text:
Apparatus Comprising a Drive Cable for a Medical Device
An article comprising a drive cable suitable for high-speed operation in an anatomy having small-radii bends is disclosed. The drive cables disclosed herein include one or more physical adaptations that enable them to be "tuned" to avoid large amplitude vibrations during operation.
Shifflette, Michael J. (Alachua, FL, US)
MEDICAL VALUE PARTNERS, LLC (Los Angeles, CA, US)
A61M1/10
20100021947 Detection meter and mode of operation January, 2010 Emery et al.
20090131744 Sexual Aid Device May, 2009 Pattenden
20070282165 Optically coupled endoscope with microchip December, 2007 Hopkins et al.
20040015056 Medical-information providing apparatus and portable telephone January, 2004 Shinoda
20080208070 Defibrillator with Automatic Shock First/Cpr First Algorithm August, 2008 Snyder et al.
20080269540 SEED CARTRIDGE ADAPTOR AND METHODS FOR USE THEREWITH October, 2008 Lamoureux
20060058639 Subject moving apparatus and imaging apparatus March, 2006 Izuhara et al.
20070088189 Pelvic implant with anchoring frame April, 2007 Levy
20080139969 Fabric Sensor and a Garmet Incorporating the Sensor June, 2008 Gough et al.
20030220588 Electrically conductive guide wire November, 2003 Tenerz et al.
20090247880 ULTRASONIC DIAGNOSIS SYSTEM AND PUMP APPARATUS October, 2009 Naruse et al.
LEE, YUN H
Kaplan Breyer Schwarz, LLP (Matawan, NJ, US)
1. An article comprising a rotary drive cable, wherein the drive cable comprises: (a) a first coil; and (b) at least a first physical adaptation that affects a dynamic response of the drive cable, wherein the first physical adaptation is selected as a function of a forcing frequency to prevent harmonic resonance in the drive cable.
2. The article of claim 1 wherein the forcing frequency is greater than 20,000 rpm.
3. The article of claim 1 wherein the forcing frequency is in a range of about 1000 rpm to about 100,000 rpm.
4. The article of claim 1 wherein the dynamic response that is affected by the first physical adaptation is a vibrational characteristic of the drive cable.
5. The article of claim 1 and further wherein the first adaptation affects a characteristic of the drive cable, wherein the characteristic is selected from the group consisting of drive-cable tension, localized drive-cable bending stiffness, and localized drive-cable linear density.
6. The article of claim 1 wherein the first physical adaptation comprises at least one additional coil, wherein the additional coil and the first coil are linearly coupled.
7. The article of claim 6 further comprising a second physical adaptation, wherein the second physical adaptation is at least one collar for coupling the first coil and the at least one additional coil to each other.
8. The article of claim 6 further comprising a second physical adaptation, wherein the second physical adaptation is at least one rod, wherein the rod is disposed between the first coil and the additional coil such that the coils and rod form a linear arrangement.
9. The article of claim 8 further comprising a plurality of collars, wherein the collars couple each one of the coils to a respective rod.
10. The article of claim 1 wherein the first physical adaptation is at least one collar, wherein the collar is disposed on the first coil and does not couple the first coil to another coil or to a rod.
11. The article of claim 10 wherein there is a plurality of collars disposed on the first coil.
12. The article of claim 11 wherein the plurality of collars are identical to one another.
13. The article of claim 11 wherein at least one of the collars differs from the other of the collars in terms of at least one characteristic selected from the group consisting of length, diameter, stiffness, and mass.
14. The article of claim 1 wherein the first coil is a machined coil, and the first physical adaptation is a variation in size of a material that forms the first coil.
15. The article of claim 1 wherein the first physical adaptation comprises at least one bound section of the first coil.
16. The article of claim 1 wherein the first coil comprises an encapsulating material.
17. The article of claim 1 wherein the article is a cardiac-assist device.
18. A drive cable for driving an impeller of a catheter blood pump, wherein the drive cable comprises a plurality of discrete segments that are coupled end-to-end, and wherein a position of each of the discrete segments along the drive cable is related to the anatomy in which the drive cable is to be used, and further wherein the discrete segments, as coupled, are suitable for driving the impeller at a rate of at least 1000 rpm.
19. The drive cable of claim 18 wherein some of the discrete segments have a first structural configuration, and wherein some other of the discrete segments have a second structural configuration, and further wherein the first structural configuration and the second structural configuration are different from one another.
20. The drive cable of claim 19 wherein the first structural configuration comprises a rod.
21. The drive cable of claim 19 wherein the second structural configuration comprises a coil.
22. The drive cable of claim 20 wherein the anatomy includes relatively straight portions, and wherein the drive cable is configured so that when the drive cable is disposed in the anatomy, a discrete segment having the first structural configuration is disposed in each of the relatively straight portions.
23. The drive cable of claim 21 wherein the anatomy includes curved portions having relatively small-radii bends, and wherein the drive cable is configured that when the drive cable is disposed in the anatomy, a discrete segment having the second structural configuration is disposed in each of the curved portions.
24. (canceled)
25. The drive cable of claim 18 wherein the drive cable has five discrete segments, and wherein three of the discrete segments are rods and two of the discrete segments are coils.
26. The drive cable of claim 18 wherein the plurality of discrete segments comprise an encapsulating material.
27. An article comprising a rotary drive cable, wherein the drive cable comprises a plurality of segments in a linear arrangement, wherein: (a) at least some of the segments differ from some other of the segments as to their relative capacity for transmitting torque along a curved path; (b) a position of the segments in the linear arrangement thereof is selected to correspond to a geometry of a system in which the drive cable is used, wherein segments that possess a relatively greater ability to transmit torque along a curved path are positioned to coincide with relatively more curved regions of the system; and
28. The article of claim 27 wherein the segments that possess a relatively greater ability to transmit torque along a curved path comprise a coil.
29. The article of claim 27 wherein the segments comprise either: (1) a rod or (2) a coil, and further wherein segments comprising a rod and the segments comprising a coil are disposed in alternating order in the linear arrangement thereof.
30. The article of claim 27 wherein the system is a human vascular system and a route to a patient's heart from the patient's femoral artery defines the geometry.
31. The article of claim 27 wherein the drive cable is dimensioned and arranged so that when the drive cable is disposed in the system, a segment comprising the rod is disposed in a descending aorta of the patient.
32. The article of claim 30 wherein the drive cable is dimensioned and arranged so that when the drive cable is disposed in the system, a segment comprising the coil is disposed in an aortic arch of the patient.
33. The article of claim 27 further comprising a sheath, wherein the drive cable is disposed in a lumen of the sheath.
34. The article of claim 33 wherein the article is a cardiac assist device, and wherein the cardiac assist device further comprises a motor and a pump assembly, and wherein the pump assembly comprises the rotatable element, and further wherein a first end of the drive cable is coupled to the motor and a second end of the drive cable is coupled to the pump assembly.
35. 35-40. (canceled)
41. A percutaneous blood pump comprising: a motor; a rotary drive cable, wherein a first end of the drive cable is operatively coupled to the motor, and wherein the drive cable comprises a plurality of discrete, linearly-arranged segments, and further wherein at least two of the segments are coils and at least two other of the segments are rods; and an impeller, wherein a second end of the drive cable is operatively coupled to the impeller.
42. A percutaneous blood pump comprising: a motor; a rotary drive cable, wherein a first end of the drive cable is operatively coupled to the motor, and wherein the drive cable comprises a plurality of discrete, linearly-arranged segments, and wherein at least some of the segments differ from some other of the segments as to their relative capacity for transmitting torque along a curved path, and wherein a position of the segments in the linear arrangement thereof is selected to correspond to a geometry of a system in which the drive cable is used, wherein segments that possess a relatively greater ability to transmit torque along a curved path are positioned to coincide with relatively more curved regions of the system; and an impeller, wherein a second end of the drive cable is operatively coupled to the drive the impeller in rotary motion.
The following cases are incorporated by reference herein:
(1) U.S. patent application Ser. No. 11/565,969, filed Dec. 1, 2006; and
(2) U.S. patent application Ser. No. 11/565,970, filed Dec. 1, 2006.
If there are any contradictions or inconsistencies in language between this application and one or more of the cases that have been incorporated by reference that might affect the interpretation of the claims in this case, the claims in this case should be interpreted to be consistent with the language in this case.
The present invention relates to drive cables, including those suitable for use in conjunction with a blood pump or other medical device.
Acute heart failure is the sudden inability of the heart to fill with or pump a sufficient volume of blood. The afflicted patient may become weak and short of breath and, in some instances, die. In the most severe acute heart-failure episodes, a patient experiences cardiogenic shock, a condition that is associated with high reported mortality rates.
Acute heart failure occurs in a variety of contexts. For example, some patients who are hospitalized for Acute Coronary Syndrome (i.e., heart attack and unstable angina) develop acute heart failure. Furthermore, some open-heart surgery patients develop acute heart failure. Acute heart failure also complicates certain illnesses. Additionally, some patients who undergo a Percutaneous Coronary Intervention or other procedure are at risk for developing acute heart failure or dying.
Acute heart failure does not necessarily progress to chronic heart failure or death; recovery is possible. Many patients who have acute heart failure and those at risk for developing it receive interventions that are intended to temporarily assist the heart during a recovery period. The intervention typically lasts for less than a week, but may last longer.
These interventions may include pharmaceuticals and medical devices, including cardiac-assist devices. When these cardiac-assist devices include a pump that supplements the heart's pumping action, they often are referred to as "blood pumps." An effective cardiac-assist device assumes some of the heart's pumping function, thereby unloading the heart and enabling it to recover. Cardiac-assist devices and blood pumps can be temporary or permanent.
Over the years, various types of temporary blood pumps have been developed. One type of temporary blood pump is the catheter blood pump. This type of blood pump has a cable-driven rotor that is attached to a catheter. The catheter is inserted into a peripheral vessel, such as the femoral artery, and is then typically advanced to the aorta.
The catheter encloses a rotating drive cable that couples to impeller blades at one end. The other end of the drive cable couples to an extracorporeal motor. As the motor turns, the drive cable rotates, thereby conveying motor torque through the length of the catheter to the impeller blades. This causes the impeller to rotate at high speed, usually in the range of about 1000 to about 100,000 rpm. The impeller's rotation induces a flow of blood through the pump.
One of the more problematic components of the catheter blood pump is the drive cable/catheter assembly. Among other issues for concern, it is very difficult to provide a drive cable/catheter assembly that:
is capable of rotating at the required speeds; and
has the flexibility to negotiate small-radii bends, such as the aortic arch, as occur in the vascular system; and
is able to maintain structural integrity for a clinically relevant duration (e.g., hours to weeks, etc.) at operating speed.
Flexible drive cables currently exist; a common example is an automobile speedometer cable. But these cables operate at gentle curvature and low speed; they are not suitable for use at higher speeds in geometries having small-radii bends.
Rods (solid or hollow) are suitable for transmitting torque at high rpm, but only if the rod is relatively straight. A rod is too stiff to spin in an arc; it will soon fracture and fail. Failure occurs even if the rod is constructed of a super-elastic material, such as Nitinol.
Coils are better suited than solid rods for high-speed operation over small-radii bends. In fact, coils are currently available for transmitting torque "around corners" for long-length applications. But manufacturers normally limit these coils to maximum operating speeds of about 20,000 rpm. As previously mentioned, catheter blood pumps often operate at rotational speeds well in excess of 20,000 rpm. In fact, in some instances, rotational speeds of up to 100,000 rpm might be required.
To avoid the problematic nature of drive cables in catheter blood pumps, some blood pumps have been developed that have a miniature motor that is positioned adjacent to the impeller blades of the pump. In such devices, the motor is implanted in the vascular system or heart along with the pump, and therefore drives the blades directly. See, e.g., U.S. Pat. No. 6,794,789.
But an implantable motor is expensive and complicated, given the extreme miniaturization and wiring/sealing challenges associated with a motor/pump combination that is significantly smaller than the diameter of an average "BB" used in BB guns (i.e., 0.177 inches in diameter). Since these blood pumps are single-use, disposable devices, the high cost of such a miniaturized, implantable motor is particularly disadvantageous.
