Latest / Deep Dive Ortho — Orthopaedic Surgery, AI & Digital Health Podcast. / Orthobiologics 2

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Orthobiologics 2 · Deep Dive Ortho — Orthopaedic Surgery, AI & Digital Health Podcast.

0:00
Trying to truly fix a joint after an injury feels
0:02
like it should be straightforward in the 21st
0:04
century, doesn't it? It really does feel that
0:06
way sometimes. But think about this. Even, well,
0:10
a seemingly small tear in the ankle's delicate
0:12
network of ligaments or maybe a subtle rip in
0:16
the hip labrum can fundamentally change how forces
0:19
travel through the joint. Absolutely. It can
0:22
lead to complex long -term issues down the line.
0:24
Or considered knee replacement. after all that
0:28
sophisticated surgery, replicating the fluid,
0:30
natural motion of your original knee, well, it
0:34
remains a significant challenge. That's right.
0:36
It often limits the very activities patients
0:38
hope to return to. So why is it so incredibly
0:41
difficult to perfectly fix a joint once it's
0:44
damaged, to fully restore its native function?
0:47
What intricate secrets do our body's own mechanics
0:50
still hold that perhaps evade our best repair
0:53
efforts? Welcome to the Deep Dive. We take stacks
0:56
of information from dense textbooks to cutting
0:58
-edge research and distill the most important
1:01
nuggets of knowledge to help you get well -informed,
1:03
fast. A valuable service. Today we're plunging
1:06
into the absolutely fascinating world of orthopedic
1:09
biomechanics. Specifically, we're zeroing in
1:12
on how these mechanical principles govern sports
1:14
injuries and how we attempt to fix them. Our
1:19
guide for this journey is a foundational source.
1:22
A comprehensive textbook, orthopedic biomechanics
1:26
and sports medicine put together by a global
1:28
collective of leading experts. A really thorough
1:30
piece of work. And to help us navigate this wealth
1:33
of information and unpack the key insights for
1:36
you, we have our expert guide today. He brings
1:39
deep expertise in biomechanics and a remarkable
1:43
ability to synthesize complex material into understandable
1:47
concepts. Happy to be here and dive into it.
1:49
Great. Thank you for joining us. Let's maybe
1:51
kick off with a few rapid -fire questions straight
1:54
from the core of this material just to set the
1:56
stage. Okay, sounds good. From the foundational
1:58
chapters of this textbook, what's one fundamental
2:00
principle of biomechanics that someone absolutely
2:04
must grasp to understand how our joints cope
2:07
under load? It's really about the material properties.
2:11
You have to understand them. Each tissue type
2:13
in a joint bone, ligament, tendon, cartilage,
2:17
behaves uniquely under stress. Understanding
2:19
how, say, ligaments resist tension or how cartilage
2:23
handles compression through its sort of biphasic
2:26
nature, that's utterly fundamental. Right. You
2:30
really can't appreciate the resilience or vulnerability
2:32
of a joint without knowing the inherent strengths
2:35
and weaknesses of its constituent parts. The
2:37
building blocks, as you might say. That makes
2:40
intuitive sense. The building blocks definitely
2:41
matter. Now, when we talk about repair, the book
2:44
details techniques for different tissues. Is
2:46
there a core biomechanical challenge that just
2:49
crops up again and again, regardless of whether
2:51
you're trying to fix a ligament, a tendon, cartilage,
2:54
or maybe using a bone graft? Yes, that's a crucial
2:56
point, actually, about restoration versus replication.
2:59
The consistent challenge is that biological repair,
3:02
or even surgical reconstruction, it rarely perfectly
3:06
replicates the native tissue's original mechanical
3:08
properties, or its intricate architecture. So
3:10
it's never quite the same. Exactly. We often
3:13
end up with scar tissue or perhaps replacement
3:15
material that's mechanically inferior or sometimes
3:18
just different. And that impacts how the joint
3:21
functions under stress compared to how it was
3:23
before the injury. And technology plays a growing
3:25
role here, doesn't it? The source highlights
3:28
tools like finite element analysis, FEA. How
3:31
is that fundamentally changing how we approach
3:34
understanding and treating joint injuries? Well,
3:37
FEA is a bit of a game changer. It allows us
3:39
to create these sophisticated virtual models
3:41
of joints and then simulate how forces and stresses
3:45
distribute within them. So you can test things
3:47
out virtually. Precisely. We can test hypotheses
3:49
about entry mechanisms. We can evaluate surgical
3:52
plans before cutting any tissue or predict how
3:54
implants will behave under load. It provides
3:56
insights we simply couldn't get from, say, physical
3:59
tests or imaging alone. It offers a predictive
4:02
power that just wasn't available previously.
4:05
Fascinating. Finally, this material dives into
4:08
the specifics of different joints. Why does paying
4:11
close attention to incredibly subtle anatomical
4:14
details, things like specific ligament attachments
4:17
or the precise shape of a joint surface, become
4:20
so critical when dealing with injuries in areas
4:22
like the shoulder or ankle? It's because joints
4:25
are systems of, well, carefully balanced constraints
4:28
and motions. Think about the ankle. The specific
4:31
orientation and tension of tiny ligaments dictate
4:34
stability through a full range of motion. In
4:36
the shoulder, it's the dynamic interaction of
4:38
muscles and the subtle angulation of the glenoid
4:42
socket that are key. So the small stuff really
4:44
matters? Absolutely. Small anatomical details
4:46
aren't just academic points, they're biomechanical
4:49
levers. If you disrupt one small part, it can
4:52
have disproportionate effects on the entire joint
4:54
stability and its load bearing capacity. And
4:56
that predisposes it to further injury or degeneration
5:00
down the line. Those rapid -fire points really
5:03
underscore the complexity, don't they? Let's
5:05
dive deeper into that first area you mentioned,
5:08
the foundational understanding of how these distinct
5:10
tissues behave under load. The textbook makes
5:14
it abundantly clear these aren't just passive
5:16
materials, they have active measurable biomechanical
5:20
personalities. Absolutely, and understanding
5:22
these personalities, as you put it, is the starting
5:24
point for everything else. Take ligaments, for
5:27
example. Their primary job is to resist tensile
5:30
forces, so pulling or stretching. Think of them
5:32
as biological ropes that check or limit excessive
5:35
joint motion. They have a specific stress strain
5:38
curve showing how they elongate under load before,
5:41
well, ultimately failing if the load is too high.
