
position P1; and a lower end thereof is located at a connection portion where a lower portion of
the hollow fiber body 1440 and a sealing member 1451 are connected to each other. To be
specific, the filter structure 1430 is provided so as to cross a passage through which the blood
having flowed through the hollow fiber body 1440 flows toward the blood outflow port 1417,
and foreign matters are removed from the blood passing through the filter structure 1430. It
should be noted that the shape of the filter structure 1430 is not limited to the shape shown in
FIG. 11 and may be an arch shape projecting to the left side. Moreover, as shown in FIG. 11, a
lower portion of the filter structure 1430 may be provided close to the left side surface of the
hollow fiber body 1440. However, the present embodiment is not limited to this. The lower
portion of the filter structure 1430 may have such a shape as to extend in the lower direction
without contacting the left side surface of the hollow fiber body 1440.
[0180] According to this configuration, even when there are bubbles which flowed through
the hollow fiber body 1440 but were not absorbed, such bubbles flow upward in the bubble guide
portion 1490 along the inclined surface 1472 of the cap portion 1412 or the left side surface 1441
of the hollow fiber body 1440 by buoyancy of the bubbles. Since the space 1491 included in
the bubble guide portion 1490 gradually decreases in width toward the upper side, the bubbles
flowing upward gradually approach the hollow fiber body 1440. On this account, a larger
amount of bubbles can be absorbed by the hollow fiber body 1440, and therefore, the bubbles
can be prevented from being excessively accumulated in the housing 1402. In other words, in
Embodiment 5 according to the second disclosure, a space is constituted by the inner wall
surface of the housing 1402, the inside surface of the filter structure 1430, and the outer surfuce
of the hollow fiber body 1440 and constitutes the bubble guide portion 1490 or the bubble
46
storing portion 1491.
[0 181] Embodiment 6 according to Second Disclosnre
FIG 12 is a front sectional view showing an artificial lung device 100 IF according
to Embodiment 6. The artificial lung device lOOIF is of a so-called vertical type and includes a
housing 1502 and an inner tube 1503. It should be noted that in FIG. 12, reference signs
obtained by adding 500 to the reference signs used in the explanation of the artificial lung device
100 IA are used for the components of the artificial lung device 100 IF which components
correspond to the components of the artificial lung device 1001Ain terms of at least the
functions.
[0182] As shown in FIG. 12, according to the artificial lung device lOOIF, a heat exchange
chamber 1520 and a gas exchange chamber 1521 are formed in the housing 1502. The
temperature of the venous blood having flowed into the housing 1502 is adjusted. In addition,
carbon dioxide is removed from the blood, and oxygen is added to the blood. Then, the blood
as the arterial blood flows to the outside. The housing 1502 includes a cylindrical housing main
body 1510, a frrst header 1512 provided at an upper opening of the housing main body 1510, and
a second header 1513 provided at a lower opening of the housing main body 1510.
[0183] The cylindrical housing main body 1510 is arranged such that an axis thereof
extends in the vertical direction. The upper opening of the housing main body 1510 is closed
by the frrst header 1512. The frrst header 1512 is formed in a cup shape including an opening
directed downward. A suspending tooll511 is connected to an upper portion of the frrst header
1512. Moreover, a gas supply port (not shown) is connected to a peripheral portion of the frrst
header 1512, and oxygen-rich gas is introduced into the housing 1502.
[0184] The second header 1513 provided at the lower opening of the housing main body
1510 is formed in a cup shape including an opening directed upward. An opening 1513a is
formed at a middle position of the second header 1513. Moreover, a gas discharge port (not
shown) is connected to a peripheral portion of the second header 1513, and the gas is discharged
from the housing 1502 to the outside.
[0185] A tubular hollow fiber body 1540 is accommodated in an internal space 1502a of the
housing 1502 so as to be externally fitted to a tubular core 1505. To be specific, the hollow
fiber body 1540 is constituted by a sheet-shaped hollow fiber membrane formed by a plurality of
hollow fibers. The hollow fiber membrane is wound around an outer periphery of the tubular
core 1505 and is accommodated in the housing 1502 together with the tubular core 1505.