There is a need, therefore, for a drive cable/catheter assembly that (1) can rotate at speeds well in excess of 20,000 rpm (2) while conforming to an anatomy that includes small-radii bends (3) and can maintain structural integrity for a clinically relevant duration.
The present invention provides a way to transmit torque at high rpm through portions of mammalian anatomy, which may include twists, turns, or even loops, and to do so for a clinically relevant duration, while avoiding some of the shortcomings of the prior art.
The inventor recognized that a major impediment to the use of a continuous coil for torque transmission at high rotational speeds is the potential for significant vibrations in the coil. In particular, and among other concerns, if the forcing frequency (i.e., the rate at which the motor or other "prime mover" rotates the coil) is near the natural frequency of the coil (or a harmonic of the natural frequency), large-amplitude vibrations and standing waves will occur. Since the coil would typically be in a catheter or sheath in many medical applications, these vibrations would result in intermittent and spatially irregular contact between the coil and the sheath. Such contact would contribute to system noise, heat generation, and wear that could shorten cable life.
Drive cables in accordance with the present invention are physically adapted to "tune" large-amplitude vibrations, etc., out of the operating drive cable. In other words, the dynamic response of the drive cable is tailored to be damped within the operational regime of interest. This is accomplished by keeping natural frequency of the cable relatively remote from the forcing frequency. Since there is relatively less latitude to vary the forcing frequency due to the requirements of the pump or whatever device is being driven by the transmitted torque, the natural frequency of the cable is advantageously altered, as required, in accordance with the present invention.
Four main parameters contribute to the vibrational characteristics of the drive cable: (1) tension, (2) bending stiffness, (3) linear mass density including localized or point masses, and (4) length. The inventor recognized that by appropriately altering the dynamic characteristics of the drive cable, such as by changing any one or more of the listed parameters, a flexible drive cable could be used to transmit torque at high rpm. As previously indicated, relatively longer-length coils are unsuitable for transmitting torque at rotational speeds in excess of 20,000 rpm. But testing performed by the inventor has revealed that coils are suitable for transmitting torque at speeds well in excess of 20,000 rpm as long as the coil is kept relatively short.
In accordance with the illustrative and some other embodiments of the invention, favorable (i.e., suitable for the operating regime of interest) dynamic characteristics are achieved for a drive cable by using an in-line combination of one or more coils, where needed, and one or more rods, where acceptable. This ensures that drive cables disclosed herein will not incorporate a continuous, un-modified coil in a length that is any longer than is required to accommodate the required harmonic damping and bends in the anatomy.
In the illustrative embodiment, the one or more rod segment(s) and the one or more coil segment(s) are joined end-to-end via any of a variety of techniques for joining such dissimilar elements. The specific location of coils and rods along the drive shaft is dependent upon the required harmonic damping and the anatomy in which the drive cable is used.
Consider, for example, a drive cable in accordance with the illustrative embodiment that is used in conjunction with a blood pump that is to be inserted via the femoral artery. In operation, the blood pump will be positioned in the vascular system along a path defined by the femoral artery, iliac artery, descending aorta, aortic arch, and ascending aorta. (See definitions of the "iliac artery" and "descending aorta" in paragraph 0040.)
In some embodiments, the inventive drive cable will include three rod segments and two coil segments, as follows:
A first rod segment will transition from an extracorporeal motor to the insertion point at the femoral artery.
A first coil segment will span the femoral artery and iliac artery, accommodating any curvature.
A second rod segment will span the descending aorta.
A second coil segment will span the aortic arch, accommodating its small-radii bend.
A third rod segment, which couples to the pump shaft, will span the ascending aorta.
In this fashion, for some embodiments, the required harmonic damping and anatomy will determine the appropriate positions of certain cable segments. And again, rods are used where acceptable, and coils are used where required, so that coil segments are no longer than required.
In some other embodiments that are consistent with the illustrative embodiment and that are suitable for use with a blood pump, a drive cable will include one rod segment and two coils segments. The first coil segment will span the extracorporeal motor to the descending aorta. The rod segment will span a portion of or the entire descending aorta. The second coil segment will span the aortic arch and ascending aorta. In this embodiment, therefore, a single rod in the descending aorta provides the required harmonic damping sufficient for the cable/catheter assembly to operate for a clinically relevant duration.
The length of various anatomical features (e.g., femoral artery, descending aorta, etc.) will vary, of course, from person to person as a function of body size and normal anatomical variation. As a consequence, several versions of a drive shaft for use with the blood pump discussed in the example are suitably provided. One is sized for a child, a second is sized for an adolescent, a third is sized for an adult of relatively small stature, and a fourth is sized for an adult of relatively large stature, etc. In some embodiments, all four of such drive cables include the same number and allotment of segments, but the lengths of such segments differ. As a consequence, for these embodiments, the actual position (i.e., distance along the drive shaft) of the various rod segment(s) and coil segment(s) will be different for these different versions of the drive cable.
In some alternative embodiments of a drive cable in accordance with the present teachings, a plurality of relatively short coil segments are attached to one another via collars (e.g., implemented as sections of hypotube, etc.). This configuration is similar to the configuration of the drive cable in the illustrative embodiment in the sense that the collars of the present configuration provide the functionality of the rods. In other words, in these alternative embodiments, the collars provide a dual function—they link adjacent coil sections to one another as well as alter the dynamics of the drive cable in the manner of the stiff rod sections of the previous embodiment.
In some further alternative embodiments, a drive cable incorporates a means for adjusting the relative stiffness or flexibility and/or mass of regions of a continuous drive cable (as opposed to a "composite" rod/coil drive cable or the "segmented-coil" drive cable previously disclosed). This is implemented in some embodiments by, for example, disposing one or more discrete "collars" at various locations along the length of coil. This effectively breaks-up the coil into shorter sections, thereby changing the dynamics of the drive cable. Thus, the dynamic response of a continuous coil can be altered by using:
a single collar; or
multiple collars having the same characteristics; or
multiple collars having varying lengths; or
multiple collars having varying thicknesses; or
multiple collars having varying masses; or
multiple collars having varying stiffness; or
any combination of the foregoing.
Collars for any of the embodiments described above can be situated externally or internally relative to the coils section(s). In other words, the collars can either be:
(i) hollow and have an inside diameter that is suitable for receiving, internally, coils segments or rods segments (e.g., to join them, etc.); or
(ii) have an outside diameter suitable that enables the collar to be received internally by coils segments or (hollow) rods segments (e.g., to join them, etc.). In other words, the internal collars are used to create a "pin-and-socket" attachment.
Situating the collars within the coil/rod segments reduces the overall diameter of drive cables disclosed herein. For embodiments in which collars are used to alter the relative stiffness or flexibility and/or mass of regions of a continuous (coil) drive cable, the collars will typically, but not necessarily, be situated on the outside of the drive cable.
In yet some further embodiments of a drive cable in accordance with the present teachings, select regions of the coil can be bound together (e.g., soldered, welded, banded, etc.), thereby increasing stiffness and affecting the dynamic characteristics.
In yet some additional embodiments, a machined spring or coil can be formed that has, along its length, variations in material thickness or other properties (material or otherwise) to appropriately tailor dynamic characteristics.
The drive cables described herein are not limited for use in catheter blood pumps. Rather, they are suitable for use in any medical device that requires a torque-transmission cable within a curved portion of the anatomy, such as, for example, within other parts of the vasculature, the gastrointestinal tract, or the spinal canal/ventricular system of the brain. The cables that are disclosed herein are particularly advantageous for use in applications that require a relatively longer cable that is turning at relatively higher rpm in an anatomy that includes relatively smaller-radii bends, since very few if any other drive cables can satisfy such requirements.
FIG. 1 depicts a cardiac-assist device that incorporates a drive cable in accordance with an embodiment of the present invention, wherein the cardiac-assist device is disposed in the human vascular system and heart.
FIG. 2A depicts the illustrative embodiment of the drive cable that is depicted in FIG. 1.
FIG. 2B depicts a drive cable similar to the drive cable of FIG. 2A but having fewer segments.
FIG. 3A depicts a first alternative embodiment of the drive cable that is used in the device of FIG. 1.
FIG. 3B depicts the drive cable of FIG. 3A except that collars for connecting adjacent coil segments are disposed within those segments (i.e., pin-and-socket connection).
FIG. 4 depicts a second alternative embodiment of the drive cable that is used in the device of FIG. 1.
FIG. 5 depicts a third alternative embodiment of the drive cable that is used in the device of FIG. 1
FIG. 6 depicts a drive cable similar to the drive cables of FIGS. 2A and 2B being used in conjunction with a hypothetical medical device deployed within the rectum and colon.
FIG. 7 depicts, via a cross section, a drive cable that is encapsulated in a polymer.
The following terms and their inflected forms are defined for use in this Specification, including the appended claims:
i. Axial means an axis or direction that is coincident with a centerline (of a device) and contrary to "radial."
ii. Bio-compatible means the property of being biologically compatible as determined by accepted medical industry standard.
iii. Coil is a generally helical element that exhibits good flexibility in bending, is resilient and fatigue resistant. The term "coil" is meant to include uni-filar and multi-filar coils, and also includes multi-layer (i.e., a coil-within-a-coil) arrangements, such as the various coil-within-coil arrangements disclosed in U.S. Pat. No. 6,685,696. Thus, as used herein, a coil-within-coil arrangement is considered to be a single coil.
iv. Descending aorta means the anatomy defined by the descending thoracic aorta and abdominal aorta,
v. Discrete means "separate" or "distinct."
vi. Distal means relatively farther from a first end of a drive cable. The drive cable typically connects a source of torque, (e.g., a motor, etc.) to a user of torque, which is usually a rotatable component, such as a pump assembly or the like. Typically, the source of torque is located at the first (proximal) end of the drive cable and the user of torque is located at the distal end of the drive cable.
vii. Dynamic Response means the resultant motion (or other output, including sound or heat) of a mechanical element, structure, or system from a mechanical excitation (e.g., rotation, etc.) under specified conditions. For example, vibration, such as the vibration of a cable, is considered to be a dynamic response.
viii. Forcing Frequency is the frequency at which a system is excited. In rotational systems, the forcing frequency is the rotational speed (e.g., rpm, Hz, radians/second, etc.)
ix. Harmonic Frequencies are overtones, or integer multiples of the natural frequency.
x. Harmonic Resonance is an undesirable condition wherein the forcing frequency and the natural frequency (or harmonic frequencies) are equal or close in magnitude. The amplitude of oscillation and energy exchanged (between potential and kinetic) are an appreciable fraction of the maximum. This condition results in undesirable noise, wear and heat generation.
xi. Iliac artery means the anatomy defined by the external iliac artery and the common iliac artery.
xii. Natural Frequency means a frequency at which a system oscillates or vibrates if it is disturbed.
xiii. Operatively coupled means that the operation of one device affects another device. For example, if a drive cable is "operatively coupled" to an impeller of a pump, it is capable of driving the impeller (i.e., causing the impeller to rotate). Operatively coupled devices need not be directly physically coupled.
xiv. Physically coupled means direct, physical contact between two objects (e.g., two surfaces that abut one another, etc.).
xv. Proximal means relatively closer to the first end of the drive cable.
xvi. Proximate means "near to."
Other definitions may be provided later in this disclosure.
FIG. 1 depicts heart 112 and a portion of human vascular system 100; in particular, femoral artery 102, iliac artery 104, descending aorta 106, aortic arch 108, and ascending aorta 110. FIG. 1 also depicts cardiac-assist device 120 that is deployed in vascular system 100 and heart 112.
The cardiac-assist device 120 comprises controller 122, motor 124, drive cable 126, and pump assembly 128. In use, some elements of cardiac-assist device 120 are extracorporeal (i.e., remain outside of the patient) and others are located within the patient's body. More specifically, controller 122, motor 124, and some of drive cable 126 remain outside of the body while, when deployed, much of the drive cable and all of pump assembly 128 are located within the body.