5:44
And the book details how surprisingly difficult
5:47
it is even to measure that strength accurately
5:49
in a lab setting. Why is that? Well, what's fascinating
5:52
here is the practical challenge. How do you grip
5:55
a soft, complex biological tissue without damaging
5:58
it or having it slip? I can see how that would
6:00
be tricky. It is. If your clamps are too aggressive,
6:03
you induce stress concentrations right there
6:05
at the clamping site. Then the ligament fails
6:07
there, not in the mid -substance where you want
6:10
to measure its true properties. So how do researchers
6:12
get around that? They use clever techniques,
6:16
things like serrated clamps or embedding the
6:18
ends in resin and then freezing them, or even
6:21
non -contact methods using markers and cameras
6:24
to track deformation along the ligament's length,
6:27
all trying to get an accurate picture of its
6:28
real behavior. And their healing process. It's
6:32
notoriously slow and often imperfect, leading
6:34
to scar tissue. What's the biomechanical and
6:37
biological reason for that slowness? Well, their
6:40
biology really dictates it. Ligaments have relatively
6:44
low cell density, and they're hypovascular, meaning
6:46
they have a limited blood supply compared to,
6:48
say, muscle tissue. Ah, okay. This restricts
6:51
the delivery of healing factors and cells needed
6:53
for repair. The healing process itself, as described
6:56
in the source, follows a four -phase cascade,
7:00
initial bleeding and inflammation, then proliferation,
7:03
where fibroblasts lay down a temporary matrix,
7:05
and then a very long remodeling phase. And that
7:07
remodeling takes a long time. It does. Crucially,
7:11
the new matrix laid down is often primarily weaker
7:14
type 3 collagen initially. That's only slowly
7:18
replaced by the stronger type I collagen found
7:20
in the native ligament. This remodeling and reorganization
7:24
into properly aligned fibers under load takes
7:27
months, sometimes even years. And the result,
7:30
often tissue that is mechanically inferior to
7:32
the original. So it never quite gets back to
7:35
100%. Often not. The MCL, the medial collateral
7:38
ligament in the knee. It's a classic example.
7:41
It's an extra -articular ligament outside the
7:43
joint capsule, and it follows this relatively
7:45
slow but often quite successful healing pathway.
7:48
However, even then, the heel tissue is still
7:51
biomechanically different from the native ligament.
7:53
That difference between the original and the
7:55
heel tissue seems like a recurring theme, doesn't
7:57
it? It really is. Moving on to tendons, they
8:00
seem built differently to handle load. Tendons
8:02
are primarily designed to transmit forces from
8:04
muscle to bone. Their structure reflects this.
8:07
They are highly organized, almost modular units.
8:10
The basic building block is the type I collagen
8:12
triple helix. These aggregate into fibrils, which
8:16
then bundle into fibers and then into fascicles.
8:19
It's this hierarchical structure that allows
8:21
them to be so strong under tension. The source
8:24
points out the concept of load capacity, the
8:27
amount of force a tendon can withstand before
8:29
damage. And this capacity varies massively between
8:33
individuals. Depending on activity levels. Exactly.
8:35
Which is why the patellar tendon of a professional
8:37
weightlifter is dramatically different biomechanically
8:41
from that of a sedentary individual. It's adapted
8:43
to handle much higher stresses through remodeling.
8:46
And there's an interesting hypothesis mentioned
8:48
about the different types of collagen fibrils
8:50
within tendons. Yes. The textbook discusses this
8:54
idea that tendons contain both large and small
8:57
diameter collagen fibrils. The hypothesis is
9:00
that the large fibrils are the primary load bearers
9:02
resisting that tensile stress. And the smaller
9:04
ones. The smaller, perhaps newly synthesized,
9:07
fibrils might play a role in repairing micro
9:10
damage and supporting the structure between the
9:12
larger fibers. It suggests is this ongoing process
9:15
of adaptation and maintenance happening within
9:18
the tendon structure, constantly responding to
9:20
daily loading. Fascinating. Let's shift to cartilage,
9:24
that smooth shock -absorbing material on the
9:27
ends of our bones. It's described in the book
9:29
as a biphasic medium. What does that mean, and
9:32
why is it so crucial for its function? Biphasic
9:35
essentially means it has two phases. There's
9:38
a solid phase, made up of collagen, protiglycans,
9:40
or PG's, and chondrocytes, those are the cartilage
9:43
cells. And then there's a fluid phase, which
9:45
is primarily water. This structure is absolutely
9:49
key to how it handles compressive loads. like
9:51
when you step or jump. How does that work? Well,
9:54
compression is resisted by two main mechanisms.
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Firstly, there's a flow -independent mechanism.
9:58
This comes from the negative charges on the PG's,
10:00
which repel each other within the collagen network,
10:03
resisting collapse. Okay, sort of like internal
10:05
springs. In a way, yes. But secondly, and perhaps
10:09
more importantly, there's a flow -dependent mechanism.