Moreover, instead of directly winding the hollow fiber membrane around the tubular core 1505,
a hollow fiber membrane bundle formed in a cylindrical shape in advance may cover the tubular
47
core 1505 and be accommodated in tbe housing 1502. The tubular core 1505 is located
coaxially witb tbe housing main body 1510. A ring-shaped space between the tubular core
1505 and tbe housing main body 1510 constitutes the gas exchange chamber 1521 and is filled
with the hollow fiber body 1540.
[0186] A first sealing member 1550 having an annular shape is provided at the upper side of
the hollow fiber body 1540, and a second sealing member 1551 having an annular shape is
provided at tbe lower side of the hollow fiber body 1540. A gas inflow space 1552
communicating witb tbe gas supply port is formed at the upper side of the first sealing member
1550 by the first sealing member 1550. A gas outflow space 1553 communicating with the gas
discharge port is formed at the lower side of the second sealing member 15 51 by the second
sealing member 1551. Therefore, the gas supplied from the gas supply port at the upper portion
flows from tbe gas inflow space 1552 through the inner holes of the hollow fibers of the hollow
fiber body 1540 toward the lower side, flows through the gas outflow space 1553, and is
discharged through the gas discharge port at the lower portion to the outside. It should be noted
that the second sealing member 1551 is provided so as to be externally fitted to a lower portion
oftbe tubular core 1505.
[0187] A cylindrical heat exchanger casing 1503 is provided so as to be internally fitted in
tbe tubular core 1505 except for a lower portion of the heat exchanger casing 1503. The lower
portion of the heat exchanger casing 1503 projects downward from a lower opening of the
tubular core 1505 and further projects downward from the opening 1513a of tbe second header
1513 to be exposed to the outside. A lower end opening oftbe heat exchanger casing 1503 is
closed by a bottom cap 1570. A medium inflow port 1518 and a medium outflow port 1519 are
connected to a lower side surface of the heat exchanger casing 1503.
[0 188) The bottom cap 1570 is formed in a cup shape including an opening directed upward.
A blood inflow port 1516 is connected to a peripheral portion of the bottom cap 1570. The
medium inflow port 1518 extends in an obliquely downward direction from a predetermined
position of the lower side surface oftbe heat exchanger casing 1503. The medium outflow port
1519 extends in an obliquely downward direction from a predetermined position of the lower
side surface oftbe heat exchanger casing 1503, tbe predetermined position being different from
the position to which tbe medium inflow port 1518is connected.
[0189] The inside of the heat exchanger casing 1503 constitutes the heat exchange chamber
1520. A tube bundle 1560 is accommodated in tbe heat exchange chamber 1520 such that an
axial direction of the tube bundle 1560 coincides with an axial direction of the heat exchanger
casing 1503. The tube bundle 1560 is an assembly of a plurality of heat exchange pipes. The
48
pipes are made of a material, such as stainless steel, having high heat conductivity. An outer
periphery of an upper end portion of the tube bundle 1560 is sealed by a sealing member (not
shown) such that the heat exchange medium and the blood having flowed out from the tube
bundle 1560 are prevented from being mixed with each other.
[0190] ln the heat exchange chamber 1520, when the blood flows into the blood inflow port
1516located at the lower side, the blood enters into the pipes of the tube bundle 1560 from lower
end openings of the pipes, flows upward, and flows out from the tube bundle 1560 through upper
end openings of the pipes. On the other hand, the heat medium which is maintained at a
predetermined temperature flows into the medium inflow port 1518, flows through the gaps of
the pipes of the tube bundle 1560, and flows out from the medium outflow port 1519.
[0191] A diffusing portion 1571 is provided above the heat exchanger casing 1503 so as to
be fitted to an opening portion of the first sealing member 1550 having an annular shape. As
shown in FIG 12, a lower surface of the diffusing portion 1571 projects downward in a
circular-arc shape in a front view. Therefore, the flow direction ofthe blood having flowed out
from the upper portion of the tube bundle 1560 is changed to a radially outward direction by the
diffusing portion 1571, and the blood flows into the gas exchange chamber 1521 from an upper
portion of the gas exchange chamber 1521.