To maintain a focus on issues that are germane to an understanding of the present invention, only brief mention will be made of elements of cardiac-assist device 120 other than drive cable 126. Further disclosure concerning such other elements of a cardiac-assist device can be found, for example, in co-pending U.S. patent application Ser. Nos. 11/565,969 and 11/565,970.
Controller 122 is the human interface of cardiac-assist device 120. The controller, which incorporates a microprocessor, typically provides control and monitoring functions. Motor 124 is the prime mover that drives pump assembly 128.
Pump assembly 128 includes a rotating impeller (not depicted) that is capable of supplementing native cardiac output by inducing flow through the pump. Drive cable 126 operatively couples motor 124 to pump assembly 128, thereby transmitting motor torque to the pump assembly to drive the impeller. Drive cable 126 will typically rotate at a speed well in excess of 1000 rpm and possibly as high as 100,000 rpm.
In some embodiments, known catheterization techniques (e.g., Seldinger, etc.) are used to percutaneously introduce pump assembly 128 into femoral artery 102 and advance it through iliac artery 104, descending aorta 106, around aortic arch 108, and then to its intended placement site. A variety of placement sites are possible; typical sites include ascending aorta 110 and within heart 112 (e.g., across the aortic valve, within the left ventricle, etc.). Other sites may be possible as well (e.g., in descending thoracic aorta, in suitably-sized peripheral blood vessels, or in the right side of the heart or in right-side-related vasculature).
FIGS. 2A through 5 depict several embodiments of drive cable 126, identified as drive cables 126A, 126B, 126C, and 126D. In all of these embodiments, the drive cables include physical adaptations that are intended to tune out large-amplitude vibrations and provide harmonic damping in the desired operating regime. Broadly defined, the desired operating regime is between about 1000 rpm and about 100,000 rpm. The desired operating regime will more typically fall between about 20,000 rpm to 100,000 rpm, and most likely be within the range of about 30,000 rpm to about 80,000 rpm.
Turning now to FIG. 2A, drive cable 126A comprises a plurality of discrete segments, and is therefore referred to as a "composite" drive cable. By way of illustration, but not limitation, drive cable 126A depicted in FIG. 2A includes five discrete segments 230A, 230B, 230C, 234A, and 234B. The segments are coupled end-to-end, thereby forming a linear arrangement. Some other embodiments of drive cable 126A in accordance with the illustrative embodiment of the present invention will have fewer than five discrete segments (see, e.g., FIG. 2B) and still further embodiments will have more than five discrete segments (see, e.g., FIG. 6). As discussed further below, the specific number of discrete segments that are included in drive cable 126A, and the position of such segments along the cable, is related to the required harmonic damping and the anatomy in which drive cable 126A is being used.
The five discrete segments of composite drive cable 126A of FIG. 2A can be classified as being associated with one or the other of at least two segment types or groups. Segments 230A, 230B, 230C (generically or collectively referenced "segment[s] 230") belong to a first group. Segments 234A and 234B (generically or collectively referenced "segment[s] 234") belong to a second group. The segments in the first group differ from those in the second group in terms of structural configuration.
The phrase "structural configuration" is used herein to refer to the structural arrangement of the segment. Examples of a "structural configuration" include, without limitation, a rod, a coil, a bellows, and the like. The phrase "structural configuration," as used in this description and in the appended claims, is not intended to refer to segment attributes or characteristics such as the thickness, mass, diameter or length of a segment.
Each of segments 230 in the first group of segments has a structural configuration that is stiff, both in torsion and in bending, and is therefore stiff in torsional and planar vibration. In the illustrative embodiment, segments 230 are configured as a "rod." It should be understood that stiff segments 230 are flexible enough to pass atraumatically through the sometimes tortuous anatomy of a natural body lumen, cavity, vessel, orifice and the like.
In some embodiments, stiff segments 230 are solid. In some additional embodiments, stiff segments 230 are hollow. In some further embodiments, drive cable 126A will include some solid, stiff segments as well as some hollow, stiff segments. Whether solid or hollow, a rod is well suited for transmitting torque at high rpm (in excess of 20,000 rpm). More particularly, by virtue of its structure, a segment configured as a rod can withstand high levels of torque without fracturing or otherwise losing structural integrity.
There is, however, a caveat to the use of stiff segments as torque transmitters. And that is that while rotating during normal operation these stiff segments must remain substantially straight. If a stiff segment were to rotate while bent, such as might be required to accommodate the anatomy, its ability to transmit torque at high rpm and maintain structural integrity would be substantially compromised. In fact, if a drive cable that included stiff segment(s) 230 were situated in a system that required the stiff segment to be radically bent while rotating, such as to negotiate a 45-degree bend, it is likely that the segment would experience structural failure soon after coming up to rotational speed (or even before reaching its rated rpm).
Each of the segments 234 in the second group has a structural configuration that renders it flexible enough to rotate while conforming to a curved path. In the illustrative embodiment, segments 234 are configured as coils, which are preferably, but not necessarily, hollow (i.e., have lumens). Compared to a rod configuration, a straight section of coil has a substantially decreased ability to withstand the stresses that result from transmitting torque at high rpm. But a bent section of coil has a substantially greater ability than a rod to withstand the stresses that result from transmitting torque at high rpm around a corner or bend. Thus, flexible segments 234 have a greater capacity for transmitting torque at high rpm along a curved path than rod segments 230. It is notable that even if a rod were formed from a super-elastic substance, such as Nitinol, it would not be able to operate long term in a system having small-radii bends.
In various embodiments, coil segments 234 can be a single coil or multi-layer (i.e., a coil-within-a-coil), such as the various coil-within-coil arrangements disclosed in U.S. Pat. No. 6,685,696. Additionally, in some embodiments, the coils are uni-filar and in some other embodiments, they are multi-filar.
Composite drive cable 126A therefore comprises a linear arrangement or in-line alternating combination of discrete stiff (e.g., rod, etc.) segments 230 and discrete flexible (e.g., coil, etc.) segments 234. The discrete segments that form drive cable 126A must, of course, be joined to one another. The segments can be joined by any of variety of known techniques for joining dissimilar elements. For example, segments can be joined by using adhesives, pin-and-socket construction, swaging, brazing, welding, soldering, or combinations thereof.
In the illustrative embodiment that is depicted in FIG. 2A, segments 230 and 234 are joined by fitting a tube or "collar" 232 over opposed ends of adjacent segments and then swaging the tube to those segments. Adhesive is typically (but not necessarily) used in conjunction with swaging to enhance joint strength and durability.
Segments 230 and 234 can be formed from a wide variety of materials. For example, and without limitation:
stiff segments 230 are suitably formed from materials such as nickel titanium super-elastic shape memory alloy (Nitinol), stainless steel, MP-35 alloy (chromium/nickel/molybdenum/cobalt), various other metals and metal alloys;
flexible segments 234 are suitably formed from materials such as stainless steel, MP-35, or other metals and metal alloys; and
tubes/collars 232 are suitably formed from stainless steel hypotube, plastics, and the like.
In some embodiments, one or more stiff segments 230 are tapered or stepped. This will vary stiffness, etc. Furthermore, to the extent that stiff segments 230 and flexible segments 234 may have different diameters, the stiff segments can be stepped to match the diameter of the coil segments. Steps are advantageously radiused to minimize stress concentration at a step.
As previously indicated, in accordance with the present teachings, drive cable 126A is advantageously configured for use in conjunction with a specific system. The particular number, location, and length of specific stiff segments 230 and flexible segments 234 will, therefore, be functions of the required harmonic damping and the anatomy.
Referring again to FIG. 1, consider the anatomy of the path leading from femoral artery 102 to heart 112 in the human vascular system. Starting at the upper thigh, femoral artery 102 curves as it becomes iliac artery 104 and then connects to descending aorta 106. Proceeding toward heart 112, descending aorta 106 is relatively straight. There is a sharp bend at aortic arch 108; this vascular feature is roughly a 180-degree arc on a 1.5 inch radius. Aortic arch 108 leads to ascending aorta 110.
So, in some embodiments in which composite drive cable 126A is to be used in conjunction with cardiac-assist device 120, the drive cable includes:
at least two flexible sections (i.e., one to accommodate bending between femoral artery 102 and descending aorta 106 and the second to negotiate aortic arch 108); and
at least three stiff sections (i.e., one to extend from motor 124 to a certain point in femoral artery 102, a second for placement in descending aorta 106, and a third for placement in ascending aorta 110).
The stiff sections will be implemented as rods and the flexible sections will be implemented as coils. The general approach is to provide flexible segments where required and stiff segments where permissible, as a function of the required harmonic damping as well as the anatomy in which composite drive cable 126A is being used.
Of course, the specific position along composite drive cable 126A at which any particular segment begins and ends is a function of the required harmonic damping and anatomy. In the case of the femoral path to the heart depicted in FIG. 1, in some embodiments, the various segments have a size that typically (but not necessarily) falls in the following ranges:
First flexible segment (i.e., 234A in FIG. 2) has a length A that is typically within a range of about 10 centimeters to about 90 centimeters.
Second flexible segment 234B has a length C that is typically within a range of about 5 centimeters to 25 centimeters.
First stiff segment (i.e., 230A), which is at least partially extra-corporeal, will typically be about 5 centimeters to about 25 centimeters.
Second stiff segment (i.e., 230B) has a length B that is typically within a range of about 10 centimeters to about 90 centimeters.
Third stiff segment (i.e., 230C) has a length D that is typically in a range of about 5 centimeters to about 15 centimeters.
It will be appreciated that the distances and the lengths of the various segments, as provided above, depend upon the required harmonic damping and the anatomy of the patient. The anatomy will, of course, be dictated by the patient's size, age, and gender, as well as other factors. It will be understood, therefore, that the length of any given segment 230 or 234, as provided above, may be significantly outside the stated ranges, as a function of required harmonic damping and anatomical variation. An illustrative embodiment of cable 126A, for use in conjunction with cardiac-assist device 120 via femoral insertion, is provided in Table 1A below:
Embodiment of Drive Cable 126A that is Suitable for
use in conjunction with a Cardiac-Assist Device
POSITION LOCATION CM LOCATION
IN ALONG CABLE IN VASCULAR
CABLE TYPE START END SYSTEM
1 Stiff (ROD) 0 15 Extracorporeal to
2 Flexible (COIL) 15 65 Femoral Artery to
Descending Aorta
3 Stiff (ROD) 65 110 Descending Aorta
4 Flexible (COIL) 110 125 Aortic arch
5 Stiff (ROD) 125 135 Ascending aorta
FIG. 2B depicts a variation of drive cable 126A, wherein the drive cable includes less than five discrete segments. More particularly, in the embodiment of drive cable 126A that is depicted in FIG. 2B, the drive cable comprises three segments: one rod segment 230D that is flanked by two coils segments 234C and 234D. Like the illustrative embodiment that is depicted in FIG. 2A, the various segments of the drive cable that are depicted in FIG. 2B are joined via collars 232. This embodiment of drive cable 126A is also intended for use in conjunction with cardiac-assist device 120 via femoral insertion, among any other uses.
Variation of Drive Cable 126A, as depicted in FIG. 2B
1 Flexible (COIL) 0 65 Extracorporeal to
2 Stiff (ROD) 65 75 Descending Aorta
3 Flexible (COIL) 75 135 Descending Aorta to
Ascending Aorta
Table 1B, above, provides additional detail of the variation of drive cable 126A that is depicted in FIG. 2B. The distances and the lengths of the various segments in drive cable 126A, as provided in Table 1B, are provided by way of illustration, not limitation. It is to be understood that a three-segment drive cable can be implemented with segments having different lengths than those indicated in Table 1B. In particular and as previously disclosed, the specific lengths of the various segments of drive cable 126A depend upon the required harmonic damping and the anatomy of the patient.
FIG. 3A depicts drive cable 126B. Drive cable 126B comprises a plurality of short, flexible segments, which are implemented in the embodiment that is depicted in FIG. 3 as coils 334i, i=1, n (segments 334A, 334B, 334C, and 334n are shown). Coils 3341 can be uni-filar or multi-filar. The flexible segments are joined to one another by collars 332, which can be implemented in the same fashion and use the same methods for joining as described for previous embodiments.
Drive cable 126B is typically coupled, at its two ends, to rigid shafts, etc. These shafts (e.g., shaft 330 and shaft 336) are typically associated with (1) a prime mover and (2) the device that uses the torque that is provided by the prime mover. For example, in the case of a cardiac-assist device, in some embodiments, shaft 330 extends from the motor and shaft 336 extends from the pump. In such embodiment, shafts 330 and 336 are not considered to be a part of drive cable 126B.