10:12
When you compress cartilage, the fluid in the
10:14
tissue is squeezed out through the solid matrix
10:17
and across the articular surface. Right. Because
10:20
cartilage has very low permeability, this fluid
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flow is slow. That creates a frictional drag
10:26
that resists the compression. This is known as
10:29
viscoelastic behavior, essentially the tissue's
10:33
time -dependent response to load due to that
10:36
fluid movement. It's vital for absorbing impact
10:38
and protecting the solid matrix from excessive
10:41
stress. So it's not just a simple cushion, it's
10:44
more like a very stiff, slow -moving, fluid -filled
10:47
sponge that dissipates energy. Exactly, that's
10:49
a very good analogy. That fluid phase and its
10:52
controlled movement are critical for protecting
10:54
the solid framework. Now bone grafts are another
10:56
essential tool in orthopedic surgery. The source
10:59
goes into detail about different types and why
11:01
autographed is often called the gold standard.
11:03
Yes, autographed is using the patient's own bone.
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What makes it the benchmark? It's because autograft
11:08
inherently possesses all three key properties
11:11
needed for optimal bone formation. First, osteogenicity.
11:15
It contains live bone -forming cells. Okay. Second,
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osteoinductivity. It contains growth factors
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that signal surrounding cells to become bone
11:24
-forming. And third, osteoconductivity. It provides
11:27
a physical scaffold for new bone to grow across.
11:30
Plus it's your own. Tissue. Exactly. So it's
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histocompatible, non -immunogenic, and carries
11:35
minimal risk of disease transmission or infection
11:38
compared to using donor bone. What about allografts,
11:41
then, from a donor? They seem necessary when
11:43
a lot of bone is needed, but they come with different
11:45
challenges, right? They do. Allografts from deceased
11:48
donors are widely used, especially for larger
11:50
defects, but they do carry theoretical risks
11:53
of immune reaction and disease transmission,
11:55
although modern tissue banking processes have
11:57
really significantly reduced these concerns.
11:59
But the processing affects the bone. Yes, that's
12:02
the trade -off. These processing methods, like
12:05
freezing or freeze drying while enhancing safety,
12:08
can also reduce the graft's biological activity.
12:11
They might damage or remove those osteogenic
12:13
cells and potentially reduce the osteoinductive
12:16
signals. So less biologically active? Potentially,
12:19
yes. So there's an inherent trade -off between
12:22
safety and preserving that biological potential
12:24
for bone formation. Structurally, allografts
12:27
can provide immediate mechanical support, but
12:30
processes like freeze drying, while great for
12:33
storage, can reduce the bone's mechanical strength.
12:36
The source cites a figure of around a 20 % reduction.
12:39
Wow, 20 %? It's significant. So you have to weigh
12:42
the need for structural support against the desire
12:44
for rapid biological incorporation when choosing.
12:47
And the newer options like cellular allografts
12:49
and capsiminis, how do they fit in? Cellular
12:52
allografts are an attempt to bridge that jab.
12:54
They provide a scaffold along with live mesenchymal
12:57
stem cells MSCs from a donor aiming for osteogenicity
13:00
without needing to harvest the patient's own
13:01
bone. But they have hurdles. They do. Because
13:04
they contain live cells, they require much more
13:07
stringent screening and face greater regulatory
13:10
hurdles. Calcium phosphate or campy cements are
13:14
synthetic materials. They're primarily used as
13:16
osteoconductive scaffolds to fill bone voids.
13:20
Their mechanical properties depend a lot on their
13:23
composition and porosity. Some are designed to
13:25
be more porous and resorb faster, but they tend
13:28
to lose strength as they resorb. So lots of factors
13:31
to consider. Definitely. Selecting the right
13:33
graft material involves a careful consideration
13:35
of all these biological and mechanical properties,
13:38
the required structural support, and the compromises
13:41
involved in each option. Fascinating how even
13:43
the material choice is such a complex biomechanical
13:46
calculation. You briefly touched on muscle actions
13:49
earlier, noting eccentric actions are more injury
13:52
-prone. Yes, eccentric contraction, that's what
13:53
a muscle lengthens under load, like lowering
13:55
yourself slowly into a squat, is critical for
13:58
controlling movement and absorbing shock. But
14:00
riskier. It generates higher forces per unit
14:03
area within the muscle and tendon compared to
14:05
concentric or shortening actions. So if the load
14:08
exceeds the tissue's capacity during a rapid
14:11
or uncontrolled eccentric movement, it significantly
14:14
increases the risk of muscle strain or tendon
14:16
tear. Right. All of this fundamental understanding
14:18
must feed into how we actually analyze mechanics.
14:21
And that's where finite element analysis, FEA,
14:24
comes in. Could you elaborate on how FEA, which
14:28
sounds very much like an engineering tool, became
14:30
so crucial in orthopedics? Well, FEA was indeed
14:34
developed in structural engineering. You know
14:36
analyzing complex loads on things like bridges
14:38
or airplane wings, right? But biological structures
14:41
like joints and bones with implants are also
14:44
complex structures subject to complex loads Fea
14:47
allows us to create a virtual 3d model of say
14:50
a femur with a hip implant. Okay, we then just
14:53
Could tease this model essentially break it down
14:55
into millions of tiny geometric elements each
14:57
connected at points called nodes We can then
15:00
apply boundary conditions and loads to this virtual
15:02
model mimicking physiological forces like muscle
15:05
contraction or weight -bearing Simulating real
15:08
-life stresses exactly the software solves complex
15:11
equations at each node To calculate the resulting
15:14
stress that's force per unit area in strain,
15:17
which is the deformation So it's like creating
15:20
a detailed stress map of the bone or joint. Precisely.