[0192] An enlarged diameter portion 1572 is formed at a lower portion of the housing main
body 1510 so as to be larger in diameter than the other portion of the housing main body 1510
over the entire periphery. The enlarged diameter portion 1572 includes: a peripheral surface
portion 1573 constituted by a tubular body; an armular upper surface portion 1574 covering an
upper end opening of the peripheral surface portion 1573; and an annular lower surface portion
1575 covering alower end opening of the peripheral surface portion 1573. The annular upper
surface portion 1574 is inclined such that an inner peripheral portion 1576 is located higher than
an outer peripheral portion 1577. ln other words, the upper surface portion 1574 is formed in a
substantially truncated cone shape. Therefore, an inner surface (lower surface) of the upper
surface portion 1574 constitutes an inclined surface 1574a which approaches a center as it
extends upward.
[0193] A space is formed between the inner surface of the enlarged diameter portion 1572
and an outer peripheral surface 1541 of the hollow fiber body 1540, and a filter structure 1530 is
arranged in the space. The filter structure 1530 is formed in a truncated cone shape including a
top portion directed downward. An upper end (large-diameter end) of the filter structure 1530
is located at a connection portion where the peripheral surface portion 1573 and the upper
surface portion 1574 in the enlarged diameter portion 1572 are connected to each other. A
49
lower end (small-diameter end) of the filter structure 1530 is located at a contact portion where
the lower surface portion 1575 of the enlarged diameter portion 1572 and the hollow fiber body
1540 contact each other. Moreover, a blood outflow port 1517 extending in the radially
outward direction is connected to a predetermined position of the peripheral surface portion 1573
of the enlarged diameter portion 1572.
[0194] Therefore, the inside of the enlarged diameter portion 1572 is divided by the filter
structure 1530 into a space I 59 I located adjacentto the hollow fiber body 1540 and a blood
outflow space 1522 communicating with the blood outflow port 1517. Then, the blood having
flowed through the hollow fiber body 1540 passes through the filter structure 1530 from the
space 1591, flows through the blood outflow space 1522, and flows through the blood outflow
port 1517 to the outside.
[0195] According to the artificial lung device IOOIF configured as above, while the blood
having flowed into the blood inflow port 1516 flows through the tube bundle 1560 of the heat
exchange chamber 1520 to the upper side, the temperature ofthe blood is adjusted by the
medium having flowed into the medium inflow port 1518. The blood having been adjusted in
temperature makes a tum at the upper side of the heat exchange chamber 1520 and flows into the
gas exchange chamber 1521. While the blood flows through the gaps of the hollow fibers of
the hollow fiber body 1540, the blood is subjected to the gas exchange. Then, foreigo matters
in the blood having flowed out from the hollow fiber body 1540 are removed by the filter
structure 1530, and the blood as the arterial blood flows to the outside.
[0196] In the artificial lung device 100 IF, a bubble guide portion 1590 is constituted by the
upper surface portion 1574 of the enlarged diameter portion 1572 and the hollow fiber body
1540. More specifically, as shown in FIG. 12, the inner surface of the upper surface portion
1574 constitutes the inclined surface 1574a as described above, and the inclined surface 1574a
constitutes the opposing wall according to the present invention. To be specific, the inclined
surface 1574a is located so as to be opposed to the outer peripheral surface 1541 of the hollow
fiber body 1540 and forms the space (bubble storing portion) 1591 between the inclined surface
1574a and the outer peripheral surface 1541. Moreover, a separation dimension D6 between
the inclined surface 1574a and the outer peripheral surface 1541 of the hollow fiber body 1540
gradually decreases to become zero toward the vertically upper side.