In some embodiments, rod 330 is not part of the prime mover; rather, rod 330 is simply the first segment of drive cable 126B. In a medical application, for example, rod 330 would typically (but not necessarily) be extracorporeal. In particular, in the case of a drive cable for a cardiac-assist device, it can be advantageous for extracorporeal portions of the drive cable to be a rod as long as there is no requirement for it to bend sharply. As previously discussed, a rod can handle much higher rotational speeds and torque along a straight line, and is therefore better suited for such service. In some further embodiments, rod 336 is part of drive cable 126B.
Unlike drive cable 126A, drive cable 126B does not include one or more discrete, relatively long rod segments interspersed among coil segments. As a consequence, the layout of drive cable 126B is not dependent upon the geometry of the anatomy to the same extent as drive cable 126A. That is, compared to drive cable 126A, the nominal arrangement or layout of drive cable 126B accommodates more anatomical variations.
In some embodiments, the length of each coil 3341 within drive cable 126B is the same. In some other embodiments, the lengths of the various coils within drive cable 126B are not equal. In all of these embodiments, the length of coil segments 3341 will depend, to some extent, upon the forcing frequency (e.g., the speed at which a motor or other prime mover is intended to turn the drive cable). Acceptable length(s) for coil segments 3341 can be determined either empirically or analytically.
Regarding an analytical approach, the equations that approximate the dynamic response of any particular embodiment of drive cable 126 (i.e., drive cable 126A, 126B, etc.) can be developed by those skilled in the art. Having an understanding (i.e., a mathematical characterization) of the dynamic response of a given drive cable, knowing the details of the forcing frequency, and in conjunction with this disclosure, those skilled in the art will be able to provide a design for drive cable 126B (e.g., determine coil length, determine coil stiffness, etc.) that tunes out large amplitude vibrations, in accordance with the invention.
FIG. 3B depicts an embodiment of a drive cable wherein collars 333 that connect adjacent coil segments (e.g., coil segments 334A and 334B) or adjacent coil and (hollow) rod segments (e.g., rod segment 330 and coil segment 334A) are disposed inside the coils (or coil and rod). It is notable that for this embodiment, the gap that appears between coil segments 334A and 334B would not be present; this is simply for illustrative purposes to demarcate the ends of these adjacent coil segments.
The use of internally-disposed collars 333 in FIG. 3B illustrates a "pin-and-socket" connection. For such embodiments, the outside diameter of collars 333 is typically sized to provide a tight fit within the coils (or rods). Additionally, adhesive, etc., can be used to bind the collars to the segments that are being joined. In comparison to externally-disposed collars, the use of internally-disposed collars will typically reduce the (maximum) outside diameter of a drive cable in accordance with the present teachings.
FIG. 4 depicts another embodiment of a drive cable in accordance with the present teachings: drive cable 126C. This drive cable includes an unbroken, long coil 434 rather than a plurality of coil segments (although coil 434 can be uni-filar or multifilar). As with drive cable 126B, the ends of drive cable 126C will typically couple to rods 430 and 436 that might or might not be considered to be a part of the drive cable (e.g., in some embodiments, these rods will be a part of the prime mover and/or torque user and not a part of drive cable 126C, proper. Alternatively, the proximal end, distal end, or any intermediate region(s) of coil 434 can be fused together to provide the dynamic characteristics of a rod.
Drive cable 126C includes a plurality of collars 4321, depicted in FIG. 4 as collars 432A, 432B, 432C, 432D, and 432E.
Collar 432A is used to couple rods 430 and 436 to the coil 434. The four other collars (collars 432B, 432C, 432D, and 432E) which each have a different length, thickness, shape, mass, and stiffness, are used to alter the dynamic response of coil 434.
The collars effectively segregate coil 434 of drive cable 126C into a plurality of coil segments, akin to drive cable 126B. Collars 4321 can be "slid" over coil 434 or formed in place around coil 434 in known fashion (e.g., fusing two collar "halves" together, etc.).
In further detail, collars 432C and 432B have the same thickness as one another but are of different lengths. When positioned on drive cable 126C in the same location, collar 432C would have the effect of stiffening the drive cable more than collar 432B. It would also add more mass to the cable and would stiffen a greater length of the drive cable.
Collar 432D is thicker than either of collars 432B or 432C, and would stiffen drive cable 126C even further. Furthermore, collar 432D will provide an ability to concentrate more mass (than either of collars 432B or 432C) at a given location.
Collar 432E has a tapered geometry that can further enhance stiffening and mass concentration, even relative to collar 432D.
The specific placement of any of these collars is an additional parameter that is used to tailor the dynamic response of drive cable 126C, as a function of its intended operating regime.
The embodiment of drive cable 126C that is depicted in FIG. 4 includes four "dynamics-affecting" collars of different types. It is to be understood, however, that embodiments of drive cable 126C are not limited to four such collars.
For example, some embodiments of drive cable 126C include less than four collars. In fact, some embodiments will include only a single collar. And that single collar can be configured as any of the collars 432B through 432E that are depicted in FIG. 4. Furthermore, a single collar having other specific configurations that are not depicted herein but will be known or otherwise occur to those skilled in the art after reading the present disclosure may suitably be used.
In some other embodiments, drive cable 126C includes more than four "dynamics-affecting" collars. In some such embodiments, all collars within a given embodiment of drive cable 126C will be the same type (e.g., all 432B, etc.) In yet some further embodiments, drive cable 126C will include plural collars of at least two different types (e.g., some are 432B and some others are 432D, and so forth). It is to be understood that the number of dynamics-affecting collars and their specific "type" are freely permutable to tune the dynamic response of drive cable 126C as dictated by application specifics (i.e., system geometry, forcing frequency, etc.).
FIG. 5 depicts drive cable 126D, which is another embodiment of a drive cable in accordance with the present teachings. This drive cable includes a single, long machined coil 534 (although coil 534 can be uni-filar or multifilar). Like drive cables 126B and 126C, the ends of drive cable 126D will typically couple to rods (not depicted) that might or might not be considered to be a part of the drive cable (e.g., in some embodiments, these rods will be a part of the prime mover and/or torque user and not a part of drive cable 126D, proper.) In yet some additional embodiments, the proximal and distal ends of machined coil 534 are machined to be suitably stiff so as to provide the functionality of a rod.
In accordance with this embodiment, the thickness or other material properties of machined coil 534 are varied along its length to appropriately tailor its dynamic characteristics to a desired operating regime. Unlike a coil that is formed by a winding process, a machined or laser-cut coil can be fabricated with a greater degree of precision to include any of a number of structural variations.
For example, in the embodiment depicted in FIG. 5, coil 534 includes two sections 537 and 539 having a first "material" width and section 538 having a second "material" width. The phrase "material width" is meant to indicate the width of the material that forms the coil, as opposed to the width or diameter of the coil itself. As depicted in FIG. 5, the first material width is relatively narrower than the second material width. In the absence of any other differences between these sections, section 538 will be relatively stiffer than sections 537 and 539. For simplicity, coil 534 in FIG. 5 includes only three sections having two different material widths. It will be appreciated that, as required, coil 534 can be machined to vary in other ways and on a more frequent basis.
FIG. 6 depicts a hypothetical device in rectum and colon ("R&C") 600. The device includes source of torque 624, drive cable 126A, and user of torque 628. Source 624 is operatively coupled to the proximal end of cable 126A and torque user 628 is operatively coupled to the distal end of cable 126A. The drive cable transmits torque from source 624 to user 628.
As depicted in FIG. 6, the anatomy of R&C 600 is defined by various straight and curved sections. In particular, R&C 600 includes relatively straight extracorporeal portion and rectum 640, "s-curved" sigmoid colon 642, relatively straight descending colon 644, curved splenic flexure 646, relatively straight transverse colon 648, curved hepatic flexure 650, and straight ascending colon 652. The lengths of these various anatomical regions can vary greatly, depending upon patient gender, age, and other factors. For this anatomy, drive cable 126A can be organized as listed in Table 2, below. The implied lengths of the particular segments are provided by way of illustration, not limitation, and can vary significantly, of course, as a function of the required harmonic damping and individual anatomy.
Embodiment of a Drive Cable Suitable for use in R&C 600 of FIG. 6
DRIVE POSITION LOCATION (CM
ANATOMY SECTION CABLE SEGMENT IN DRIVE ALONG CABLE)
SECTION DESCRIPTION SEGMENT TYPE CABLE START END
640 STRAIGHT 641 STIFF 1 0 25
642 CURVED 643 FLEXIBLE 2 25 65
644 STRAIGHT 645 STIFF 3 65 90
646 CURVED 647 FLEXIBLE 4 90 110
648 STRAIGHT 649 STIFF 5 110 150
650 CURVED 651 FLEXIBLE 6 150 170
It is assumed that the drive cable in FIG. 6 is required to rotate at high rpm to transmit torque from source 624 to user 628. Therefore, a drive cable suitable for such service, such as embodiments of drive cable 126 disclosed herein, is advantageously used. For this particular example, drive cable 126A is used; embodiments of drive cables 126B, 126C, or 126D can suitably be used as well.
For use in the human body, most embodiments of drive cable 126 (e.g., drive cable 126A, 126B, 126C, 126D etc., will be constrained by a catheter or other sheath. The sheath will be bio-compatible, capable of being pushed (through a vascular system, etc.) and flexible, to negotiate the anatomy. For use in the vasculature, the sheath must be effective in preventing fluid exchange between the bloodstream and the interior of the sheath (i.e., the sheath's lumen), from full vacuum to about 20 atmospheres internal pressure. When used in the vasculature, the size of the sheath is constrained to an outer diameter of less than about 30 Fr (10 millimeters).
Since drive cable 126 will impinge upon the sheath intermittently, if not continuously, there should be low friction at this interface. This can be accomplished by forming the sheath from a suitable polymer, elastomer, fluoropolymer, or thermoplastic material. Examples of such materials include, without limitation, PTFE (polytetrafluoroethylene, commonly known by the trademark Teflon®, available from Dupont), FEP (fluorinated ethylene propylene), ETFE (a polymer of tetrafluoroethylene and ethylene), PFA (perfluoroalkoxy copolymer resin), PP (polypropylene), PE (polyethylene), silicone rubber, PU (polyurethane), PVC (polyvinyl chloride), Pebax® (polyether block amides are plasticizer-free thermoplastic elastomers available from Arkema, Inc.), UHMWPE (ultra-high molecular weight polyethylene), Hytrel® (thermoplastic polyester elastomers available from Dupont), Polyimide, and combinations or layers thereof.
Drive cables, as disclosed herein and used throughout industry, are constructed primarily of metals because metals have favorable fatigue properties and elastic moduli. In some embodiments, the various embodiments of drive cable 126 (e.g., drive cables 126A, 126B, 126C, and 126D, etc.) are encapsulated in material 750, such as depicted in FIG. 7.
Among other benefits, the encapsulating material, which is softer than metal, attenuates the impact of collisions between the drive cable and the sheath. This impact attenuation is expected to reduce the noise and perceptible vibration that is generated by the system. Additionally, the encapsulation is expected to provide a slight increase to the bending stiffness of the encapsulated member, which will alter the dynamic response (e.g., harmonic behavior, etc.) of the drive cable.
Materials that are suitable for encapsulating the drive cable include, without limitation: elastomer, fluoropolymer, or thermoplastic material. Examples of such materials include, without limitation, PTFE (polytetrafluoroethylene, commonly known by the trademark Teflon®, available from Dupont), FEP (fluorinated ethylene propylene), ETFE (a polymer of tetrafluoroethylene and ethylene), PFA (perfluoroalkoxy copolymer resin), PP (polypropylene), PE (polyethylene), silicone rubber, PU (polyurethane), PVC (polyvinyl chloride), Pebax® (polyether block amides are plasticizer-free thermoplastic elastomers available from Arkema, Inc.), UHMWPE (ultra-high molecular weight polyethylene), Hytrel® (thermoplastic polyester elastomers available from Dupont), Polyimide, and combinations or layers thereof.
Encapsulation processes include the use of shrink tubing and/or adhesive bonding as well as other processes known to those skilled in the art.
Thus, a drive cable in accordance with the present teachings can be used to form a drive connection from a prime mover or source of torque to a blood pump, or for other medical applications that might employ a working head, cutter member, or the like.
It is to be understood that the disclosure teaches just one example of the illustrative embodiment and that many variations of the invention can easily be devised by those skilled in the art after reading this disclosure and that the scope of the present invention is to be determined by the following claims.
Previous Patent: Drive Circuit For Magnetic Stimulation
Next Patent: DUCT FOR VENTRICULAR-ASSISTANCE DEVICE