15:23
This stress map shows us where forces are concentrating
15:26
and where the tissue is deforming the most. This
15:29
is invaluable in orthopedics. How is it used
15:31
specifically? We use it to predict how different
15:34
implant designs will affect stress distribution
15:36
in the surrounding bone, which is absolutely
15:39
key for preventing loosening or fractures later
15:41
on. We can analyze the biomechanical changes
15:44
caused by different surgical techniques, or even
15:47
optimize the design of orthopedic devices like
15:49
splints or braces by modeling their forced displacement
15:52
characteristics. What are the main hurdles in
15:55
using FEA clinically? It sounds powerful, but
15:57
maybe complex to implement. It is powerful, but
16:00
there are challenges. The main ones mentioned
16:02
in the source are the sheer complexity of biological
16:04
tissues and their properties that can vary significantly
16:07
between individuals. Then there's validating
16:10
the models against real -world data, interpreting
16:12
the massive output of data in a clinically meaningful
16:15
way, and crucially, making these tools user -friendly
16:19
enough for surgeons to use in routine practice.
16:22
So it requires collaboration. Absolutely. It
16:25
requires close collaboration between biomechanical
16:28
engineers and experienced clinicians to bridge
16:30
that gap between theoretical models and practical
16:33
clinical application. Understanding those foundational
16:36
tissue properties and analytical tools like FEA
16:39
is clearly essential. It provides the context
16:42
for understanding why joints, which perform such
16:44
intricate biomechanical balancing acts, are prone
16:47
to specific injuries. Let's pivot now and apply
16:50
this lens to some specific examples from the
16:52
textbook, starting with the shoulder. It's famed
16:55
for its mobility, but that must come at a cost
16:57
to stability, right? Absolutely. The glenohumeral
17:00
joint, the main shoulder joint, has the greatest
17:02
range of motion in the body. And that's largely
17:05
due to its relatively flat socket, the glenoid,
17:08
and the large ball of the humeral head. So how
17:09
does it stay stable? Stability is achieved through
17:12
a really delicate balance of static and dynamic
17:15
components. Scatic stability comes from things
17:17
like the bony anatomy, the subtle retroversion
17:20
or backward angulation of the glenoid and the
17:23
labrum. The labrum? That's the cartilage, right?
17:25
Yes, exactly. It deepens the socket. And then
17:28
you have the capsular ligaments, which are particularly
17:30
strong at the front of the shoulder. Dynamic
17:33
stability comes from the surrounding muscles,
17:35
primarily the rotator cuff, which actively compress
17:38
the humeral head into the glenoid and coordinate
17:41
complex movements, along with muscles controlling
17:43
the scapula's position. The labrum's role seems
17:46
more significant than just being a simple room.
17:49
The source mentions the concept of a suction
17:51
seal. Can you explain that? Yes. The labrum is
17:54
crucial. It definitely adds to the socket depth.
17:57
Howell and Galeant quantify that contribution,
17:59
increasing the bony congruency. But it also works
18:02
with the joint capsule to create a negative intraarticular
18:05
pressure. Essentially a suction seal. Like a
18:07
vacuum. Pretty much. Studies... particularly
18:10
in hip, which has a similar mechanism, have shown
18:12
this suction seal provides a significant portion
18:15
of the joint's resistance to distraction, especially
18:18
in the initial millimeters of movement. So a
18:21
labral tear disrupts this seal, immediately reducing
18:24
that passive stability and altering the joint's
18:27
kinematics, even if the bony structures themselves
18:29
are intact. So a labral tear isn't just a structural
18:32
defect, it's also breaking a crucial biomechanical
18:35
vacuum. Wow. Exactly. It changes the subtle mechanics
18:39
of how the joint moves and loads. When this overall
18:42
static and dynamic balance is disrupted, that's
18:44
when you see problems like glenohumeral instability
18:47
or rotator cuff tears. And biomechanics helps
18:50
explain why these happen. It does. For rotator
18:53
cuff tears, the source points to factors like
18:55
degenerative changes, often starting in what's
18:58
called a critical zone of the supraspinatus tendon.
19:01
This area has a relatively limited blood supply,
19:04
making it more vulnerable to mechanical overload
19:06
or impingement. And the specific pattern of the
19:09
tear matters biomechanically. Oh, absolutely.
19:12
Small, isolated tears might have minimal impact
19:15
on overall kinematics. But larger tears, especially
19:18
those extending into the subscapularis tendon
19:20
at the front, can lead to significant superior
19:23
migration of the humeral head. Why is that? Because
19:27
they disrupt crucial force couples that normally
19:30
keep the head centered. There's this concept
19:32
called the rotator cuff cable. supported by cadaveric
19:35
studies, it highlights that the anterior portion
19:38
of the rotator cuff acts like a strong cable,
19:41
resisting this upward translation of the humeral
19:43
head. If that cable is intact, even with tears
19:47
behind it, superior migration is limited. But
19:50
if the tear extends through the cable, the humeral
19:52
head can rise significantly. Throwers shoulder
19:55
example is a perfect illustration of how repeated
19:58
specific biomechanical stress leads to specific
20:00
injury patterns, isn't it? It is, absolutely.
20:03
Overhead athletes like baseball pitchers develop
20:04
incredible throwing speeds, but it comes at a
20:07
biomechanical cost. How do they adapt? They adapt,
20:09
for instance, by increasing scapular upward rotation
20:12
to create more space under the acromeon during
20:15
the overhead phases of throwing. However, the
20:19
repetitive stress Particularly, the extreme external
20:22
rotation during the late cocking phase can cause
20:24
what's called internal impingement. What's that?
20:27
That's where the posterior rotator cuff and the
20:30
labrum get compressed against the posterior rim
20:33
of the glenoid. This can lead to injuries like
20:36
post lesions, partial articular supraspinatus
20:39
tendon avulsions, or SLAP tears, which are superior
20:43
labral tears. And they can develop other changes,
20:45
too. Yes. Furthermore, over time, some athletes
20:48
develop acquired scapular changes. Their scapula
20:51
might become more internally rotated or tilted
20:54
interiorly. This might be a way to compensate
20:56
for a restricted follow -through motion after
20:58
throwing. But these altered scapular mechanics
21:01
can actually reduce the subacromial space, leading
21:03
to secondary external impingement, the more common
21:06
type of shoulder impingement seen in non -athletes.