[0197] According to this configuration, even when there are bubbles which flowed through
the hollow fiber body 1540 but were not absorbed, such bubbles flows upward in the bubble
guide portion 1590 along the inclined surface 1574a ofthe enlarged diameter portion 1572 or the
outer peripheral surface 1541 of the hollow fiber body 1540 by buoyancy of the bubbles. Since
50
the space 1591 included in the bubble guide portion 1590 gradually decreases in width toward
the upper side, the bubbles flowing upward gradually approach the hollow fiber body 1540. On
this account, a larger amount of bubbles can be absorbed by the hollow fiber body 1540, and
therefore, the bubbles can be prevented from being excessively accumulated in the housing 1502.
In other words, in Embodiment 6 according to the second disclosure, a space is constituted by
the inner wall of the housing 1502, the inside surface of the filter structure 1530, and the outer
surface of the hollow fiber body 1540 and constitutes the bubble guide portion 1590 or the
bubble storing portion 1591.
[0198] Embodiment 7 according to Second Disclosure
FIG 13 is a front sectional view showing an artificial lung device 1001 G according
to Embodiment 7. Hereinafter, portions of the artificial lung device 1001G which portions are
different from those of the artificial lung device 1001F will be mainly described. It should be
noted that in FIG 13, reference signs each obtained by replacing "5" that is the third digit (except
for the alphabetical letter) in the reference signs used in the explanation of the artificial lung
device 1001F with "6" are used for the components of the artificial lung device 1001G which
components correspond to the components of the artificial lung device 100 1F in terms of at least
the functions.
[0199] As shown in FIG. 13, in the artificial lung device 1001 G, the enlarged diameter
portion is not provided at a lower portion of a housing main body 1610. To be specific, the
housing main body 1610 is formed in a cylindrical shape having a substantially constant
diameter from its upper end to its lower end. A blood outflow port 1617 is connected to a lower
end portion of the housing main body 1610. Moreover, an inner peripheral surface of a tubular
hollow fiber body 1640 wound around an outer periphery of a tubular core 1605 is in contact
with an outer peripheral surface of the tubular core 1605. However, an outer peripheral surface
of the hollow fiber body 1640 is located so as to be spaced apart from an inner peripheral surface
of the housing main body 1610 by a predetermined distance. Therefore, a cylindrical space is
formed between the housing main body 1610 and the hollow fiber body 1640 over the entire
periphery, and a cylindrical filter structure 1630 is provided in this space.
[0200] The filter structure 1630 has a diameter larger than an outer diameter of the hollow
fiber body 1640 and is provided so as to surround an outer periphery of the hollow fiber body
1640. An upper end 1631 of the filter structure 1630 is in contact with a lower surface of a first
sealing member 1650, and a lower end 1632 of the filter structure 1630 is in contact with an
upper surface of a second sealing member 1651. Moreover, the filter structure 1630 is arranged
eccentrically with respect to the hollow fiber body 1640. Therefore, a part of an inner
51
peripheral surface ofthe filter structure 1630 in a circumferential direction is located so as to be
spaced apart from an outer peripheral surface 1641 of the hollow fiber body 1640, and the other
part of the irmer peripheral surfuce of the filter structure 1630 in the circumferential direction is
in contact with the outer peripheral surface 1641. Then, a space sandwiched between the filter
structure 1630 and the housing main body 1610 constitutes a bubble outflow space 1622
communicating with the bubble outflow port 1617.
[020 1] A bent portion 1633 is provided at a predetermined position of an upper portion of a
part of the filter structure 1630, the part being spaced apart from the outer peripheral surface
1641 of the hollow fiber body 1640. An inner surface of a part of the filter structure 1630
which part connects the bent portion 1633 and the upper end 1631 constitutes an inclined surface
1634. In the artificial lung device IOOlG, a bubble guide portion 1690 is constituted by the
inclined surface 1634 and the outer peripheral surface 1641 of the hollow fiber body 1640. To
be specific, the inclined surface 1634 constitutes the opposing wall according to the present
invention. The inclined surface 1634 is located so as to be opposed to the outer peripheral
surface 1641 of the hollow fiber body 1640 and forms a space (bubble storing portion) 1691
between the inclined surface 1634 and the outer peripheral surface 1641 of the hollow fiber body
1640. Moreover, a separation dimension D7 between the inclined surface 1634 and the outer
peripheral surface 1641 of the hollow fiber body 1640 gradually decreases to become zero
toward the vertically upper side.