text:
Enforcement of Mediated Settlement Agreements in Vietnam: A Step Forward the International Trend?
On 24 February 2017, the Government of Vietnam promulgated Decree No.22/2017/ND-CP on Commercial Mediation (the "Decree"). It is the first legislation specifically governing commercial mediation in Vietnam. The Decree is inspired by the UNCITRAL Model Law on International Commercial Conciliation (the "UNCITRAL Model Law"), but includes several local modifications. From the drafting process, the Decree has attracted the attention and comments of experts and practitioners not only from Vietnam but also from the international community.
Furthermore, Vietnam also recently introduced an effective regime for the enforcement of mediated settlement agreements, one of the most critical issues of mediation. It is secured by the regulations on recognition of results of out-of-court mediation (mediated settlement agreements) in Chapter 33 of the 2015 Vietnamese Civil Procedure Code (the "CPC").
Beyond the national level, the EU-Vietnam Free Trade Agreement (the "EVFTA"), which is regarded as the most comprehensive and ambitious FTA that the EU has ever concluded with a developing country, also dedicates a considerable role to the mediation of both state-state and investor-state disputes.
Considered altogether, will these legal frameworks create firm ground for the rise of mediation in Vietnam? Disputes allowed to be settled by commercial mediation
Mediation is a brand-new issue for the legislators in Vietnam. In lack of a pre-existing mediation law, the Decree is therefore instead significantly influenced by the 2010 Vietnamese Law on Commercial Arbitration (the "LCA"). In particular, similar to the scope of application of the LCA, the Decree stipulates that mediation shall only be applicable for disputes of a commercial nature, disputes in which at least one party is engaged in commercial activity or disputes specifically designated by other laws to be settled by commercial mediation. Under Vietnamese law, "commercial activities" means activities for the purpose of generating profits, including the sale and purchase of goods, provision of services, investment, and commercial promotion. Presently, only disputes falling within this scope can be settled by commercial mediation. Though the scope of application of the Decree is narrower than foreseen in the UNCITRAL Model Law, it can cover almost all current common commercial disputes. Additionally, it is expected that the sphere of application will be expanded in the near future with the amendment of the Vietnamese Law on Commerce as well as other substantive laws. These will most likely specifically designate further kinds of disputes for resolution through mediation.
Qualifications of mediators, practice of foreign mediators and presence of foreign mediation institutions in Vietnam
The Decree set out quite strict qualifications for mediators. Specifically, apart from general moral standards, mediators must have a university or higher qualification and at least two years of working experience in their educated discipline. Furthermore, mediators are required to have mediation skills as well as legal understanding, knowledge of business and commercial practice. These requirements are similar to those applicable to arbitrators under the LCA. Despite these strict requirements, the Decree lacks an accreditation system for meditators.
The Decree on Commercial Mediation promotes both institutional and ad-hoc mediation. Accordingly, mediators can choose to be listed on the panel of a mediation centre or practise independently as ad-hoc mediator or both.
Though there is no explicit restriction on the nationality of mediators, the Decree imposes a technical barrier requiring ad-hoc mediators to register with the Department of Justice where they reside. As a result, the opportunity for foreign mediators to personally practise in Vietnam may be restricted. Presently, it therefore appears that the selection of an adequate mediator may be a hard task for disputing parties as well as their counsel since the persons meeting the requirements of the law may not be as skilful and experienced as internationally accredited mediators. However, influenced by the LCA and in compliance with the commitment of Vietnam in accession to the WTO, the Decree also encourages foreign mediation institutions to open branch or representative offices in Vietnam. Furthermore, the branch offices of international mediation centres can establish their own panels of mediators provided that the mediators meet the general qualifications specified by the Decree. We expect that these regulations will facilitate international mediation centres to explore the Vietnamese mediation market.
Recognition of mediated settlement agreements
The enforceability of mediated settlement agreements is maybe the most important factor contributing to the success of mediation. Accordingly, in order to safeguard the enforceability of mediated settlements, Vietnamese law provides a mechanism for the recognition of mediated settlement agreements, which converts the agreements into court judgments.
The written mediated settlement agreement, on the one hand, will be valid and have binding effect on the disputing parties in accordance with the provisions of civil law. On the other hand, pursuant to the Decree and Chapter 33 of the CPC one or both parties to the mediated settlement agreement can apply to the courts for the recognition of their agreement. After being recognized, the mediated settlement agreement is enforceable as a full and final court judgment in compliance with the Vietnamese Law on the Enforcement of Civil Judgments. However, this recognition mechanism only applies for settlement agreements resulting from mediations conducted under the provisions of the Decree. Hence, the results of mediations conducted by foreign mediation centres such as the Singapore International Mediation Center (SIMC), the Center for Effective Dispute Resolution (CEDR), etc. are presently not be covered by these regulations.
The Vietnamese regulations mirror Directive 2008/52/EC of the European Parliament and Council of 21 May 2008 on Certain Aspects of Mediation in Civil and Commercial Matters, especially its Article 6 on the enforceability of agreements resulting from mediation.
With these regulations, Vietnam is at the forefront of a new international trend on the enforcement of mediated settlement agreements. In future, this trend may well lead to an instrument, most favourably in form of an international convention, on the enforcement of international commercial settlement agreements resulting from mediation, which could have a similar effect as the 1958 New York Convention on the Recognition and Enforcement of Foreign Arbitral Awards. The draft of such a Convention is currently the main topic of discussion in Working Group II of the UNCITRAL (Agenda of Working Group II of the UNCITRAL http://www.uncitral.org/uncitral/en/commission/working_groups/2Arbitration.html accessed on 15 May 2017).
Investment Mediation
Apart from building the framework for commercial mediation, with the EVFTA Vietnam also entered into one of the very first new generation free trade agreements promoting and detailing the settlement of investment dispute through mediation. Under the EVFTA, at any time during the settlement of an investor-state dispute, any disputing party can invite the other party to conduct mediation in accordance with the procedure stipulated therein.
The specific regulations on mediation included in the EVFTA demonstrate the special attention given by the legislators in Europe and Vietnam to dispute resolution through mediation, which is apparently gradually becoming a favourable new trend in the world. Consequently, we believe that this trend will also positively affect and further help the development of commercial mediation in Vietnam.
It is apparent from the above that both commercial mediation and investment mediation in Vietnam have received due attention from legislators and are now provided with a sound legal framework, which will be the cornerstone for its future development. Despite certain drawbacks, it can be expected that the new legislation will bring mediation in Vietnam closer to the standards of international practice and will help it to become an effective method of dispute resolution for the business community. In addition, we expect that the new legislation on mediation will actually support rather than pose competition to arbitration, as it will enhance the usage of multi-tiered dispute resolution and strengthen the pro-ADR policy of the Vietnamese government. Accordingly, we have the strong belief that mediation will flourish in Vietnam in the near future due to its facilitation by the new legal framework as well as the support from the Vietnamese courts and government.
Credits: Nguyen Manh Dzung (Dzungsrt & Associates LLC ) and Dang Vu Minh Ha(Dzungsrt & Associates LLC)
In essence, mediation (or Reconciliation, Conciliation) is the process of negotiating between parties in order to settle the disputes with the help from a third party (called mediator).
Commercial dispute mediation – Friendly and win-win
In 2018, a range of FTA agreements have been into effect, the competition becomes more cutthroat. Therefore, the risk of disputes among Vietnamese enterprises as well as disputes between Vietnamese enterprises and foreign enterprises have increased.
On 24 February 2017, the Government of Vietnam promulgated Decree No.22/2017/ND-CP on Commercial Mediation (the "Decree"). It is the first legislation specifically governing commercial mediation in Vietnam.
Decree No. 22/2017/ND-CP on Commercial Mediation
On February 24, 2017, The Government promulgates the Decree No. 22/2017/ND-CP on commercial mediation.