21:09
Wow. Cadaveric studies have confirmed that increasing
21:11
scapular internal rotation significantly increases
21:14
contact pressure in the glenohumeral joint itself.
21:17
It really is a complex chain reaction of adaptation
21:20
and potential injury. Moving down to the knee
21:23
now, ligaments are clearly paramount for stability
21:26
there. The knee's stability is just a masterpiece
21:28
of ligamentous checks and balances. You have
21:31
the collateral ligaments, the MCL and LCL, controlling
21:33
side -to -side motion. Right. And then the cruciate
21:36
ligaments, the ACL and PCL, controlling front
21:39
-to -back translation and rotation. The MCL complex
21:42
on the inside of the knee is particularly robust.
21:45
It comprises superficial and deep layers, plus
21:47
the posterior oblique ligament, or POL. What's
21:51
its main job? Its primary role, as the source
21:53
details, is to resist valgus forces, forces pushing
21:57
the knee inward, and to limit internal tibial
21:59
rotation. It also plays a secondary role in resisting
22:02
external rotation and anterior translation, especially
22:06
when the tibia is externally rotated. Modern
22:08
reconstruction techniques aim to restore this
22:10
complex anatomy with multiple graphs to try and
22:13
achieve near -normal stability. OK. And on the
22:15
outside, you have the LCL and the post -relateral
22:17
complex, or PLC. Correct. The LCL resists varous
22:22
forces. It's outward forces. The postural lateral
22:25
complex is a collection of structures, including
22:27
the pallidius tendon and the poplidofibular ligament,
22:30
and it works together with the LCL. What does
22:32
the PLC do? This complex is essential for resisting
22:36
varous stress. It significantly limits posterior
22:39
tibial translation, especially if the PCL wasn't
22:41
functional, and it's the primary restraint to
22:44
excessive external tibial rotation. While its
22:47
role in limiting internal rotation is smaller,
22:50
its integrity is critical for overall knee stability,
22:53
and injuries here often involve multiple structures.
22:55
It's a complex area. The ACL and PCL are often
22:58
talked about as a pair working together. They
23:00
work very synergistically. The textbook mentions
23:02
the four -bar linkage concept, which is a biomechanical
23:06
model that helps explain how the ACL and PCL
23:08
guide the tibia's movement relative to the femur
23:11
through the knee's range of motion. So specific
23:13
roles. Yes. The ACL is the primary barrier stopping
23:16
the tibia from shifting too far forward, particularly
23:18
at lower flexion angles. The PCL is the primary
23:21
barrier stopping the tibia from shifting too
23:23
far backward. And if the PCL is deficient, what
23:26
are the biomechanical consequences of that? Well,
23:29
a deficient PCL results in increased posterior
23:31
tibial translation. The tibia basically sags
23:35
backward relative to the femur. And that changes
23:38
things. It significantly alters the loading patterns
23:40
across the joint. Clinically, you might see what's
23:43
called a varus thrust gait, where the knee seems
23:45
to push outwards during walking. But more importantly,
23:48
from a long -term perspective, this posterior
23:51
shift significantly increases contact pressures
23:54
in the medial compartment of the knee, and also
23:57
the patella -feral joint, the joint behind the
23:59
kneecap. And that leads to... Adavric studies
24:01
have repeatedly shown this increase in pressure.
24:03
This abnormal loading pattern accelerates cartilage
24:06
wear, predisposing patients to early osteoarthritis
24:09
in those specific areas. Finally, let's consider
24:11
the ankle, another joint that relies heavily
24:14
on its ligamentous structure for stability. Indeed.
24:17
The ankle joint proper, the tabulcural joint,
24:19
is primarily a hinge joint, allowing up and down
24:22
movement, dorsiflexion, and plantar flexion.
24:25
Side -to -side stability is almost entirely provided
24:27
by the ligaments. Which ones are key? The lateral
24:29
complex, on the outside, consists of three main
24:32
ligaments. the anterior telofibular ligament,
24:35
ATFL, the calcaneofibular ligament, CFL, and
24:39
the posterior telofibular ligament, PTFL. These
24:42
resist inversion and varus forces with their
24:44
specific contributions changing depending on
24:46
whether the foot is pointed up or down. The ATFL
24:49
is the one most commonly injured in ankle sprains.
24:52
And on the inside? On the medial side, you have
24:54
the robust deltoid ligament complex, which resists
24:57
aversion and abduction. and then slightly above
24:59
the ankle, the syndesmotic ligaments hold the
25:02
tibia and fibula together, resisting external
25:04
rotation of the talus cone within the mortis
25:07
or socket. When these ligaments are injured and
25:09
don't heal well, chronic ankle instability can
25:12
develop. How does that change the biomechanics?
25:15
Well, chronic instability means the normal checks
25:17
on excessive motion are gone or impaired. This
25:20
leads to altered gait biomechanics. Studies show
25:23
individuals with chronic instability often have
25:25
increased inversion motion during the swing phase
25:27
of walking and also at heel strike. And that
25:30
has knock -on effects. Yes, this abnormal movement
25:32
and loading can increase forces transmitted through
25:35
the lateral side of the foot. It can also lead
25:38
to compensatory movement patterns higher up the
25:40
kinetic chain in the knee and hip. And the source
25:43
has a really stark statistic about how critical
25:45
this ligamentous stability is for joint contact.