[0202] According to this configuration, even when there are bubbles which flowed through
the hollow fiber body 1640 but were not absorbed, such bubbles move upward in the bubble
guide portion 1690 along the inclined surface 1634 of the filter structure 1630 or the outer
peripheral surface 1641 of the hollow fiber body 1640 by buoyancy of the bubbles. Since the
space 1691 included in the bubble guide portion 1690 gradually decreases in width toward the
upper side, the bubbles flowing upward gradually approach the hollow fiber body 1640. On
this account, a larger amount of bubbles can be absorbed by the hollow fiber body 1640, and
therefore, the bubbles can be prevented from being excessively accumulated in a housing 1602.
In other words, in Embodiment 7 according to the second disclosure, a space is constituted by
the inside surface of the filter structure 1630 and the outer surface of the hollow fiber body 1640
and constitutes the bubble guide portion 1690 or the bubble storing portion 1691.
[0203] Embodiment 8 according to Second Disclosure
FIG 14 is a front sectional view showing an artificial lung device 1001H according
to Embodiment 8. Hereinafter, portions of the artificial lung device 100 lH which portions are
different from those of the artificial lung device 1001 G will be mainly described. It should be
52
noted that in FIG 14, reference signs each obtained by replacing "6" that is the third digit (except
for the alphabetical letter) in the reference signs used in the explanation of the artificial lung
device lOOlG with "7" are used for the components of the artificial lung device lOOlH which
components correspond to the components of the artificial lung device lOOlG in terms of at least
the functions.
[0204] As shown in FIG. 14, in the artificial lung device 100 lH, a tubular hollow fiber body
1740 is formed such that a hollow fiber membrane is wound around a tubular core 1705.
Moreover, a tubular filter structure 1730 is included so as to be externally fitted to the hollow
fiber body 1740. An inner diameter of the filter structure 1730 is substantially equal to an outer
diameter of the hollow fiber body 1740. Therefore, an outer peripheral surface of the hollow
fiber body 1740 is in contact with an inner peripheral surface of the filter structure 1730 over the
substantially entire region.

CLAIMS

1. An artificial lung device comprising:
a housing including a blood inflow port and a blood outflow port and arranged such
that a center axis of the housing is directed in a lateral direction;
a gas exchanger arranged in the housing and configured to perform gas exchange
with respect to blood while the blood flows from the blood inflow port to the blood outflow port;
a filter structure arranged around the gas exchanger;
an opposing wall arranged so as to be opposed to a surface of the gas exchanger; and
a space constituted by the opposing wall and/or the filter structure, wherein
the opposing wall includes an inclined surface inclined toward the gas exchanger,
and/or the filter structure includes an inclined surface inclined toward the gas exchanger.
2. The artificial lung device according to claim 1, wherein:
the gas exchanger is formed in a columnar shape such that a center axis of the gas
exchanger is directed in the lateral direction in the housing;
the space constitutes a bubble guide portion by which bubbles having flowed
through the gas exchanger by flow of the blood are guided to the gas exchanger again in the
housing;
the bubble guide portion includes a straightening surface provided so as to cross a
passage extending from the gas exchanger to the blood outflow port;
the straightening surface is provided so as to be opposed to an outer peripheral
surface of the gas exchanger and surround the gas exchanger; and
the straightening surface includes
a first straightening surface provided at a relatively lower side and inclined such
that a downstream portion of the first straightening surface in a flow direction of the blood is
located closer to the outer peripheral surface of the gas exchanger than an upstream portion of
the first straightening surface in the flow direction of the blood and
a second straightening surface provided at a relatively upper side and located
closer to the outer peripheral surface of the gas exchanger than the upstream portion of the first
straightening surface, the second straightening surface being inclined differently from the first
straightening surface.