redpajama_set_name: RedPajamaCommonCrawl


text:
Holiday parks and rental agencies
Sustainable recreation
My island
Today & tomorrow
VVV Goeree-Overflakkee
Bosweg 2
3253 XA Ouddorp
+31 (0) 187 - 681 789 info@vvvgoeree-overflakkee.nl
Monday to Friday 9 am - 5 pm
Discover Goeree-Overflakkee!
What would you like to do? Events Day out Night out Dinner Drinks Stay the night Excursions Music Theater Exhibition Kids Shopping
Specifick
Finding your location
Near {city}, {country}
Location not found
Couldn't find your location
Toekomst 70 Market Rcn toppershoedje Flower Toppershoedje Toekomst Nieuwsbrief Bach Tulip Flakkeese dagen
Charing stations
HomeSee & doSightseeing
Sightseeing on Goeree-Overflakkee
The world-famous Delta Works, harbour channels throughout the island, the Westhoofd lighthouse, the Goedereede tower, the lookout tower on the Hellegat Platen and windmills scattered across the island are just some examples of sights to see on Goeree-Overflakkee—connecting water and nature.
Beacons and lighthouses
Goedereede used to be surrounded by water. The small, but grandiose town was conveniently located adjacent to a large, undulating sea from which merchants and fishers sailed. For centuries, the tower of Goedereede served as a beacon for shipping. The silting up of the coastline caused the island to grow, making the beacon of Goedereede less and less visible. In 1911, the Westhoofd lighthouse was constructed. The lighthouse tower was destroyed by the German occupiers on 5 May 1945, at the end of the Second World War. The lighthouse was rebuilt in 1948, and in 2019 the national monument was given a fresh layer of purple-red paint. A must-see when you cycle along the North Sea coast.
The Delta Works
The sea giveth, the sea taketh away. Being an island, Goeree-Overflakkee has a history that is irrefutably connected to the water. The water has given the island a lot, but the fear of flooding was ever-present. The St Elisabeth's Flood in 1421, the All Saint' Flood in 1570 and the Flood Disaster of 1953 are moments in which the sea proved its capabilities. The now world-famous Delta Works had to prevent this from happening once and for all and protect the underlying areas. Goeree-Overflakkee is connected to Brouwersdam, the Haringvlietdam, the Philipsdam and the Volkerakdam.
There are many windmills, or gristmills to be precise, spread all over the island. Most of the windmills are groundsailers, but there are a few platform windmills. One windmill that is still operational is De Hoop, which still grinds flour every week. When possible, it runs on wind, but it has an electric motor for when there is insufficient wind.
The island is home to a plethora of historical buildings. In the atmospheric town of Middelharnis, in Flakkees called 'Menheerse', you will find, for example, the Town Hall, built-in 1639, popularly called 'the Old Town Hall'. The Chicory drier Ceres in Ouddorp is also a special building. As suggested by the name, wild chicory used to be dried there. The plant is closely related to witloof and endive and was used, among other things, for surrogate coffee. Production stopped in the fifties but the striking building remained standing. The possibilities for further renovation are currently being investigated and prepared.
The eternal struggle against water is inextricably linked to this island. Evidence of this is everywhere...
Old buildings and traces of the past can be found all over the island.
Green Key at Goeree-Overflakkee
+31 (0) 187 - 681 789
info@vvvgoeree-overflakkee.nl
A DINK and WebNL site
VVV Goeree-Overflakkee uses cookies to improve the website.
Click here to learn more about the cookie policy and the cookies we use.
Accept Don't accept