25:48
Can you share that again? Yes. This is one of
25:51
the most important takeaways regarding the long
25:53
-term health of the ankle joint. Ramsey and Hamilton's
25:56
classic study, cited in the source, demonstrated
25:59
something quite remarkable. What was it? They
26:01
show that if the talus bone is shifted laterally
26:03
by just one millimeter within the ankle mortis,
26:06
something that can easily happen with combined
26:08
ligamentous injuries, like a deltoid rupture
26:11
plus a fibula fracture, the contact area between
26:15
the talus and the tibia is reduced by a staggering
26:17
42%. 42%, just from one millimeter. 42%. Think
26:22
about that. A tiny shift, barely noticeable visually,
26:27
nearly halves the circus area over which load
26:29
is transmitted. This dramatically increases the
26:31
pressure on the remaining cartilage, accelerating
26:33
its wear and leading directly to degenerative
26:35
joint disease or ankle arthritis much earlier
26:38
than it would otherwise occur. It really highlights
26:41
the absolute necessity of restoring anatomical
26:43
alignment and stability in the ankle. That 1
26:46
millimeter 42 percent statistic is truly eye
26:49
-opening. It perfectly illustrates the delicate
26:51
balance involved. So given this deep understanding
26:54
of tissue properties, joint mechanics, and these
26:56
injury patterns, how do these biomechanical principles
26:59
directly drive the choices surgeons make? And
27:02
how do they shape the outcomes patients can realistically
27:05
expect from orthopedic treatments? Let's start
27:07
with ligament reconstruction, like the ACL. OK.
27:10
When reconstructing a ligament like the ACL,
27:12
biomechanics heavily influences the graft choice
27:14
and the fixation techniques used. The textbook
27:17
compares commonly used autografts, the patellar
27:19
tendon, or BPTB, and hamstring tendons, HT. What
27:23
are the differences? Well, biomechanical studies
27:26
show BPTB grafts often have a higher initial
27:29
load to failure, and they offer bone -to -bone
27:31
healing, which potentially provides quicker initial
27:33
stability. However, they could be associated
27:36
with more anterior knee pain and sometimes patellar
27:40
stiffness. And hamstrings. Hamstring grafts may
27:43
lead to less anterior knee pain, but historically
27:46
there were concerns about fixation strength and
27:48
potential stretching over time. Though, modern
27:52
fixation techniques and using multiple strands
27:54
like a quadrupled graft have significantly improved
27:57
this. Long -term studies, including a 15 -year
28:00
follow -up mentioned in the source, suggest comparable
28:02
laxity rates between HT and BPTP over the long
28:06
haul, but differences in other outcomes like
28:08
pain or kneeling difficulty can persist. So surgeons
28:11
weigh these factors. Exactly. Surgeons weigh
28:13
these biomechanical pros and cons alongside patient
28:16
factors like age, activity level, and specific
28:18
demands to make the best choice for that individual.
28:21
And for PCL reconstruction, there are also different
28:24
surgical approaches with biomechanical implications.
28:27
Yes, precisely. Comparing the trans -tibial tunnel
28:29
technique to the tibial inlay technique for PCL
28:32
reconstruction. Well, biomechanical studies highlight
28:36
a significant concern with the trans -tibial
28:38
method. What's that? The acute angle where the
28:40
graft exits the tibia tunnel, the killer turn
28:43
as it's sometimes called, can cause the graft
28:46
to rub against the bone. This risks graft abrasion
28:49
and weakening over time. And the inlay technique
28:52
avoids this? Yes, the tibial inlay technique
28:55
avoids this acute angle by attaching the graft
28:57
directly onto the back surface of the tibia.
29:00
Biomechanical tests have shown it provides superior
29:02
strength after cyclical loading, suggesting potentially
29:05
better durability. Again, graft choice matters
29:08
here too. While quadrupled hamstring grafts show
29:10
high ultimate load to failure, some biomechanical
29:13
tests suggest they might have less resistance
29:15
to stretching compared to BPTB grafts when used
29:18
for the PCL. There's also increasing interest
29:20
in adding extra -articular procedures like a
29:23
lateral extra -articular tenodesis, LAT, or perhaps
29:26
an all anterolateral ligament reconstruction
29:28
alongside ACL reconstruction, especially for
29:32
patients with high -grade instability. What's
29:35
the biomechanical rationale there and what are
29:38
the potential downsides? Right. The biomechanical
29:40
goal of adding an LET or all reconstruction is
29:44
to provide supplemental restraint on the anterolateral
29:47
side of the knee. What does that achieve? It
29:49
helps resist anterior tibial translation and
29:52
also internal rotation, especially at lower flexion
29:55
angles. It can potentially load -share with the
29:58
ACL graft, theoretically protecting it in high
30:00
-stress situations like pivoting movements. It's
30:03
often considered for patients with significant
30:05
rotational instability a high pivot shift on
30:08
examination, or those deemed at high risk of
30:10
ACL graft re - rupture, like young athletes returning
30:13
to pivoting sports. But there are concerns. Yes,
30:16
the biomechanical concern is that adding a structure
30:18
that's tensioned outside the joint's natural
30:20
axis of rotation could potentially constrain
30:23
normal knee motion. Over -constrain it. Prudentially.
30:27
Studies have shown that while these procedures
30:28
effectively reduce that pivot shift in stability,
30:32
they can slightly constrain normal knee flexion
30:35
and internal rotation. This could alter contact
30:38
pressures, particularly in the lateral compartment
30:40
of the knee. Techniques that pass the graph deep
30:44
to the fibular collateral ligament and fix it
30:46
with a knee in slight flexion around 30 degrees
30:48
seem to replicate native kinematics better than
30:51
some older techniques, but they can still minimally
30:54
constrain motion. And clinically, do they lead
30:57
to better results? Well, clinically, while they
30:59
improve objective stability measures like the
31:01
pivot shift, meta -analyses in clinical studies
31:04
cited in the source often don't show significantly
31:06
better patient -reported outcomes or return to
31:09
sport rates compared to isolated ACL reconstruction.