3. The artificial lung device according to claim 2, wherein, a filter is provided at the
straightening surface.
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4. The artificial lung device according to claim 2 or 3, wherein:
an opening is formed at the first straightening surface; and
a filter is provided at the opening.
5. The artificial lung device according to any one of claims 2 to 4, wherein:
the second straightening surface is located so as to be spaced apart from the outer
peripheral surface of the gas exchanger by a predetermined distance; and
a bubble storing portion is formed between the second straightening surface and the
outer peripheral surface of the gas exchanger.
6. The artificial lung device according to any one of claims 2 to 5, wherein at least the
second straightening surface of the straightening surface is constituted by an inner wall surface
ofthe housing.
7. The artificial lung device according to any one of claims 1 to 6, wherein a filter is
provided at the blood outflow port.
8. The artificial lung device according to claim 7, wherein the filter is formed in a
columnar shape such that a dimension of the filter in a flow direction of the blood in the blood
outflow port is larger than an inner diameter of the blood outflow port.
9. The artificial lung device according to claim 5, further comprising a bubble trap
portion provided downstream of the bubble storing portion.
10. The artificial lung device according to claim 9, wherein the bubble trap portion
includes an air vent port.
11. An artificial lung device comprising:
a housing formed in a tubular shape including both end portions that are closed, the
housing including a blood inflow port and a blood outflow port and arranged such that a center
axis of the housing is directed in a lateral direction;
a gas exchanger arranged in the housing and configured to perform gas exchange
with respect to blood while the blood flows from the blood inflow port to the blood outflow port;
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a filter structure provided around the gas exchanger; and
a bubble storing portion provided between the filter structure and the gas exchanger,
wherein
the bubble storing portion is located at an upper side of the housing and faces the gas
exchanger.
12. The artificial lung device according to claim II, wherein the bubble storing portion
includes an inner peripheral surface of the straightening frame and an outer peripheral surface of
the gas exchanger.
13. The artificial lung device according to claim 11 or 12, wherein the straightening
frame includes an inclined straightening surface located close to the gas exchanger.
14. The artificial lung device according to any one of claims 11 to 13, further comprising
a bubble trap portion provided downstream of the bubble storing portion.
15. The artificial lung device according to claim 14, wherein the bubble trap portion
includes an air vent port.
16. The artificial lung device according to claim 1, wherein a separation dimension
between the surface of the gas exchanger and the opposing wall gradually decreases to approach
zero toward a vertically upper side or toward a downstream side in a flow direction of the blood
in the space.
17. The artificial lung device according to claim 16, wherein:
the filter structure configured to remove foreign matters in the blood is provided so
as to cross a passage such that at least part of an inside surface of the filter structure contacts the
surface of the gas exchanger, the passage being a passage through which the blood having
flowed through the gas exchanger flows toward the blood outflow port; and
the filter structure constitutes the opposing wall.
18. The artificial lung device according to claim 17, wherein:
the gas exchanger is provided such that part of the surface of the gas exchanger
contacts an inner wall surface of the housing; and
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the inner wall surface of the housing constitutes the opposing wall.
19. The artificial lung device according to claim 18, further comprising a heat exchanger
arranged in the housing and configured to adjust a temperature of the blood having flowed into
the heat exchanger through the blood inflow port and deliver to the gas exchanger the blood
having been adjusted in temperature, wherein:
the gas exchanger is formed in a tubular shape surrounding the heat exchanger;
a tubular wall is provided between the heat exchanger and the gas exchanger so as to
separate the heat exchanger and the gas exchanger from each other; and
the bubble guide portion is formed by an inner peripheral surface of the gas
exchanger and a portion of the tubular wall which portion is opposed to the inner peripheral
surface of the gas exchanger.
20. The artificial lung device according to any one of claims 1 to 19, wherein:
the housing includes an attaching portion to which the blood outflow port is
attached; and
a base end-side portion of the blood outflow port is attached to the attaching portion
such that the blood outflow port is rotatable about an axis of the base end-side portion.