text:
Where have all the earthquakes gone? Oregon.
Cascadia subduction zone
Chris Goldfinger
CSZ fault
Drain the Oceans
full-margin rupture
Kansas earthquakes
Kathryn Schulz
magnitude 9
mega-quake
Oklahoma earthquakes
WHATS IN THIS BLOG: • Earthquakes in Oregon? • The big one is coming. • It will be the worst natural disaster in the history of North America.
I'VE WRITTEN ABOUT EARTHQUAKES IN OKLAHOMA, caused mainly by the oil-and-gas industry (see HERE and HERE). The numbers reached their peak in 2015-2016 and have been falling since then due partly to regulations by the Oklahoma Corporation Commission.
I've also written about Kansas earthquakes (see HERE), which were caused by the same oil-and-gas practices that spilled over the border from Oklahoma. Seismic activity dropped from 1,967 earthquakes in mid-2015 to 668 earthquakes at end of 2016 (both were 5-month recording periods). The number of quakes dropped to one-third of what it was in a period of 18 months, and this was partly due to new State regulations.… More
Is Fracking responsible for Earthquakes?
earthquake forecast
fault slip
geologic fault
granite basement
induced seismicity
Mississippi lime
WHATS IN THIS BLOG: • Earthquakes in my Iphone. • Fracking doesn't cause earthquakes. • Largest earthquake in Oklahoma was missed by forecasters. • Earthquakes are declining with time in Oklahoma. • What are the chances of a big one? • What to do if you are in the path of the big one.
THREE TIMES MY IPHONE WHISTLED AT ME LAST NITE. This means three earthquakes on my earthquake app. Here is what it told me: A 3.7 earthquake occurred close to Waynoka, Oklahoma. A 3.3 earthquake occurred close to Harper, Kansas. A 3.5 earthquake occurred close to Gardnerville, Nevada. The app tells me earthquakes of magnitude 3-4 can be felt by people but little damage.
The quakes in northern Oklahoma and southern Kansas have one thing in common: they occurred in an area that has been heavily drilled to extract oil from the Mississippi limestone.… More


How To Accidentally Get A Job In InfoSec.
Johnny Xmas will share with us the story of his extremely tangential path to Infosec, from recording studio intern to penetration tester, with stops at some great places like "pharmaceutical college" and "literal homelessness" along the way. Prepare to have your imposter syndrome cured and your resume boosted with this tale of just how far a pair of cat ears can get you!


I love to travel. I also revel in the fine detail work of crafting intricate itineraries. Planning a trip brings me as much joy—maybe more!—as setting out on the adventure itself.
After all, if my husband is coming along, he's taking rare time off from his demanding career. One of the divisions of labor that we've agreed to, in our partnership, is my assumption of responsibilities for vacation planning.
Also, DH is a homebody, so most trips are my idea. If his role isn't a relaxing one, he won't want to travel the next time. My family would lose out if my husband just stayed home.
I believe studies that suggest there are health benefits to travel, especially when a trip is well planned.
The kids need to see their dad with fewer distractions, stepping outside his comfort zone, and with more time than usual to spend with them. DH benefits by seeing the kids blossom in a new environment.
Plus, I miss him like crazy when we leave him home alone.
I want to give my overworked husband a relaxing break from his daily stresses. That's a loving gesture on my part because I like doing nice things for the man I love.
It's also good sense for a spouse who doesn't generate income. I am protecting our financial future by allowing the partner who brings home the paycheck to unwind a little.
My husband's success is due largely to his creative mind. He should also get credit for his hard work and specialized skills, but many people can and do work hard and complete advanced degrees. Few of them manage to push scientific boundaries in new directions as he does. A refreshed intellect generates better ideas.
Some vacations offer reduced efforts in the realms of housework and feeding the family. My favorite thing about staying in a hotel is walking into an immaculate room with nothing on the floor!
And eating in restaurants? It's hard to say how much I enjoy dodging the washing of dishes and the wiping of sticky counters. My admiration for those who work in food service borders on love and devotion. I hate most of these tasks, and I'm so grateful to those who are willing to do them for me.
But, though these jobs take up plenty of time at home, they don't comprise the bulk of my effortful work as a parent. They are necessary, but not particularly complex or demanding. Even at home, when I want a break, I can hire a house cleaner or take the kids out to eat.
The really challenging requirements of parenting relate to its most vital goal: raising small people into fully-formed adults.
Helping them—but not too much!
Most of these tasks get harder on vacation!
With all the predictable routines of daily life gone, we experience the thrill of something new. This has a cost of anxiety about the unknown. Using myself as an example, I know that I lose my cool more rapidly when I feel anxious. I don't blame the kids for doing the same.
My job is to keep my own composure, and offer enough strength of will to help the boys do the same. Or throw an upset child a lifeline that he can use to drag himself back to equanimity.
We grow when we are challenged. Changes—even positive ones—create challenges. Travel promotes growth, but it is rife with challenges, small and large.
Preparing my family for a trip is part of my "job description" as a stay at home mom. It's a task I enjoy, and one I do pretty well. It's not a burden.
That said, when we return from a really great vacation, I'm typically exhausted. Sometimes I even fall prey to "leisure sickness" (or something like it), succumbing to a cold as soon as the work of vacation preparations is complete.
Last month, for example, after a whirlwind road trip with a van full of boys and a week of family camp supervising the full crew, I "enjoyed" ten days of respiratory illness and coughing of the oh-my-aching-stomach-muscles variety.
Beyond the physical, returning home after weeks away comes with an emotional let down, too.
In other words, life goes on, and so does my work. I've even made more of it by going away.
But, I have learned to plan for at least one quiet day upon our return. When asked, I give the date we'll be home as a day later than my plan. That final "vacation day" gives me a chance to nudge our life back into order.
I don't schedule early appointments for a few days after a trip. I plan to sleep my fill until my body's ready to resume the usual routine.
I'll order groceries from Amazon Fresh or a similar delivery service if possible. There's usually a pizza night right after a trip.
I do what I can to ease the transition. I accept what I can't change as a cost of the new experiences gained. I let the post-vacation let down run its course and give myself permission to have mixed emotions.
I help the kids process their own transitions, too, from jet lag to lost toys to keeping in touch with new friends in faraway places.
And, in the middle of all this, I usually spend at least a few minutes daydreaming about what might be our next big adventure—between loads of laundry, that is.
← Road Trip! New England to Minnesota Part II: a mom, four kids, 1633 miles, and two hotel rooms.


text:
Q: Flexbox two rows same width with overflow I'm trying to create a "simple" information bar that should be displayed inline.
The bar consist of two divs, where the first contains all the required info (and is always visible) and the second shows information messages when they apply.
I have created a pen to demonstrate here.
My problem is that the content of the upper div is not always the same width and in some cases it overflows (which is a valid behavior based on my requirements since I always want it to be in one line). Thus when the screen gets shrinked enough the upper div overflows but the below keeps a width same as the screen width and does not follow the upper div's width.
What I want to achieve is make the below div have the same width as the upper even when the upper one overflows. Any ideas anyone?
Adding code here as well for reference:
HTML:

 Shrink me to see than warning div is not the same width as the other one

          21:12

 #28125

 This can be a long text...

 Yo mama

          <button>Stop</button>

          <button>Switch To #28192</button>

This is an information message

CSS:
#TaskTimeBar {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-direction: normal;
  -webkit-box-orient: vertical;
  -webkit-flex-direction: column;
  -moz-flex-direction: column;
  -ms-flex-direction: column;
  flex-direction: column;
  -webkit-flex-wrap: wrap;
  -moz-flex-wrap: wrap;
  -ms-flex-wrap: wrap;
  flex-wrap: wrap;
}
#main-wrapper {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
}
.task-time-bar-content {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
  padding: 5px;
}
#time-cell {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
  font-weight: bold;
  font-size: 22px;
}
.time-container {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-box-pack: center;
  -ms-flex-pack: center;
  -webkit-justify-content: center;
  -moz-justify-content: center;
  justify-content: center;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
}
.time-container i {
  padding-right: 5px;
}
#active-task-bar-main-content {
  padding: 0 10px;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-pack: space-around;
  -ms-flex-pack: space-around;
  -webkit-justify-content: space-around;
  -moz-justify-content: space-around;
  justify-content: space-around;
}
#active-task-bar-main-content div {
  padding: 0 10px;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
}
#active-task-bar-buttons {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  padding: 0 10px;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
  -webkit-box-pack: end;
  -ms-flex-pack: end;
  -webkit-justify-content: flex-end;
  -moz-justify-content: flex-end;
  justify-content: flex-end;
}
.active-bar-button-wrapper {
  line-height: 28px;
  margin-right: 5px;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
}
.active-task-bar-information {
  background-color: #ffa500;
  color: #f3ebf8;
  border: thin solid #808080;
  border-top: none;
  text-align: center;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-box-pack: center;
  -ms-flex-pack: center;
  -webkit-justify-content: center;
  -moz-justify-content: center;
  justify-content: center;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
}

Edit:
Let me explain a little bit more based on the div's ids as asked in the comments.
I hava a #TaskTimeBar that contains two divs inside, #main-wrapper and #active-task-bar-information. Requirements are as follows:

*

*#main-wrapper should always be in one line

*#active-task-bar-information should always have the same width as #main-wrapper and be underneath it.