31:12
However, they are associated with increased complication
31:15
rates, things like infection or stiffness. So
31:18
it's a trade -off? It's a classic biomechanical
31:20
trade -off. You gain some objective stability
31:23
but potentially lose some natural motion and
31:25
introduce other risks. It has to be carefully
31:27
considered for the right patient. That's a crucial
31:30
nuance. Surgery can improve stability, but doesn't
31:33
always perfectly restore native function or lead
31:35
to better subjective outcomes for the patient.
31:38
This seems perhaps even more pronounced in joint
31:40
replacements. Let's talk about the biomechanics
31:42
of total knee arthroplasty, or TKA. Yes, total
31:46
knee replacement is a truly remarkable procedure
31:49
for relieving pain and restoring function in
31:51
arthritic knees. But biomechanically, you're
31:55
replacing a complex biological system with mechanical
31:57
components. The design of the implant itself
32:00
matters significantly. How so? More constrained
32:02
designs, which have more built -in stability
32:05
between the components, rely less on the patient's
32:07
remaining ligaments. But they transfer more stress
32:10
to the bone implant interface, which can increase
32:13
the long -term risk of loosening. Less constrained
32:15
designs rely more on preserving and carefully
32:17
balancing the patient's own ligaments for stability,
32:20
aiming for perhaps more natural kinematics, but
32:23
requiring good soft tissue integrity. And designs
32:25
like CR versus PS. Right. Different designs,
32:29
like cruciate retaining CR versus posterior stabilized
32:32
PS designs, handle the role of the sacrifice
32:35
PCL differently. This impacts the rollback motion
32:38
of the femur on the tibia during flexion, which
32:40
is part of normal knee kinematics. And getting
32:43
the alignment right during surgery must be absolutely
32:46
paramount for load distribution and longevity.
32:48
It's absolutely critical. The source highlights
32:50
different alignment philosophies like aiming
32:53
for a straight mechanical axis aligned with the
32:55
center of the hip, knee, and ankle versus aiming
32:58
for a more kinematic alignment trying to replicate
33:00
the patient's native pre -arthritic anatomy.
33:03
Does the philosophy matter most or the execution?
33:06
Regardless of the philosophy, Restoring the appropriate
33:09
coronal plane alignment, avoiding excessive varus
33:11
or valgus, and restoring the native joint line
33:14
height are essential for balancing the soft tissues
33:16
properly and distributing load evenly across
33:19
the implant. FEA studies, like the one by Kang
33:23
et al. mentioned, clearly show that even small
33:25
degrees of malalignment in the femoral component
33:27
can significantly shift the stress distribution
33:30
on the polyethylene bearing surface and any remaining
33:33
cartilage. This can lead to uneven wear and potentially
33:37
earlier failure. Valgus malalignment in particular
33:40
appears detrimental in shipping contact stresses
33:43
laterally. What about the biomechanical reality
33:46
of what patients can actually do after TKA? The
33:49
textbook suggests they often don't achieve completely
33:51
normal gait mechanics. Is that right? That's
33:53
a key point for setting realistic patient expectations.
33:56
Systematic reviews cited in the source indicate
33:58
that while TKA dramatically improves function
34:01
compared to a painful arthritic knee, most patients
34:04
do not achieve a gait pattern identical to healthy
34:06
individuals. How is it different? They often
34:08
walk with a reduced range of motion. particularly
34:11
less knee flexion during the swing phase of gait
34:14
and also reduced loading of the operated leg
34:17
during the stance phase. And that affects activities.
34:20
Yes. This altered gait pattern along with the
34:23
inherent mechanical limitations of the implant
34:25
designs themselves explains why high impact or
34:28
pivoting sports like tennis, basketball or running
34:31
remain challenging or generally unadvised. There's
34:34
just too much risk of loosening or excessive
34:36
wear. Activities with more predictable, less
34:39
complex loads like cycling, swimming, or golf
34:42
are typically much more achievable and recommended.
34:44
And this ties into concerns about implant longevity,
34:47
especially for younger or more active patients
34:49
receiving a TKA. Precisely. Higher activity levels
34:53
generate more load cycles and potentially higher
34:55
peak forces on the implant components. This leads
34:58
to increased wear on the polyethylene, insert
35:01
the plastic liner, and increased stress at the
35:03
bone implant interface. And that leads to failure.
35:06
This increased wear and stress is believed to
35:09
contribute significantly to aseptic loosening,
35:12
which is the most common reason for revision
35:14
surgery in TKAs. Registry data, such as from
35:17
the Norwegian Arthroplasty Registry referenced
35:19
in the text, clearly shows a higher revision
35:22
risk for younger, more active patients, particularly
35:25
males under 65. This supports the biomechanical
35:29
link between activity level, implant loading,
35:32
and lifespan. So managing expectations is key.
35:34
Absolutely. Surgeons must communicate this reality,
35:38
guiding patients toward realistic expectations
35:40
about their potential function and the potential
35:43
impact of their activity choices on the longevity
35:45
of their knee replacement. Lastly, let's just
35:47
circle back briefly to mechanical loading and
35:49
tissue healing, specifically in cartilage repair.