21. The artificial lung device according to claim 20, wherein the blood outflow port is
bent such that a tip end-side portion of the blood outflow port forms a predetermined angle with
respect to the axis of the base end-side portion.
22. The artificial lung device according to claim 20 or 21, wherein:
the attaching portion is formed in a substantially cylindrical shape;
an inner peripheral surface of the attaching portion includes an engaging portion;
the base end-side portion of the blood outflow port is attached to the attaching
portion; and
the base end-side portion of the blood outflow port includes an engaged portion
which is engaged with the engaging portion when the base end-side portion of the blood outflow
port is attached to the attaching portion.
23. The artificial lung device according to claim 22, wherein:
one of the engaging portion and the engaged portion is constituted by a plurality of
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engagement pieces arranged so as to be spaced apart from each other in a circumferential
direction;
each of the engagement pieces is formed in a tapered shape that projects inward in a
radial direction as the engagement piece extends upward; and
the other of the engaging portion and the engaged portion is arranged so as to
correspond to the engagement pieces, is formed so as to project outward in the radial direction,
and is engaged with the plurality of engagement pieces so as to be located higher than the
plurality of engagement pieces.
24. The artificial lung device according to any one of claims 20 to 23, further
comprising frrst and second sealing members configured to seal between an outer peripheral
surface ofthe base end-side portion and an inner peripheral surface of the attaching portion,
wherein:
the first sealing member is arranged at a portion of an outer peripheral surface of the
base end-side portion of the blood outflow port which portion is closer to a base end of the blood
outflow port than the second sealing member; and
compressibility of the second sealing member is higher than compressibility of the
frrst sealing member.
25. The artificial lung device according to any one of claims 20 to 24, wherein:
the base end-side portion of the blood outflow port projects from the housing main
body toward one side in an upper-lower direction;
a tip end-side portion of the blood outflow port is connected to the base end-side
portion through a bent portion and is inclined outward in a radial direction so as to be directed
toward one side in the upper-lower direction relative to the base end-side portion; and
the blood outflow port includes a holding portion formed at the bent portion so as to
project from the bent portion toward one side in the upper-lower direction.
26. An artificial lung device comprising:
a tubular housing including both ends that are closed;
a heat exchanger provided in the housing and configured to perform heat exchange
with respect to blood;
a gas exchanger arranged around an axial direction of the heat exchanger in the
housing and configured to be in fluid communication with the heat exchanger and perform gas
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exchange with respect to the blood;
a heat medium partial chamber which is arranged between the heat exchanger and
the gas exchanger and around the axial direction of the heat exchanger and through which a heat
medium flowing in and out from the heat exchanger flows;
a blood inflow port provided at a first end side of the housing and configured to be in
fluid communication with the heat exchanger;
a blood outflow port provided at the housing and configured to be in fluid
communication with the gas exchanger;
a medium inflow port and a medium outflow port which are provided at a second
end side of the housing and are in fluid communication with the heat medium partial chamber;
and
a bridge structure forming
a blood passage through which the blood flows in a radial direction from the
heat exchanger through a second end side of the heat medium partial chamber to the gas
exchanger and
a medium passage through which the heat medium flows in the axial direction
between the medium inflow port and the heat medium partial chamber and between the medium
outflow port and the heat medium partial chamber.
27. The artificial lung device according to claim 26, wherein:
the heat exchanger includes
a blood chamber configured to be in fluid communication with the blood inflow
port and the blood outflow port and
a heat exchange portion configured to be in fluid communication with the
medium inflow port and the medium outflow port, a heat medium flowing through the heat
exchange portion;
the heat medium partial chamber includes
a fust heat medium partial chamber provided around an axial direction of the
blood chamber and communicating with the medium inflow port and
a second heat medium partial chamber provided around the axial direction of the
blood chamber and communicating with the medium outflow port;
the medium passage includes
a first medium passage through which the medium inflow port and the first heat
medium partial chamber are in fluid communication with each other;
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a second medium passage through which the second heat medium partial
chamber and the medium outflow port are in fluid communication with each other;
a passage sectional area of the first medium passage is smaller than a passage
sectional area of the medium inflow port; and
a passage sectional area of the second medium passage is smaller than a passage
sectional area of the medium outflow port.