The problem is that when the screen becomes small the contents of #main-wrapper overflow and exceed the screen width but #active-task-bar-information does not follow. If you play around with the window width in the linked pen you will see the effect.

A: Just to make sure I got this right:

*

*main-wrapper never actually wraps it's content, therefore it overflows.

*active-task-bar-information content actually wraps and never exceeds the viewport.

*main-wrapper's behavior is correct.

*active-task-bar-information's behavior is not correct. It should behave as it's sibling #main-wrapper.

Going by these criterions I think I got it. Try this:
html { box-sizing: border-box; font: 16px/1.5 Consolas; }
body { width: 100%; min-width: 60em; height: auto; }
*, *:before, *:after { box-sizing: inherit; margin: 0; padding: 0; border: 0; }
#TaskTimeBar {

  display: -webkit-inline-box;
  display: -webkit-inline-flex;
  display: -moz-inline-box;
  display: -moz-inline-flex;
  display: -ms-inline-flexbox;
  display: inline-flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-direction: normal;
  -webkit-box-orient: vertical;
  -webkit-flex-direction: column;
  -moz-flex-direction: column;
  -ms-flex-direction: column;
  flex-direction: column;
  -webkit-flex-wrap: nowrap;
  -moz-flex-wrap: nowrap;
  -ms-flex-wrap: nowrap;
  flex-wrap: nowrap;
  -webkit-box-pack: stretch;
  -ms-flex-pack: stretch;
  -webkit-justify-content: stretch;
  -moz-justify-content: stretch;
  justify-content: stretch;

}
#main-wrapper {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
}
.task-time-bar-content {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
  padding: 5px;
}
#time-cell {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
  font-weight: bold;
  font-size: 22px;
}
.time-container {
  display: -webkit-inline-box;
  display: -webkit-inline-flex;
  display: -moz-inline-box;
  display: -moz-inline-flex;
  display: -ms-inline-flexbox;
  display: inline-flex;
  -webkit-box-pack: center;
  -ms-flex-pack: center;
  -webkit-justify-content: center;
  -moz-justify-content: center;
  justify-content: center;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
}
.time-container i {
  padding-right: 5px;
}
#active-task-bar-main-content {
  padding: 0 10px;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  -webkit-box-pack: space-around;
  -ms-flex-pack: space-around;
  -webkit-justify-content: space-around;
  -moz-justify-content: space-around;
  justify-content: space-around;
}
#active-task-bar-main-content div {
  padding: 0 10px;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
}
#active-task-bar-buttons {
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
  padding: 0 10px;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
  -webkit-box-pack: end;
  -ms-flex-pack: end;
  -webkit-justify-content: flex-end;
  -moz-justify-content: flex-end;
  justify-content: flex-end;
}
.active-bar-button-wrapper {
  line-height: 28px;
  margin-right: 5px;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-flex-shrink: 0;
  -moz-flex-shrink: 0;
  -ms-flex-negative: 0;
  flex-shrink: 0;
}
.active-task-bar-information {
  background-color: #ffa500;
  color: #f3ebf8;
  border: thin solid #808080;
  border-top: none;
  text-align: center;
  display: -webkit-box;
  display: -webkit-flex;
  display: -moz-box;
  display: -moz-flex;
  display: -ms-flexbox;
  display: flex;
  -webkit-box-pack: center;
  -ms-flex-pack: center;
  -webkit-justify-content: center;
  -moz-justify-content: center;
  justify-content: center;
  -webkit-box-flex: 1;
  -webkit-flex-grow: 1;
  -moz-flex-grow: 1;
  -ms-flex-positive: 1;
  flex-grow: 1;
}

To get more accurate results I reset everything to border-box sizing, zeroed all margins, paddings, and borders. That's optional.
I changed how the parent flexbox (TaskTimeBar) contents are kept since main-wrapper and active-task-bar-information are siblings. The changes are as follows:
#TaskTimeBar {...
.....
  -webkit-flex-wrap: nowrap;
  -moz-flex-wrap: nowrap;
  -ms-flex-wrap: nowrap;
  flex-wrap: nowrap;
  -webkit-box-pack: stretch;
  -ms-flex-pack: stretch;
  -webkit-justify-content: stretch;
  -moz-justify-content: stretch;
  justify-content: stretch;
 }

TaskTimeBar (the parent) stretches it's children (main-wrapper and active-task-bar-information), past the viewport due to the justify property stretch and the flex-wrap property nowrap. As a side note, active-task-bar-information was always 2px shorter than main-wrapper until I did that reset and now they measure the same width in any sized viewport (as far as I'm able to determine).
Hopefully I understood your question properly and gave you appropriate advice.
EDIT: While I was fulfilling a request for a [demo][1], I added inline-flex to all three divs. Details are provided with the demo. Below are screenshots illustrating the 2 divs equal widths.

A: In this fiddle I've taken @zer00ne's code, and tried to simplify the situation, by keeping only the outer div a flex-box, instead of managing a hierarchy of flex-boxes. I've kept the inner divs in line with display: inline and white-space: nowrap. Is seems to achieve the desired result.

redpajama_set_name: RedPajamaStackExchange


What if I forgot my parking placard? Can I park in the Disabled Parking spots?
No, if you do not have your valid Disabled Parking placard on your vehicle, you cannot park in the Disabled parking spots. The Carlsbad police department monitors these spots daily and will ticket any vehicle that does not have their placard visible. Guests are responsible for any tickets they receive.


This is a small primed 10cm square canvas. The canvas measures 100mm x 100mm and is perfect for decorating and altering. We are an 'Angel' company and you are welcome to use our rubber stamps and other products to create handmade artwork to sell.


text:
Kelly Rizzo Declares Late Husband Bob Saget "The Most Incredible Man on Earth"
Disney CEO Bob Iger's Annual Pay Falls to $47.5 Million
The Walt Disney Company on Friday disclosed that chairman and CEO Bob Iger's compensation package was $47.5 million for the company's latest fiscal year, which ended in September. That compared with $65.6 million in fiscal 2018, which was boosted by a stock package that Iger was awarded as incentive to remain with the company past his originally planned retirement date.
Georg Szalai, Alex Weprin
Tristan Fewings/Getty Images
The Walt Disney Company on Friday disclosed that chairman and CEO Bob Iger's compensation package was $47.5 million for the company's latest fiscal year, which ended in September.
That compared with $65.6 million in fiscal 2018, which was boosted by a stock package that Iger was awarded as incentive to remain with the company past his originally planned retirement date. He earned $36.3 million in 2017 and $43.9 million in the year before that.
Disney disclosed the compensation for its top executives in a filing with the Securities and Exchange Commission on Friday afternoon. In the filing, the board wrote that it revised Iger's 2019 compensation "three separate times," after speaking with 11 of the company's top 20 shareholders, including six of its top 10. "Through that feedback, we learned of the concerns about certain aspects of Mr. Iger's employment agreement, including concerns from some shareholders regarding the amount of Mr. Iger's total compensation and the rigor of the performance criteria for Mr. Iger's one-time performance-based equity award," the board wrote in the filing.
"In an effort to appropriately balance the pay for performance design of our compensation program with this shareholder feedback, the Compensation Committee discussed with Mr. Iger, and Mr. Iger agreed on three separate occasions, to reduce for fiscal 2019 the compensation he would have otherwise been entitled to under his employment contract," the statement added.
2019 was a significant year for the company, as Disney closed its $71.3 billion mega-deal for large parts of the 21st Century Fox entertainment business. It also completely dominated the worldwide box office, with Avengers: Endgame becoming the highest-grossing release of all time, not adjusted for inflation.
For its latest fiscal year, the conglomerate reported net income from continuing operations of $10.4 billion, down 17 percent from $12.6 billion in the previous year, on revenue of $69.6 billion, up 17 percent.
After the close of the fiscal year, it also launched its Disney+ streaming service, which analysts have called a transformative refocusing of the Hollywood giant. Iger himself has called it the "most important product" launch since he became CEO in 2005.
The streaming service — whose original content offerings include Star Wars series The Mandalorian, featuring breakout star Baby Yoda; a new live-action Lady and the Tramp; and a High School Musical reboot — reported 10 million signups after one day.
The entry into streaming will also result in Disney reevaluating the company it considers in its industry "peer groups."
"For fiscal 2020, the Committee expanded the Company's media industry peer groups to include more technology-focused companies entering the media industry, adding Alphabet, Amazon.com, Apple, AT&T, Discovery, Facebook and Netflix to our media industry peers, and retaining current peers, CBS, Comcast and Viacom," the board wrote in the filing.
Iger has said he will retire at the end of 2021, with observers discussing his likely successor. Many believe the inside track may belong to Kevin Mayer, chairman of direct-to-consumer and international.
Disney CEO Bob Iger's Annual Pay Rises 80 Percent to $65.6 Million
Bob Iger
Netflix Increases Subscription Price in U.S. and Canada
Triller's Suit Against Podcasters Over "Troll" Reviews Tossed by Judge
TikTok Creator and YouTuber Kris Collins Signs With UTA
Art House Streaming Platform Mubi Buys European Sales Company Match Factory
Disney Stock Gets Downgrade on Higher Streaming Spending, Theme Parks Outlook
Euro Cinema Group Predicts 75 Percent Box Office Growth in 2022