35:52
The source mentions some intriguing, almost conflicting
35:54
findings from in vitro studies regarding the
35:57
effects of shear forces. Yes, this highlights
36:00
the real subtlety and complexity of mechanobiology,
36:03
how mechanical stimuli influence biological processes
36:06
at a cellular level. In the context of cartilage
36:10
repair, particularly techniques like microfracture,
36:12
which aim to create a clot that hopefully forms
36:14
fibrocartilage, there's been interest in the
36:17
role of mechanical loading, such as using continuous
36:19
passive motion CPM machines after surgery. What
36:23
did the studies show? Some in vitro studies,
36:25
using cartilage cells or repair tissue constructs
36:27
in a lab environment, have suggested that applying
36:30
certain types of mechanical stimulation, including
36:33
shear forces, could be beneficial. They might
36:35
stimulate the cells to produce matrix components
36:38
like proteoglycans or PRG4, which is a lubricating
36:41
protein. One study by Nugent, Derfus, and Au
36:45
found this with specific shear stresses. But
36:48
other studies found a different or even opposite
36:50
response. Yes, that's the intriguing part. Other
36:53
in -Beetro studies, perhaps looking at different
36:55
types of mechanical stimuli or different time
36:57
points after injury, have shown that mechanical
37:00
loading, including the fluid shear stress associated
37:03
with movement, could also upregulate catabolic
37:06
enzymes. Things like matrix metalloproteinases,
37:09
enagricanases, adMTS. And those break down tissue.
37:12
Exactly. These enzymes break down the extracellular
37:15
matrix. So the same type of stimulus shear stress
37:17
applied under slightly different conditions or
37:19
analyzed differently can potentially elicit both
37:22
anabolic like building up. and catabolic breaking
37:25
down responses. That's a bit counterintuitive,
37:27
isn't it? It suggests that the precise type,
37:29
magnitude, duration, and frequency of mechanical
37:32
load, as well as the specific biological state
37:35
of the tissue at that time, are absolutely critical.
37:38
It's exactly right. This is why translating promising
37:41
in vitro findings directly into clinical practice
37:43
is so challenging. While CPM is sometimes used
37:46
after cartilage repair, based on the hypothesis
37:49
that early movements beneficial, the clinical
37:51
evidence supporting its routine use for improving
37:54
actual cartilage repair outcomes isn't as strong
37:57
or consistent as those initial in vitro findings
37:59
might suggest. So still more to learn. It underscores
38:02
that we still have a lot to learn about the optimal
38:04
mechanical environment for promoting true regeneration
38:07
rather than just repair in tissues like cartilage.
38:10
Yeah. The interaction between mechanics and biology
38:12
is incredibly complex. We've covered a tremendous
38:15
amount of ground today, really peeling back the
38:17
layers on orthopedic biomechanics, from the inherent
38:21
properties of tissues to the intricate mechanics
38:23
of our joints and the biomechanical realities
38:26
driving treatment outcomes. Before we wrap up,
38:30
could you share maybe a couple of your most memorable
38:31
quick hits or facts from this source material?
38:34
Certainly. One that always sticks with me is
38:37
that the iliofemoral ligament, one of the key
38:39
stabilizers in the hip, is actually biomechanically
38:42
the strongest ligament in the entire human body.
38:45
Quite impressive. Wow, I didn't know that. Another
38:47
is the versatility of finite element analysis,
38:50
seeing a tool originally developed for analyzing
38:52
bridges now being routinely used to understand
38:55
the intricate mechanics of a hip implant or a
38:58
reconstructed knee. That's quite a leap. It is.
39:01
And then those striking statistics we discussed
39:03
earlier, freeze -drying bone grafts potentially
39:06
reducing their mechanical strength by 20 percent
39:08
and that incredible one millimeter talar shift
39:11
reducing ankle contact area by 42 percent. They're
39:14
just powerful reminders of the precision involved
39:16
and how small changes can have big consequences.
39:19
Those details truly highlight the deep dive nature
39:22
of this material. For our listener, perhaps a
39:24
mid to senior professional navigating various
39:27
industries, what would you say are the core takeaways
39:29
from this exploration? Well, I think firstly,
39:31
understanding orthopedic biomechanics provides
39:34
a fundamental framework. It helps comprehend
39:36
injury mechanisms, the rationale behind different
39:39
treatment approaches, and the challenges of recovery.
39:41
And that knowledge is valuable whether you're
39:44
involved in health care directly, medical devices,
39:46
insurance, sports management, or related fields.
39:50
Secondly, every orthopedic intervention from
39:52
Grafting tissues to implanting joints involves
39:55
specific biomechanical trade -offs. There's rarely
39:58
a perfect solution that fully replicates native
40:01
function, and understanding these compromises
40:03
is absolutely key to setting realistic expectations
40:07
for patients and for product development. Thirdly,
40:10
advanced analytical tools like FEA are transforming
40:14
our ability to understand complex biological
40:16
systems and predict the outcomes of interventions.
40:19
This marks a clear direction for the future of
40:21
the field, even though translating this fully
40:24
into routine clinical practice takes time and
40:26
effort. Makes sense. And fourthly, perhaps most
40:29
fundamentally, the inherent complexity and delicate
40:32
balance of static and dynamic stability within
40:34
our joints mean that seemingly minor injuries
40:38
can have significant cascading biomechanical
40:41
effects. This can predispose individuals to long
40:44
-term issues if not addressed with that biomechanical
40:48
understanding firmly in mind. That's a fantastic
40:51
summary. Thank you so much for guiding us through
40:53
this complex yet utterly fascinating subject
40:55
today. My pleasure. It's a feel I'm passionate
40:57
about. If you found this deep dive insightful,
41:00
please consider rating and sharing the show.
41:02
It really helps others discover valuable knowledge.
41:04
As we continue to advance our understanding and
41:06
develop new technologies and orthopedics, that
41:09
central challenge seems to remain. Can we truly,
41:12
perfectly replicate the complex, dynamic biomechanics
41:16
of a healthy, living, human joint? The ultimate
41:19
goal. And if not, or perhaps not yet, what does
41:22
that fundamental limitation mean for the ultimate
41:25
potential of restoring full mobility and function
41:27
after injury or disease? Something to ponder.
41:31
You can explore these questions further by diving
41:32
into comprehensive texts on orthopedic biomechanics
41:35
like the one that guided our discussion today.
41:37
Until next time, keep diving deep.