28. The artificial lung device according to claim 27, wherein the heat exchange portion
includes an extending portion provided between a group of the first heat medium partial chamber
and the second heat medium partial chamber and a group of the medium inflow port and the
medium outflow port.
29. The artificial lung device according to claim 28, wherein:
the extending portion includes a first chamber into which the heat medium flows
from the medium inflow port and from which the heat medium flows out to the first heat medium
partial chamber; and
the first chamber has a passage sectional area larger than the passage sectional area
of the medium inflow port.
30. The artificial lung device according to claim 29, wherein:
the first chamber includes a first chamber outlet configured to be in fluid
communication with the first heat medium partial chamber; and
a passage sectional area of the first chamber outlet is smaller than the passage
sectional area of the medium inflow port.
31. The artificial lung device according to any one of claims 26 to 30, wherein:
the extending portion includes a second chamber into which the heat medium flows
from the second heat medium partial chamber and from which the heat medium flows out to the
medium outflow port; and
the second chamber has a passage sectional area larger than a passage sectional area
of the medium outflow port.
32. The artificial lung device according to claim 31, wherein:
the second chamber includes a second chamber inlet configured to be in fluid
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communication with the second heat medium partial chamber; and
a passage sectional area of the second chamber inlet is smaller than the passage
sectional area of the medium outflow port.
33. The artificial lung device according to any one of claims 26 to 32, wherein:
the gas exchanger includes a gas exchange chamber configured to perform gas
exchange with the blood; and
the artificial lung device comprises a middle tube arranged in the housing and
forming the gas exchange chamber together with an inner peripheral surface of the housing.
34. The artificial lung device according to any one of claims 26 to 33, further
comprising an inner tube which forms part of the heat exchange portion and in which the blood
chamber is provided.
35. The artificial lung device according to claim 33 or 34, wherein:
the middle tube includes
a middle tube main body portion,
a dividing wall portion arranged so as to be spaced apart from an end portion of
the middle tube main body portion, the end portion being located close to the medium inflow
port, and
a plurality of hollow tubular supporting portions extending between the dividing
wall portion and the end portion of the middle tube main body portion, the heat medium flowing
inside the plurality of tubular supporting portions;
the blood passage is formed between the end portion of the middle tube main body
portion and the dividing wall portion; and
the plurality of tubular supporting portions include
one or a plurality of first supporting portions arranged so as to intersect with the
blood passage and constituting the first medium passage and
one or a plurality of second supporting portions arranged so as to intersect with
the blood passage and constituting the second medium passage.
36. The artificial lung device according to claim 35, wherein:
a total of passage sectional areas of the first supporting portions is equal to or more
than a passage sectional area of the medium inflow port; and
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a total of passage sectional areas of the second supporting portion is equal to or more
than a passage sectional area of the medium outflow port.
37. The artificial lung device according to claim 35 or 36, wherein:
the dividing wall portion constitutes part of the extending portion; and
the first chamber and the second chamber are provided at the dividing wall portion.
38. The artificial lung device according to any one of claims 35 to 37, wherein the
dividing wall portion is formed in a mortar shape that is recessed toward the heat exchange
portion.
39. The artificial lung device according to any one of claims 34 to 38, wherein the inner
tube includes:
a plurality of first heat medium holes provided so as to be lined up in an axial
direction of the inner tube and configured to be in fluid communication with the blood chamber
and the first heat medium partial chamber; and
a plurality of second heat medium holes provided so as to be lined up in the axial
direction of the inner tube and configured to be in fluid communication with the bloodchamber
and the second heat medium partial chamber.
40. The artificial lung device according to claim 39, wherein:
the first heat medium holes and the second heat medium holes are the same in size as
each other; and
the first heat medium holes are arranged symmetrically with respect to the second
heat medium holes across the blood chamber.